Patent Publication Number: US-2022226028-A1

Title: Contoured bone plate with locking screw for bone compression, particularly across a tarsometatarsal joint

Description:
RELATED MATTERS 
     This application claims the benefit of U.S. Provisional Patent Application No. 63/138,726, filed Jan. 18, 2021, the entire contents of which are incorporated herein by reference. 
    
    
     TECHNICAL FIELD 
     This disclosure relates to bone plates and methods for fixating bones using a bone plate, including compressing opposed bone ends together using a bone plate. 
     BACKGROUND 
     Bones, such as the bones of a foot, may be anatomically misaligned. In certain circumstances, surgical intervention is required to correctly align the bones to reduce patient discomfort and improve patient quality of life. Surgical intervention may involve cutting one or more of the misaligned bones and then physically realigning the bones into an anatomically corrected position. A bone plate or multiple bone plates may be used to hold the bones in the anatomically corrected position, helping to prevent the bones from shifting back to their misaligned position. 
     SUMMARY 
     In general, this disclosure is directed to bone plates and screws, systems incorporating bone plates and screws, and methods of using bone plates. In some examples, bone plate systems and techniques are described to facilitate compression (e.g., angular compression) between opposed ends of two bone portions to which a bone plate is attached, which may be different portions of the same bone or two different bones separated by a joint. The force generated by the plating system may be asymmetrically distributed across the faces of the bone ends being pressed together, e.g., such that there is a greater force on a side of the bone ends opposite the plate than on a side of the bone ends closer to the plate. This may help facilitate angular correction of the bone portions relative to each other and/or promote healing (e.g., fusion) between the bone portions in a corrective orientation. 
     In some implementations, a bone plate includes an elongated body having a length greater than a maximum width and thickness. For example, the bone plate may have a length sized to span a tarsometatarsal joint separating a metatarsal from an opposed cuneiform. The bone plate may include a bend that displaces a portion of the bone plate positionable over the joint between the two bone portions away from the joint. As a result, the bone plate may include a first end contacting one bone portion and a second end contacting the second bone portion, with an intermediate portion between the two ends displaced off of one or both bone portions and/or the joint between the two bone portions. 
     To secure the bone plate to the bone portions, the bone plate can include multiple fixation holes extending through the bone plate, including at least one fixation hole positionable over the first bone portion and at least one additional fixation hole positionable over the second bone portion. One or more of these fixation holes may include threading partially or fully encircling the fixation hole to facilitate engagement with threading on the head of a locking screw insertable through the fixation hole and into an underlying bone. 
     To both secure the locking plate to an underlying bone portion and achieve compression between the ends of the two bone portions being secured together with the bone plate according to some examples, at least one locking screw may be used that is configured to both interlock with the bone plate and deform the bone plate when driven beyond its initially engaged position in the bone plate. For example, as an arch in the bone plate is physically deformed toward a flattened or unbent profile (e.g., resulting in a residual arch of smaller height after deformation), an underside of the plate may be placed in tension and a topside of the plate placed in compression. As a result, a moment force may be applied that has an asymmetrically distributed magnitude across the end faces of the bones being compressed. When used, the locking screw may be configured to interlock with the bone plate and deform the bone plate by controlling the compression ratio of the locking screw. The compression ratio of the bone screw may be controlled by adjusting the pitch of the threading on the head of the screw relative to the pitch of the threading on the shaft of the screw and/or by controlling the lead of the head relative to the lead of the shaft. 
     Traditional bone plate systems utilize one of two different types of screws: compression screws or locking screws. Compression screws are screws that have a threaded shaft but do not have a threaded head. In use, a compression screw can be driven until the head of the screw contacts the bone plate and then further driven into the bone to compress the bone plate. By contrast, locking screws have both a threaded head and a threaded shaft. However, locking screws are generally designed to be screwed until the threaded head is interlocked with the counter threading on the bone plate without causing any compression on the bone plate. 
     In accordance with some examples of the present disclosure, a bone plate is provided with one or more locking screws that achieve both interlocking between the head of the screw and the counter threading around the fixation hole on the bone plate as well compression of the bone plate during rotation. The pitch of the threading on the shaft of the screw may be sufficiently greater than the pitch of the threading on the head of the screw to achieve both interlocking and compression. Additionally or alternatively, the lead of the threading on the shaft may be greater than the lead of the threading on the head to generate a compressive force as the locking screw is inserting into an underlying bone. In either case, as the threading on the head of the screw rotationally interlocks with the counter threading around the fixation hole, the threading on the shaft may continue to draw the bone plate engaged with the threading on the head down toward the bone. As a result, a bend in the bone plate may deform (e.g., elastically and/or plastically) toward the bone portions being fixated. 
     In some examples, the bone plate is provided with the one or more locking screws configured for both interlocking with the bone plate and for compression. The bone plate has a bend portion. The bend portion may be a region of the bone plate between opposed ends of the bone plate that is non-planar with one or both end portions (e.g., prior to deformation and/or installation). The bend portion may be offset from the end portions in one or more planes. For example, when one end of the bone plate is positioned in contact with one bone portion and the second end of the bone plate is positioned in contact with the other bone portion, the bend portion may define a gap between a bone-facing surface of the bone plate in the bend portion and the surfaces of the underlying bone(s). This gap may be reduced or eliminated through flattening of the bend upon installation of the one or more locking screws that are also configured to achieve compression. 
     With the bend portion of the bone plate positioned over the joint between the two bone portions to be fixated together, one or more locking screws configured for compression may be installed through corresponding fixation holes in the bone plate and into underlying bone. As the one or more locking screws are installed, the bend portion in the bone plate may deform toward the joint between the two bone portions. With the bone plate deformed from an initial bend to a reduced bend profile, the bone plate may function as a spring providing a distributed load through the end faces of the bones being pressed together, e.g., with a greater force on the cortex of the bones on an opposite the plate than the force on the cortex of the bones closest to the plate. As a result, the force provided by the tensioned bone plate may be angular, e.g., helping to reinforce a bone realignment performed prior to fixation using the bone plate. 
     In some examples, a bone plate with a bend portion may be positioned over a joint between two adjacent bone portions to be fixated and one or more locking screws configured for compression installed through the fixation holes of the bone plate into the underlying bone portions. One or more additional screws (e.g., compression screws, locking screws not configured for compression) may also be installed through one or more fixation holes of the bone plate into one or more underlying bone portions. 
     Additionally or alternatively, one or more driving pins may be used to help install and pre-compress the bone plate prior to installation of the screws. When used, a driving pin may include a threaded head, a shaft, and an enlarged region having a cross-sectional area larger than a cross-sectional area of the fixation hole through which the head of driving pin is to be inserted. One or more driving pins can be installed through the fixation holes of the bone plate into the underlying bone portions, e.g., by screwing the distal head of the one or more driving pins into the underlying bone portions. As the driving pin(s) are driven deeper into the underlying bone portion(s), the enlarged region of the driving pin can press against a top surface of the bone plate adjacent a corresponding fixation hole. This can cause the bone plate to compress toward the bone portions being fixated. One or more individual driving pins can then be removed and corresponding screws installed to complete the installation process. 
     In yet additional examples, a bone plate with a bend portion may be pre-deformed (e.g., pre-compressed) before or concurrent with being positioned over a joint between two adjacent bone portions to be fixated (and prior to installation of any screws or, optionally, driving pins). For example, using hand manipulation and/or a bending instrument, the bend portion of the plate may be compressed toward a more planar shape and held in compression while placed spanning the joint between the bone portions being fixated. The bone screws and/or driving pins can then be installed through the fixation holes of the bone plate while held in compression. One example bending instrument that may be used is a pair of plate bending arms inserted through fixation holes on opposite sides of the apex of the bend portion (e.g., into drill guides installed in the fixation holes), which are then used to manipulate the bone plate. 
     In one example, a method of applying a bone plate across a tarsometatarsal joint is described. The method includes positioning a bone plate across a tarsometatarsal joint separating a metatarsal from a cuneiform. The bone plate has a first fixation hole, a second fixation hole, and a bend between the first fixation hole and the second fixation hole. Positioning the bone plate across the tarsometatarsal joint involves positioning the bend over the tarsometatarsal joint with a gap between a bone-facing surface of the bone plate and the tarsometatarsal joint. The method also involves inserting a locking screw through the first fixation hole. The locking screw has a head with a head thread and a shaft with a shaft thread. The shaft thread has a pitch greater than a pitch of the head thread, and the first fixation hole includes threading for engaging with the head thread. The method involves screwing the locking screw into a metatarsal or a cuneiform under the first fixation hole until the head thread of the locking screw is engaged with the threading defined by the first fixation hole and further screwing the locking screw into the metatarsal or the cuneiform, thereby deforming the bend in the bone plate toward the tarsometatarsal joint. 
     In another example, an orthopedic fixation system is described. The system includes a bone plate having a length defining a longitudinal axis extending from a proximal end of the body to a distal end of the body. The bone plate has a top surface and a bone-facing surface opposite the top surface and includes a first fixation hole extending through the body and a second fixation hole extending through the body. The length of the bone plate is sized to cross a tarsometatarsal joint with one of the first fixation hole and the second fixation hole positioned over a metatarsal and an other of the first fixation hole and the second fixation hole positioned of a cuneiform. At least the first fixation hole includes threading, and the bone plate includes a bend offsetting a portion of the bone plate between the first fixation hole and the second fixation hole relative portions of the bone plate defining the first fixation hole and the second fixation hole. The system also includes a locking screw having a head with a head thread and a shaft with a shaft thread, the shaft thread having a pitch greater than a pitch of the head thread. The locking screw exhibits a compression ratio defined by the pitch of the shaft thread divided by the pitch of the head thread. The locking screw is configured to be inserted through the first fixation hole into at least one of the metatarsal and the cuneiform and the head thread engaged with the threading defined by the first fixation hole. The compression ratio is effective to cause the bone plate to deform when the head thread is fully engaged with the threading defined by the first fixation hole and the screw is further turned. 
     In another example, a method is described that includes tensioning a bone plate having a first fixation hole, a second fixation hole, and a bend between the first fixation hole and the second fixation hole by bending the bone plate against the bend toward a flattened profile, thereby providing a tensioned bone plate. The method includes positioning the tensioned bone plate across a tarsometatarsal joint separating a metatarsal from a cuneiform and inserting a locking screw through the first fixation hole. The locking screw has a head with a head thread and a shaft with a shaft thread. The shaft thread having a pitch greater than a pitch of the head thread, and the first fixation hole includes threading for engaging with the head thread. The method also includes screwing the locking screw into the metatarsal or the cuneiform under the first fixation hole until the head thread of the locking screw is engaged with the threading defined by the first fixation hole. 
     The details of one or more examples are set forth in the accompanying drawings and the description below. Other features, objects, and advantages will be apparent from the description and drawings, and from the claims. 
    
    
     
       BRIEF DESCRIPTION OF DRAWINGS 
         FIGS. 1 and 2  are side and top views, respectively, of an example bone plate that may be used to achieve both fixation and compression across two bone portions. 
         FIG. 3  is side view of an example locking screw that can be used with the bone plate of  FIGS. 1 and 2 . 
         FIG. 4  is an illustration of the example bone plate of  FIGS. 1 and 2  secured to a first bone portion and a second bone portion across a joint between the two bone portions. 
         FIGS. 5, 6A and 6B  are illustrations showing an example application of the bone plate of  FIGS. 1 and 2  using first and second locking screws. 
         FIG. 7  is a flow diagram illustrating an example technique for attaching a bone plate system according to disclosure. 
         FIG. 8  is side view of an example driving pin that can be used to help install a bone plate on a bone. 
         FIG. 9  is a side view of an example bone plate illustrating an example driving pin of  FIG. 8  inserted through a fixation hole of the bone plate. 
         FIGS. 10-15  illustrate example procedure steps for attaching a bone plate to a medial cuneiform and a first metatarsal separated by tarsometatarsal joint. 
         FIGS. 16-22  illustrate example procedural steps that may be performed after the procedure steps described with respect to  FIGS. 10-15 . 
         FIGS. 23 and 24  show example procedure steps for pre-tensioning a bone plate prior to installation. 
     
    
    
     DETAILED DESCRIPTION 
     The present disclosure is generally directed to bone plates, systems and kits that include one or multiple bone plates and screws, and method of using one or multiple bone plates and corresponding screws. In an exemplary application, a bone plate and screw system according to the disclosure can be useful for internal fixation of a bone or bones during a surgical procedure, such as a bone alignment, osteotomy, fusion procedure, fracture repair, and/or other procedures where one or more bones are to be set in a desired position. Such a procedure can be performed, for example, on bones (e.g., adjacent bones separated by a joint or different portions of a single bone) in the foot or hand, where bones are relatively small compared to bones in other parts of the human anatomy. In one example, a procedure utilizing an embodiment of the bone plate and screw system can be performed to correct an alignment between a metatarsal (e.g. a first metatarsal) and a cuneiform (e.g., a medial cuneiform), such as a bunion correction. An example of such a procedure is a lapidus procedure. In another example, the procedure can be performed by modifying an alignment of a metatarsal (e.g. a first metatarsal). An example of such a procedure is a basilar metatarsal osteotomy procedure. 
     Example screw configurations and methods of installing bone plate and screw systems according to the disclosure will be described in greater detail with respect to  FIGS. 3-24 . However, an example bone plate that may be used in accordance with the disclosure will first be described with respect to  FIGS. 1 and 2 . 
       FIGS. 1 and 2  are side and top views, respectively, of an example bone plate  10  that may be used to achieve both fixation and compression across two bone portions. Bone plate  10  defines a body  12  having a central longitudinal axis  14 . The body of the bone plate  10  has a top surface  16  and a bone facing surface  18 , where the bone facing surface  18  is on a side of the body  12  opposite the top surface  16 . In some implementations, bone plate  10  is positioned so that the bone facing surface  18  interfaces with and/or is in contact with one or both bone portions along at least a portion of the length of longitudinal axis  14 . For convenience, “bone facing surface” will refer to the side of the bone plate generally facing bone when the plate is positioned on one or more bones, regardless of whether there is more than one surface contacting the bone when bone plate  10  is applied. 
     Body  12  of bone plate  10  can define a distal region  20  at or near a first terminal end  22  and a proximal region  24  at or near a second terminal end  26  that is opposite the first terminal end of the body. The distal region  20  may be separated from the proximal region  24  by an intermediate region  28 . For example, bone plate  10  may include one or more fixation holes extending through the thickness of body  12 . In these examples, body  12  may include one or more fixation holes in distal region  20 , one or more additional fixation holes in proximal region  24 , and an intermediate region  28  devoid of fixation holes positioned between the distal region  20  and the proximal region  24 . 
     In the illustrated example of  FIGS. 1 and 2 , distal region  20  of bone plate  10  has at least one fixation hole, which is illustrated as two fixation holes  30  and  32 . Proximal region  24  also has at least one fixation hole, which is also illustrated as two fixation holes  34  and  36 . First fixation hole  30  extending through body  12  in distal region  20  is the fixation hole closest to the intermediate region  28  on the distal side of the bone plate which, as will be described, can include a bend offsetting the intermediate region from an underlying bone surface. Second fixation hole  34  extending through body  12  in proximal region  24  is the fixation hole is the fixation hole closest to the intermediate region  28  on the proximal side of the bone plate. Third fixation hole  32  in the illustrated example is located between first fixation hole  30  and the first terminal end  22  of the bone plate. Fourth fixation hole  36  in the example is located between second fixation hole  34  and the second terminal end  26  of the bone plate. 
     Each feature described as a fixation hole may be an opening extending through the thickness of body  12  that is sized to receive a corresponding screw. Each fixation hole may typically have a circular cross-sectional shape although may have other cross-sectional shapes without departing from the scope of the disclosure. The fixation hole may extend perpendicularly through the thickness of body  12  or may taper (e.g., such that the hole is larger adjacent top surface  16  than adjacent bone-facing surface  18 ). In still other examples, the fixation hole may extend at a non-perpendicular angle through the thickness of body  12  and/or be configured for polyaxial screw alignment. 
     Although bone plate  10  is illustrated as being configured with four fixation holes  30 ,  32 ,  34 , and  36 , the bone plate may include fewer fixation holes or more fixation holes. For example, distal region  20  and proximal region  24  of bone plate  10  may each include fewer fixation holes (e.g., one) and/or more fixation holes (e.g., three, four). The dimensions (e.g., length) of the distal and proximal regions  20 ,  24  can be adjusted to accommodate the particular number of fixation holes included. Further, while the fixation holes on bone plate  10  are illustrated as being co-axial with each other along the longitudinal axis  14  of the bone plate, the bone plate may include one or more branches each containing a fixation hole extend off of the longitudinal axis. As a result, the one or more fixation holes in these branch(es) may be non-co-linear with the remaining co-axially arranged fixation holes. For instance, in various examples, bone plate  10  may include at least one branch extending outwardly from the longitudinal axis  14  of the bone plate to define at least one of a Y-shape, an L-shape, a T-shape, a U-shape, and/or other shape profile. 
     Bone plate  10  may include a bend  40 . Bend  40  may be a portion of bone plate  10  that is out of plane with one or more planes in which first fixation hole  30  and second fixation hole  34  are positioned. In some examples, first terminal end  22  and second terminal end  26  of bone plate  10  are coplanar (e.g., such that the terminal ends of the bone plate can be positioned in the same plane). Bend  40  may offset at least a portion of bone plate  10  out of the plane in which first terminal end  22  and second terminal end  26  are positioned. 
     As will be described, when bone plate  10  containing bend  40  is positioned across a joint between two bone portions, at least part of distal region  20  (e.g., including first terminal end  22 ) may contact one bone portion and at least part of proximal region  24  (e.g., including second terminal end  26 ) may contact the other bone portion. Bend  40  may elevate a portion of bone plate  10  off of the surface of one or both bone portions across the joint. As a result, a gap may exist between bone-facing surface  18  of bone plate  10  in the region of the bend and the underlying bone portions. The size of this gap may be reduced (optionally without eliminating the gap) upon insertion of one or more screws and/or compression of the bone plate. 
     Bend  40  of bone plate  10  may curve distal region  20  toward proximal region  24  about intermediate region  28 . For example, bend  40  can reduce the distance between first terminal end  22  and second terminal end  26  as compared to when body  12  is flat or planar. Bend  40  can be defined by a sharp transition (e.g., V-shape) or a radius of curvature. The radius of bend  40  can vary or be constant as a function of longitudinal position on body  12 , and/or be concentrated in one or more portions of the body, such as the portion of the body between the proximal and distal regions  20 ,  24 . In some examples, bend  40  is defined by a radius of curvature ranging from approximately 10° to approximately 45°, such as from approximately 15° to approximately 35°. In other examples, bend  40  may be defined by a radius of curvature ranges from 45° to 135°, such as from approximately 75° to approximately 105°. Other angles of bend are also possible. 
     When bone plate  10  is configured with a bend, the entire length of the bone plate may be bent (e.g., to define a radius of curvature) or only one region of the bone plate may be bent out of plane relative to a remainder of the bone plate. Therefore, when discussing that bone plate  10  may have a bend  40  in the intermediate region  28  between proximal and distal regions  20 ,  24 , it should be appreciated that the bend may or may not be isolated to that region. Rather, bend  40  may define an apex in intermediate region  28  between first fixation hole  30  and second fixation hole  34 , e.g., such that the peak of the bone plate and/or maximum offset relative to the first and second fixation holes (and/or first and second terminal ends) is within this region. Depending on the application, the apex of bend  40  may be positioned along the length of bone plate  10  such that, when the bone plate is positioned across a joint separating to bone portions, the apex is substantially centered over the joint (e.g., within plus or minus 3 mm of the joint, such as plus or minus 2 mm of the joint, or plus or minus 1 mm of the joint). 
     Bone plate  10  can be formed of any suitable biocompatible material or combinations of materials, such as stainless steel, nitinol, titanium, and/or polymeric materials (e.g., polyether ether ketone or PEEK). Bend  40  can be formed by manufacturing bone plate  10  to include the bend (e.g., by casting or machining the bone plate initiate that includes bend  40 ). Alternatively, bone plate  10  can be fabricated as a planar plate that is subsequently bent (e.g., plastically deformed) to create bend  40 . 
     Bone plate  10  can have a variety of features and configurations. For example, the width of bone plate  10  may be constant across the length of the bone plate or may vary such that one or more regions of the bone plate have a width greater than one or more other regions of the bone plate. For instance, in some implementations, bone plate  10  may have a larger width in regions containing fixation holes and a narrow width in regions between adjacent fixation holes. Additionally or alternatively, the thickness of bone plate  10  may be constant across the length of the bone plate or may vary such that one or more regions of the bone plate have a thickness greater than one or more other regions of the bone plate. For example, bone plate  10  may include pads projecting down from a remainder of the bone-facing surface  18  (e.g., in the region of the fixation holes) and/or channels that are recessed relative to a remainder of the bone-facing surface to define different thicknesses across the length of the bone plate. Example bone plate features that may be used are described in U.S. Pat. No. 10,245,088, titled “Bone Plating System and Method,” the entire contents of which are incorporated herein by reference. 
     Bone fasteners can be used to secure bone plate  10  to underlying bone portions. As briefly discussed above, at least one of the bone fasteners used to secure the bone plate to an underlying bone portion may be structured as a locking screw that is configured to both interlock with the bone plate and achieve compression, thereby deforming bend  40  toward underlying bone surfaces. 
       FIG. 3  is side view of an example locking screw  50  that can be used with bone plate  10  of  FIGS. 1 and 2 . Locking screw  50  extends from a proximal end  52  to a distal end  54 . Locking screw  50  includes a head  56  and a shaft  58 . Head  56  of locking screw  50  includes thread  60  partially or fully encircling the head for engaging with counter threading encircling a fixation hole of bone plate  10  into which the locking screw is intended to be inserted. Thread  60  may be referred to as head thread for purposes of discussion. Shaft  58  of locking screw  50  includes thread  62  partially or fully encircling the shaft for engaging with a bone portion underlying a fixation hole of bone plate  10  through which locking screw  50  is inserted. Thread  62  may be referred to as shaft thread for purposes of discussion. 
     Thread  60  and  62  may each be a helical structure used to convert rotational motion into linear movement or force. Thread  60  and  62  may be defined by a ridge of material wrapped around an inner cylinder or cone of material in the form of a helix, to define a straight thread or a tapered thread, respectively. 
     Locking screw  50  can be characterized by both its lead and its pitch. Lead is the distance along the axis of the screw that is covered by one complete rotation of the screw (360°). Pitch is the distance from the crest of one thread to the next. In some examples, locking screw  50  is configured as a single lead screw, e.g., such that there is only one threaded ridge wrapped around the body of the screw. When so configured, each time the body of the screw is rotated one turn (360°), it has advanced axially by a distance equal to the pitch or spacing between adjacent ridges along the axis of the screw. In other examples, locking screw  50  is configured as a multi-lead screw, such as a dual lead screw, a tri-lead screw, or a quad-lead screw, such that each time the body of the screw is rotated one turn, it is advanced axially by a multiple of the pitch or spacing between adjacent ridges. In other words, the pitch and lead may be equal for a single lead screw but the lead may be the pitch or spacing between adjacent ridges multiplied by the number of screw starts for a multi-lead screw (e.g., pitch×2 for a dual-lead screw, pitch×3 for a tri-lead screw). 
     In accordance with some implementations of the present disclosure, locking screw  50  is configured to be inserted through a fixation hole of bone plate  10  and driven into an underlying bone portion. The locking screw can be configured with a compression ratio greater than 1.0. As used herein, the term “compression ratio” means the pitch of the shaft thread multiplied by the number of number of starts on the shaft thread with that sum being divided by the pitch of head thread multiplied by the starts on the head thread. This can be represented by the following equation: 
     
       
         
           
             
               Compression 
               ⁢ 
               
                   
               
               ⁢ 
               Ratio 
             
             = 
             
               
                 
                   
                     
                       Pitch 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       of 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Shaft 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Thread 
                       × 
                     
                   
                 
                 
                   
                     
                       Number 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       of 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Shaft 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Thread 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Starts 
                     
                   
                 
               
               
                 
                   
                     
                       Pitch 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       of 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Shaft 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Thread 
                       × 
                     
                   
                 
                 
                   
                     
                       Number 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       of 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Head 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Thread 
                       ⁢ 
                       
                           
                       
                       ⁢ 
                       Starts 
                     
                   
                 
               
             
           
         
       
     
     In practice, the head thread  60  may typically be a single start threading. In such configurations, the compression ratio may be the pitch of shaft thread  62  divided by the pitch of head thread  60  when shaft thread  62  defines a single start screw. When shaft thread  62  defines a dual-start screw, the compression ratio may be twice the pitch of shaft thread  62  divided by the pitch of head thread  60 . 
     The differential pitch and/or starts between head thread  60  and shaft thread  62  may be selected to be effective to deliver a compressive force to bone plate  10  when locking screw  50  is inserted into the bone plate. For example, when bone plate  10  is secured to one bone portion with a bone fastener, locking screw  50  may be inserted through a fixation hole across a joint into another bone portion. As head thread  60  of locking screw  50  engages with counter threading encircling the fixation hole of the bone plate into which the screw is inserted, shaft thread  62  may continue drawing the screw down into the underlying bone. As a result, bend  40  in bone plate  10  may deform by bowing toward the bone portions. As locking screw  50  continues to be screwed into the fixation hole a bone plate  10 , bend  40  may further deform. Locking screw  50  may be inserted into the underlying bone until head  56  is fully seated within a receiving opening defined by the fixation hole the bone plate. 
     The specific compression ratio that is effective to achieve compression of bone plate  10  during use may vary, e.g., based on the thickness of the plate. In general, compression ratio may be greater than 1.0. As a result, one rotation (360°) of locking screw  50  may cause the shaft of the screw to traverse a larger axial distance than the axial distance the head of the screw travels seating into the counter thread defined by the fixation hole. As a result, bone plate  10  may deform a distance toward the underlying bone into which locking screw  50  is inserted to accommodate the differential travel length of the shaft relative to the head due to the compression ratio. 
       FIG. 3  illustrates head  56  having example pitch  64  and shaft  58  having example pitch  66 . The compressive force generated by having a differential pitch and/or number of thread starts between the head and shaft can be characterized by the compression ratio as discussed above. In some implementations, locking screw  50  exhibits a compression ratio greater than 1.0, such as greater than 1.5, such as greater than 1.6, greater than 1.7, greater than 1.75, greater than 1.9, greater than 2.1, greater than 2.3, greater than 2.5, or greater than 3.0. For example, the compression ratio of locking screw  50  may be of value falling within a range from 1.45 to 3.5, such as from 1.5 to 2.5. Locking screws exhibiting the foregoing compression ratios may be effective to deform bend  40  of bone plate  10  where the bone plate has a thickness less than 5 mm in the region of the bend, such as less than 3 mm, or less than 2 mm. For example, bone plate  10  may have a thickness ranging from 1 mm to 2 mm (e.g., at least in the region of bend  40 ) and may be deformed by locking screw having a compression ratio greater than 1.5. In some implementations, a locking screw having any one of the foregoing compression ratios has a single start head threading and a single start shaft threading such that the compression ratio is provided by the shaft thread having a greater pitch than the head thread. 
     Bone plate  10  can include at least one fixation hole extending through body  12  in the distal region  20  of the bone plate and at least one fixation hole extending through the body and the proximal region  24  of the bone plate. In use, at least two fixation elements can be used to secure the bone plate to two different bone portions, e.g., with intermediate region  28  of the bone plate bridging the joint or gap between the two bone portions. For example, as discussed with respect to  FIGS. 1 and 2 , bone plate  10  may include at least a first fixation hole  30  and a second fixation hole  34  which, in the illustrated example, further includes a third fixation hole  32  and a fourth fixation hole  36 . Bone plate  10  can be secured to underlying bone portions using a single locking screw configured as discussed with respect to  FIG. 3 , e.g., to interlock with the bone plate and achieve compression, or using multiple locking screws so configured. For example, at least one locking screw configured with an enhanced compression ratio, such as a compression ratio greater than 1.5, (e.g., at least two locking screws so configured) may be used to secure the bone plate to underlying bone portions. One or more other fixation elements having a configuration different than locking screw  50  with an enhanced compression ratio may be inserted through the other fixation holes of the bone plate. When using two or more locking screws  50 , the two or more locking screws may have the same configuration as each other (e.g., same compression ratio) or may have different configurations (e.g., different compression ratios) still consistent with locking screw  50  as described herein. 
     A bone plating system that includes bone plate  10  may include at least one locking screw  50  (e.g. such as two, three, or four locking screws  50 ) exhibiting a compression ratio effective to deform the bend  40  in the bone plate during use. The bone plating system may include one or more other mechanical fixation elements having a different configuration than locking screw  50  that is insertable through the other fixation holes of the bone plate to complete attachment to the underlying bone portions. Any suitable fixation elements can be used for these other attachment elements, such as screws having a different configuration than locking screw  50 , pins, rivets, spikes, or the like. 
     For example, the bone plating system may include at least one locking screw  50  exhibiting a compression ratio effective to deform the bend in bone plate  10  during use and at least one other screw (e.g., such as two, three, four or more) screws that are nonlocking screws and/or locking screws exhibiting a compression ratio less than that of locking screw  50 . For example, the bone plating system may include one or more locking screws having a compression ratio less than 1.5, such as less than 1.45, less than 1.25, or less than 1.2. For example, the bone plating system may include one or more locking screws having a compression ratio that is at least 0.05 less than the compression ratio exhibited by locking screw  50  configured as described with respect to  FIG. 3 , such as at least 0.1 less, at least 0.25 less, or at least 0.5 less. In some examples, the bone plating system may include one or more locking screws having a compression ratio of 1.0. 
     In one implementation, a bone plating system includes a bone plate  10 , at least two locking screws  50  exhibiting a compression ratio effective to deform bend  40  in the bone plate, and at least two additional locking screws having a compression ratio less than that of locking screw  50  (e.g., a compression ratio that does not result in substantial bending or any bending of the bone plate). In these systems, at least one locking screw  50  may be installed through a fixation hole on the distal region  20  of bone plate  10  and at least one locking screw  50  may be installed through fixation hole on the proximal region  24  of the bone plate. In these examples, the at least one two other locking screws having lower compression ratios than locking screw  50  may be installed through the remaining fixation holes on the distal region  20  and/or proximal region  24  of the bone plate. 
       FIG. 4  is an illustration of bone plate  10  secured to a first bone portion  70  and a second bone portion  72  across a separation  74  between the two bone portions (referred to herein as “joint  74 ” for purposes of discussion). First bone portion  70  and second bone portion  72  may be different portions of the same bone (e.g., a metatarsal) in which case separation  74  may be a cut line (e.g., where an osteotomy or bone shortening was performed) or fracture between the two bone portions. Alternatively, first bone portion  70  and second bone portion  72  may be different bones in which case separation  74  may be a joint, such as a metatarsal bone and a cuneiform bone separated by a tarsometatarsal joint. In the specific example of  FIG. 4 , first bone portion  70  is illustrated as a metatarsal and second bone portion  72  is illustrated as a cuneiform. 
     It should be appreciated that reference to first, second, third, etc. for different features or elements in the disclosure is for purposes of convenience and is not intended to impose an order of operation unless otherwise specified. For example, while bone plate  10  is described as including a first fixation hole  30  positionable over first bone portion  70  and a second fixation hole  34  positionable over second bone portion  72 , it should be appreciated that the first bone portion may be a metatarsal or a cuneiform in different examples. Further, during installation, the initial screw may be placed through second fixation hole  34  instead of first fixation hole  30 . Accordingly, other orders of installation and arrangement of components can be used and should not be limited to the specific examples described. 
     In the example of  FIG. 4 , bone plate  10  is illustrated bridging across the joint  74  with first fixation hole  30  and third fixation hole  32  positioned over an underlying first bone portion  70  (e.g., metatarsal) and second fixation hole  34  and fourth fixation hole  36  positioned over an underlying second bone portion  72  (e.g., cuneiform). When bone plate  10  is installed using at least one locking screw  50  and at least one other fixation element not configured as locking screw  50  (e.g., a non-locking screw or locking screw with lower compression ratio) the at least one locking screw can be inserted through any one of the fixation holes in the bone plate. That said, in some implementations, locking screw  50  may be installed through one or both fixation holes closest to joint  74  separating the two bone portions. 
     For example, when configured as illustrated in  FIG. 4 , one locking screw  50 A may be installed through first fixation hole  30  and/or one locking screw  50 B may be installed through second fixation hole  34 . Locking screws  50 A,  50 B may exhibit a compression ratio effective to deform plate  10  at least in the region of bend  40 . Utilizing one or more locking screws with a comparatively high compression ratio through one or more fixation holes closest to intermediate region  28  containing the apex of bend  40  may be useful to help deform the bend toward the underlying bone surfaces, e.g., by delivering the compression closest to where the bone plate is desirably deformed. 
     One or more other fixation holes of bone plate  10 , such as one or more fixation holes positioned proximally and/or distally of those fixation holes closest to intermediate region  28  may be secured to the underlying bone portions using screws having a different configuration than locking screw  50 A,  50 B. For example, one locking screw  76 A may be installed through third fixation hole  32  and/or one locking screw  76 B may be installed through fourth fixation hole  36 . Locking screws  76 A,  76 B may exhibit a lower compression ratio than each of locking screws  50 A and  50 B (e.g., when at least two locking screws  50  are utilized). 
     A bone plating system that includes a nonplanar bone plate, such as bone plate  10  with bend  40 , and one or more locking screws  50  that can interlock with the bone plate and generate a compressive force sufficient to deform the non-planarity of the bone plate during installation, can be useful to help compress the bone portions fixated together using the bone plate. When bone plate  10  is initially positioned over a joint separating two bone portions with the distal region  20  at least partially contacting first bone portion  70  and the proximal region  24  at least partially contacting the second bone portion  72 , a gap may exist between the bone facing-surface of the bone plate and the underlying bone portions. As the one or more locking screws  50  are installed through one or more corresponding fixation holes of the bone plate  10  into underlying bone, bend  40  may deform (e.g., plastically and/or elastically) toward the underlying bone portions. This can create a residual spring force compressing the ends of the bone portions together. For example, physically compressing bend  40  from an initial apex height to a reduced apex height may place to the top side of the bone plate in compression and the underside of the bone plate in tension, creating a moment force of asymmetrically distributed magnitude across the end faces of the bones being compressed. In implementations where the bone plate system is applied on a dorsal side of two bone portions (e.g., across a metatarsophalangeal joint or across a tarsometatarsal joint), this may have a tendency to plantarflex the distal bone portion relative to the proximal bone portion, thereby compressing the bone ends across the joint to promote healing (e.g., fusion) and reinforcing a joint realignment performed prior to fixation. 
       FIGS. 5, 6A and 6B  are illustrations showing an example application of bone plate  10  using first and second locking screws  50 A,  50 B.  FIG. 5  illustrates bone plate  10  positioned over a joint  74  (e.g., tarsometatarsal joint) separating a first bone portion  70  (e.g., first metatarsal) from a second bone portion  72  (e.g., medial cuneiform) prior to installation of the locking screws.  FIG. 6A  illustrates bone plate  10  after installation of first and second locking screws  50 A,  50 B.  FIG. 6B  is a force diagram schematically illustrating an example distributed load that may be applied by bone plate  10  across the joint after deformation. Bone plate  10  in  FIG. 5  is illustrated with optional drill guides screwed within the fixation holes of the bone plate. 
     During installation, bone plate  10  can be positioned across joint  74 , e.g., with the apex of bend  40  substantially centered over the joint. First fixation hole  30  may be positioned over an underlying first bone portion  70 , and second fixation hole  34  may be positioned over an underlying second bone portion  72 . For example, distal region  20  may at least partially contact first bone portion  70  and proximal region  24  may at least partially contact second bone portion  72  with bend  40  elevated above the surface of one or both bone portions. As a result, a gap  80  may exist between bone-facing surface  18  of bone plate  10  and the joint line defined by the ends of the bones underneath bend  40 . The size of gap  80  may vary, e.g., depending on the extent of bend  40 , and in some examples is at least 1 mm, such as at least 1.5 mm, at least 1.75 mm, at least 2 mm, at least 2.25 mm, at least 2.5 mm, at least 3 mm, at least 3.5 mm, at least 4 mm, or at least 5 mm. 
     The clinician may attach bone plate  10  to the first and second bone portions  70 ,  72  by inserting one or more locking screws  50 A,  50 B through one or more corresponding fixation holes of the bone plate. For example, the clinician may insert a first locking screw  50 A through first fixation hole  30  and screw the locking screw into the underlying first bone portion  70 . The clinician may continue advancing first locking screw  50 A until the head thread on the locking screw is partially but not fully engaged with the counter threading extending around first fixation hole  30  (e.g., such that the head threading on the locking screw is partially engaged with the counter threading but can continue to be advanced downwardly relative to the counter threading). If the opposite side of bone plate  10  is already secured to second bone portion  72  using a fixation element, the clinician may further screw first locking screw  50 A into first bone portion  70 . As the shaft thread of first locking screw  50 A advances down into first bone portion  70  after the head thread of the locking screw is initially engaged with the counter thread on the fixation hole, the compression ratio provided by the differential configuration of the head and shaft thread may generate a compressive force that causes bend  40  to deform towards joint  74 . 
     Depending on the order of operation, before or after installing first locking screw  50 A into first bone portion  70 , the clinician may insert a second locking screw  50 B through second fixation hole  34  and screw the locking screw into the underlying second bone portion  72 . The clinician may continue advancing second locking screw  50 B until the head thread on the locking screw is partially or fully engaged with the counter threading extending around second fixation hole  34  (e.g., such that the head threading on the locking screw is partially engaged with the counter threading but can continue to be advanced against the counter threading or is fully seated with the locking threading). The clinician may further screw second locking screw  50 B into second bone portion  72 . As the shaft thread of second locking screw  50 B advances down into second bone portion  72  after the head thread of the locking screw is initially engaged with the counter thread on the fixation hole, the compression ratio provided by the differential configuration between the head and shaft thread may generate a compressive force that causes bend  40  to deform (e.g., further deform) towards joint  74 . 
     As bend  40  of bone plate  10  deforms towards the facing surfaces of the underlying bone portions and/or joint  74 , the bend may flatten. For example, when the bend  40  is characterized by a radius of curvature, the radius of curvature may be smaller when the bend is undeformed ( FIG. 5 ) and larger when the bend is deformed ( FIG. 6A ) after installation as compared to prior to installation. In some installations, bend  40  of bone plate  10  is bowed down to the facing surface of the underlying bone portions until the bone-facing surface of the bone plate contacts the bone portions in the region formally defining the apex of the bend. In other installations, such as that shown in  FIG. 6A , bend  40  of the bone plate is bowed toward the facing surface of the underlying bone portions but a residual gap  80  remains between bone-facing surface  18  of bone plate  10  and the joint line defined by the ends of the bones underneath bend  40 . In some examples, the size of gap  80  after installation of bone plate  10  may be less than 2 mm, such as less than 1.75 mm, less than 1.5 mm, less than 1 mm, less than 0.75 mm, or less than 0.5 mm. 
     As shown in  FIGS. 5 and 6 , first fixation hole  30  and second fixation hole  34  may be oriented relative to each other such that axes extending through a geometric center of each fixation hole converge to define a converging angle  90 . After installation of screws through the first and second fixation holes  30 ,  34  angle  90  may decrease representing a flattening of bend  40 . However, the first and second fixation holes and, correspondingly, first and second screws through the fixation holes, may be angled at a converging angle relative to each other. This may be useful to help generate a force pressing an end of the first bone portion  70  against an end of the second bone portion  72 , with the force having a distributed magnitude that is greater on a portion of the bone portions opposite a side against which bone plate  10  is positioned (e.g., on an opposite cortex of the bone portions) and less on a side against which the bone plate is positioned. 
     In some examples, a difference in angle  90  prior to deformation minus angle  90  prior after deformation is 90 degrees or less, such as 60 degrees or less, 45 degrees or less, 30 degrees or less, or 20 degrees or less. For example, angle  90  prior to deformation may range from 15 degrees to 90 degrees, such as from 20 degrees to 45 degrees. After deformation, angle  90  may range from 0 degrees to 45 degrees, such as from 5 degrees to 15 degrees. In one specific example, angle  90  may be within a range from 20 to 30 degrees prior to deformation and may be in a range from 5 to 15 degrees after deformation. 
     As the bend or arch in bone plate  10  is physically deformed toward a flattened or unbent profile (e.g., resulting in a complete flattening of the plate or a residual bend or arch of smaller height after deformation), an underside of the plate may be placed in tension and a topside of the plate placed in compression. As a result, a moment force may be applied that has an asymmetrically distributed magnitude across the end faces of the bones being compressed. FIG.  6 B illustrates an example triangular distributed load profile that may be created across the end faces of the bone portions by deformation of the bone plate. An asymmetrically distributed force pressing the end faces of the bone portions together may be greater on a side (e.g., a cortex) of the bone portions opposite the side in contact with bone plate  10  than a side (e.g., a cortex) of the bone portions no the side in contact with the bone plate.  FIG. 6B  illustrates the example asymmetric force distribution with force vectors  92  of different magnitude across the depth of the joint between the two bone portions. 
     Features described as screws, including locking screw  50 , can be formed of any suitable biocompatible material or combinations of materials, such as stainless steel, nitinol, titanium, and/or polymeric materials (e.g., polyether ether ketone or PEEK). The screws may be single axial screws and/or polyaxial screws. Further, the screws may be cannulated or non-cannulated and/or may be self-tapping or non-self-tapping. In some examples, one or more of the screws are cannulated (e.g., all of the screws). In other examples, one or more of the screws are non-cannulated (e.g., all of the screws). 
     The screws, including locking screw  50 , and bone plate  10  may be sized based on the desired application for the plating system. In some examples, each screw used with bone plate  10  is sized to be inserted into a metatarsal and/or cuneiform of a human foot. For example, each screw may have a length ranging from 8 mm to 18 mm, such as from 10 mm to 16 mm, or from 12 mm to 14 mm. When provided with screws intended to be inserted into both the metatarsal and cuneiform, the screws may be the same size, or one may be longer than the other (e.g., by 1 mm, 2 mm, or more). Although the diameter of the shaft of the screws may vary, in some examples, the diameter ranges from 2 mm to 4 mm, such as from 2.5 mm to 3.2 mm. 
       FIG. 7  is a flow diagram illustrating an example technique for attaching a bone plate system according to disclosure. The technique of  FIG. 7  involves performing an optional bone realignment procedure to realign a first bone portion  70  relative to a second bone portion  72 , which is then fixated using the bone plate system ( 100 ). The bone realignment procedure may involve realigning a metatarsal relative to a cuneiform, such as a first metatarsal relative to a medial cuneiform, or may involve realigning other bone portions relative to each other. For example, the bone realignment procedure may involve realigning a second metatarsal relative to an intermediate cuneiform, a third metatarsal relative to a lateral cuneiform, a proximal phalanx relative to a metatarsal across a metatarsophalangeal joint, or yet other bone portions relative to each other. 
     To correct an alignment of a first bone portion (e.g., metatarsal) relative to a second bone portion (e.g., cuneiform), for example, the clinician may surgically access the joint between the two bone portions. Once accessed the clinician may prepare end faces of the two bone portions. The clinician can prepare the end of each bone so as to promote fusion of the bone ends across the joint following realignment. Bone preparation may involve using a tissue removing instrument to apply a force to the end face of the bone so as to create a bleeding bone face to promote subsequent fusion. Example tissue removing instruments that can be used include, but are not limited to, a saw, a rotary bur, a rongeur, a reamer, an osteotome, a curette, and the like. The tissue removing instrument can be applied to the end face of the bone being prepared to remove cartilage and/or bone. For example, the tissue removing instrument may be applied to the end face to remove cartilage (e.g., all cartilage) down to subchondral bone. Additionally or alternatively, the tissue removing instrument may be applied to cut, fenestrate, morselize, and/or otherwise reshape the end face of the bone and/or form a bleeding bone face to promote fusion. In instances where a cutting operation is performed to remove an end portion of a bone, the cutting may be performed freehand or with the aid of a cutting guide having a guide surface positionable over the portion of bone to be cut. When using a cut guide, a cutting instrument can be inserted against the guide surface (e.g., between a slot define between two guide surfaces) to guide the cutting instrument for bone removal. 
     Either before or after preparing one or both ends of the bone portions, the clinician may move one bone portion (e.g., the metatarsal) in at least one plane, such as at least the transverse plane to close an intermetatarsal angle between the bone portion (e.g., a first metatarsal) and an adjacent bone (e.g., a second metatarsal) and/or a frontal plane to reposition the sesamoid bones. In some examples, the clinician moves the bone portion in multiple planes, such as the transverse plane and/or frontal plane and/or sagittal plane. The clinician may or may not utilize a bone positioning guide to facilitate movement of the bone portion. With the bone portion moved to a desired position, the clinician can optionally provisionally fixate the moved position (e.g., by inserting a k-wire through the moved bone portion into an adjacent bone portion) and then permanently fixate the moved position using one or more bone plate systems as described herein. Details on example bone realignment instruments and techniques that can be used in conjunction with the present disclosure are described in U.S. Pat. No. 9,622,805, issued Apr. 18, 2017 and entitled “BONE POSITIONING AND PREPARING GUIDE SYSTEMS AND METHODS,” the entire contents of which are incorporated herein by reference. 
     In some applications, independent of whether the clinician performs the specific bone realignment technique discussed above, the clinician temporarily or provisionally fixates first bone portion  70  relative to second bone portion  72  prior to attaching bone plate  10  across the joint separating the two bone portions. The clinician may press the end faces of first bone portion  70  and second bone portion  72  together, e.g., with hand pressure and/or using compressing instrument physically attached to both the first bone portion and the second bone portion. For instance, the clinician may attach compressing instrument to the first bone portion  70  with one or more fixation pins and also attach the compressing instrument to the second bone portion using one or more fixation pins. The compressing instrument may have a mechanism (e.g., threaded rod, rack and pinion) that presses against the pins inserted through the two bone portions to compress the end faces of the two bone portions together. Additional details on example compressing instruments that may be used can be found in US Patent Publication No. 2020/0015856, published Jan. 16, 2020 and entitled “COMPRESSOR-DISTRACTOR FOR ANGULARLY REALIGNING BONE PORTIONS,” the entire contents of which are incorporated herein by reference. 
     In some implementations, the clinician inserts one or more fixation pins through the end faces of the first bone portion  70  and second bone portion  72  in addition to or in lieu of compressing the end faces with a compressing instrument. The fixation pin may be a k-wire, olive wire (e.g., pin with region of enlarged cross-section) or other fixation pin structure. The fixation pin crossing joint  74  between first bone portion  70  and second bone portion  72  can help provisionally fixate and/or compress the end faces of the two bone portions together prior to installation of bone plate  10  for permeant fixation (and subsequent fusion of the bone faces together). When used, the one or more fixation pins can be removed from the end faces of the two bone portions and across the joint between the bone portions after installation of bone plate  10  (e.g., after installation of at least one fixation element through the bone plate into each of first bone portion  70  and second bone portion  72 ). 
     With further reference to  FIG. 7 , the example technique includes positioning a bone plate  10  across a joint separating two bone portions ( 102 ). The bone plate  10  can include first fixation hole  30 , second fixation hole  34 , and bend  40  between the first fixation hole and the second fixation hole. Positioning the bone plate across the joint may involve positioning bend  40  over the joint, e.g., with distal region  20  of the bone plate contacting the first bone portion and the proximal region  24  of the bone plate contacting the second bone portion. As a result of the presence of the bend, a gap  80  may exist between the bone facing surface  18  of the bone plate and the underlying surfaces and/or joint of the bone ends. 
     The technique of  FIG. 7  may also involve inserting a locking screw  50  through a first fixation hole of the bone plate ( 104 ). The locking screw  50  can have a head with a head thread and a shaft with a shaft thread. The shaft thread may be configured relative to head thread to provide a compression ratio greater than 1.0, such as greater than 1.5. The head thread may be configured (e.g., size and/or shaped) to engage with corresponding counter threading encircling the first fixation hole. The clinician may insert the locking screw through the first fixation hole by advancing the distal end of the screw through the opening defined by the first fixation hole and beginning to screw the shaft of the locking screw into the underlying bone. In different examples, a hole may or may not be predrilled into the bone prior to insertion of the screw. 
     With the distal end of locking screw  50  inserted through the first fixation hole of bone plate  10 , the clinician can screw the locking screw into the underlying bones ( 106 ). Operating under hand power or with the aid of a rotary drill instrument, the clinician can rotate locking screw  50  in either a clockwise or counterclockwise direction (depending on the pattern of the thread) so as to advance the screw axially downwardly into the bone portion underlying the fixation hole in the bone plate. The clinician can continue screwing locking screw  50  and advancing the screw axially into the bone portion. When the head thread on the head of locking screw contacts the counter threading encircling the first fixation hole, the head thread may interleave with the counter threading encircling the first fixation hole thereby engaging the threading. 
     With the head thread at least partially engaged with the counter thread defined by the first fixation hole, the technique of  FIG. 7  involves further screwing locking screw  50  into the first fixation hole and into the underlying bone. When the bone plate  10  is already affixed to the other bone portion across the joint, further rotation of locking screw  50  may cause the bone plate (e.g., bend  40  in the bone plate) to deform. The bone plate may deform by bowing toward the joint and underlying bones. 
     Prior to and/or after installing locking screw  50  through the first fixation hole of the bone plate, the clinician can install one or more fixation elements, such as one or more locking screws through one or more additional fixation holes of the bone plate. For example, prior to or after installing locking screw  50  through the first fixation hole into the first bone portion, the clinician may install another locking screw (which may or may not have a comparatively high compression ratio) through the second fixation hole into the second bone portion. The clinician may install one or more additional screws, such as one or more additional locking screws (which may or may not have a comparatively high compression ratio) through other fixation holes in the bone plate, such as a third fixation hole and a fourth fixation hole. 
     A bone plating system applied across a joint separating the ends of two bone portions as described herein can help compress the end faces of the two bone portions together to facilitate fusion. In some examples, the plating system produces asymmetric compression in which the far cortex of the bone ends is compressed more than the near cortex. In some applications, such as when the bone plate is applied to the dorsal surface of the bone portions, this can help plantarflex the realigned bone portion and reinforce a corrective realignment in the sagittal plane while facilitating fusion. Additionally or alternatively, when the bone plate is applied to the medial surface of the bone portions, this can help laterally bias the realigned bone portion and reinforce a corrective realignment in the transverse plane (e.g., bias toward closing the intermetatarsal angel) while facilitating fusion. 
     A variety of different instruments and additional or alternative techniques can be used to facilitate installation of a bone plating system as described herein. For example, one or more driving pins (e.g., plate tack pins, drill pins) may be used to help facilitate installation of bone plate  10 . When used, the driving pin may be inserted through a fixation hole of the bone plate and into the underlying bone. In some examples, the driving pin includes a threaded distal region and can be rotationally driven into the underlying bone via screwing. In either case, the driving pin may enter or bore a hole in the bone portion underlying the fixation hole through which the driving pin is inserted. 
     In some implementations, the driving pin may include an enlarged region having a larger cross-sectional area than a cross-sectional area of the fixation hole. As the driving pin is advanced into the underlying bone, the region of larger cross-sectional area may press against a top side of bone plate  10  (e.g., either directly against the top side or indirectly via a drill guide extending above the top surface). Continued rotation of the driving pin may cause the enlarged cross-sectional area to deform bend  40  by compressing the bend portion toward the underlying joint and/or surfaces of the bone portions. As a result, the bone plate may be partially or fully deformed toward a desired degree of compression by the driving pin. The driving pin can then be removed from the fixation hole and a locking screw inserted through the fixation hole and into the underlying bone. Another fixation device, such as a pin, screw, etc. may be placed through one or more adjacent holes prior to removing the driving pin to help hold the compression of the bone plate for installation of the locking screw. 
     When bone plate  10  is pre-deformed using a driving pin prior to installation of one or more screws, the screws used to affix the bone plate to the underlying bone portions may or may not include locking screw  50  exhibiting a comparatively high compression ratio. In some applications using a driving pin for pre-deformation, at least one (and optionally all) fixation elements used to secure the deformed bone plate to the underlying bone may be non-locking screws or locking screws configured with a lower compression ratio (e.g., one not effective to substantially deform the plate upon installation, such as compression ratio less than 1.5, or a compression ratio of 1.0). That said, in some implementations, locking screw  50  with an enhanced compression ratio may be installed (e.g., through one or both fixation holes closest to joint  74 ) to help affix the bone plate to the underlying bone portions. 
       FIG. 8  is side view of an example driving pin  120  that can be used to help install a bone plate on a bone. For example, driving pin  120  may be connected to a driver (e.g., impact driver, rotary driver, drill) that uses driving pin  120  to impart a force for opening a hole in a bone underlying a bone plate. Additionally or alternatively, a clinician utilizing driving pin  120  can apply a force through a hand-powered instrument to drive the driving pin. In either case, after creating the hole and/or orienting the bone plate using driving pin  120 , the driving pin can be removed from the bone and bone plate. A bone fixation member (e.g., bone screw) can then be inserted into the opening created by driving pin  120  to permanently hold the bone plate to the bone. 
     In the illustrated example, driving pin  120  defines a body that extends from a proximal end  122  to a distal end  124 . The body defines multiple regions of different cross-sectional thickness which, in the illustrated example, is shown as at least three regions of different cross-sectional thickness. For example, the body of driving pin  120  may define a bone penetrating region  126  adjacent the distal end, a driving region  128  adjacent the proximal end, and bone plate orienting region  130  between the bone penetrating region and the driving region. Bone penetrating region  126  can have a smaller cross-sectional thickness than the bone plate orienting region  130 . Bone plate orienting region  130  may have a smaller cross-sectional thickness than driving region  128  or, in other implementations, can have the same cross-sectional thickness or a larger cross-sectional thickness than driving region  128 . 
     Configuring driving pin  120  with multiple cross-sectional thicknesses can be useful to provide different functionalities while limiting unnecessary trauma to the bone in which the driving pin is engaged. For example, bone penetrating region  126  can be sized comparatively small to minimize bone damage and ease insertion of the distal end of the driving pin. Bone plate orienting region  130  may be larger and be sized complementary to the dimeter of a fixation hole of the bone plate in which the driving pin is to be inserted. This can provide close conformance between the driving pin and the bone plate, e.g., for accurately rotating the bone plate about the driving pin to orient the bone plate during installation. Driving region  128  may be larger and sized for engagement with a driver to be used in the process. In some configurations, driving pin  120  is provided as part of a kit that includes other driving instruments (e.g., pins, k-wires) and has the same diameter as one or more of those other instruments to provide a uniform driving connection size across the instruments. In other words, driving pin  120  may be part of a kit (e.g., where all the components of the kit art contained in a sterile case) having one or more (and optionally two or more) other instruments, each having a substantially same diameter shaft and each being configured to couple to a same driver for driving the instruments. 
     As shown in  FIG. 8 , bone penetrating region  126  may be threaded to facilitate rotationally driving (screwing) the driving pin into the underlying bone. When threaded, the threading on bone penetrating region  126  may define any suitable pitch which may be the same as, or different than, the pitch on the shaft thread of locking screw  50  that can be inserted through the fixation hole after removal of the driving pin. Distal end  124  of driving pin  120  may have a trocar or other tip (e.g. self-tapping tip) for starting penetration of driving pin  120  into the underlying bone. 
     Although driving pin  120  is illustrated as including a threaded bone penetrating region  126  and an unthreaded plate orienting region  130 , the driving pin need not have the two distinct regions. Rather, when bone penetrating region  126  and plate orienting region  130  are configured with the same cross-sectional size, the threading may optionally extend to also encompass the region of the driving pin that functions as the plate orienting region. 
     In general, driving pin  120  can have any have desired cross-sectional shape, including polygonal shapes, arcuate shapes, and combinations thereof. In some configurations, at least bone penetrating region  126 , driving region  128 , and bone plate orienting region  130  of the driving pin have a circular cross-sectional shape. 
     While driving pin  120  have a variety of different sizes, in some examples, bone penetrating region  16  has a diameter ranging from 0.1 mm to 2 mm and/or bone plate orienting region  130  has a diameter ranging from 0.5 to 3 mm and/or driving region  128  has a diameter ranging from 1.6 mm to 3.7 mm. For example, bone penetrating region  126  may have a diameter ranging from 1 mm to 2 mm, and bone plate orienting region  130  may have a diameter ranging from 1 mm to 2 mm. 
     Driving pin  120  can have one or more regions of different cross-sectional thickness than bone penetrating region  126 , driving region  128 , and bone plate orienting region  130 . For example, in the illustrated example, driving pin  120  includes a fourth region  132  of greater cross-sectional thickness than at least bone penetrating region  126  and bone plate orienting region  130 . In the illustrated configuration, fourth region  132  also has a cross-sectional thickness greater than driving region  128 . Fourth region  132  is positioned proximally of bone plate orienting region  130  and can have a cross-sectional thickness greater than that of a bone plate fixation hole diameter and/or drill guide into which driving pin  120  is configured to be inserted. Fourth region  132  can function as a feature that limits that downward insertion depth of driving pin  120  as it is being inserted through a bone plate and/or drill guide. When included, fourth region  132  may be integral (e.g. permanently formed with) a remainder of the driving pin body or may be part of a multi-piece assembly that is separately attachable to the driving pin. 
     Fourth region  132  can have any desired cross-sectional shape (e.g., round, spherical, rectangular, triangular, elliptical), and the cross-sectional shape may be the same as or different than that of adjacent sections of the driving pin. In some examples, fourth region  132  has a cross-sectional thickness ranging from 1.5 mm to 12 mm, such as from 2 mm to 5 mm. Additional details on example driving pin techniques and devices that may be used are described in US Patent Publication No. 2020/0015870, filed Jul. 12, 2019 and titled “MULTI-DIAMETER BONE PIN FOR INSTALLING AND ALIGNING BONE FIXATION PLATE WHILE MINIMIZING BONE DAMAGE, the entire contents of which are incorporated herein by reference. 
       FIG. 9  is a side view of bone plate  10  illustrating driving pin  120  inserted through a second fixation hole  34  of the bone plate. In the illustrated configuration, a drill guide  140  is threaded into the threaded opening defined by the fixation hole. As shown in this example, the thread encircling the bone penetrating region terminates at the proximal end prior to where the driving pin intersects the bone plate, when the driving pin is fully inserted and the enlarged region is bearing against the drill guide (or, in other configurations, the top surface of bone plate itself). 
       FIGS. 10-15  are perspective illustrations showing example procedure steps that may be used to install a bone plate to two bone portions separated by a joint according to the disclosure. In particular,  FIGS. 10-15  illustrate example procedure steps for attaching bone plate  10  to a medial cuneiform  70  and a first metatarsal  72  separated by a tarsometatarsal joint, e.g., after performing preparation on the ends of the two bones and realigning the first metatarsal relative to the cuneiform and/or provisionally fixating the bone portions together. 
     As shown in  FIG. 10 , bone plate  10  can be positioned across the tarsometatarsal joint separating a metatarsal  72  from cuneiform  70 . In the illustrated orientation, bone plate  10  is positioned on the dorsal side of the two bones (e.g., dorsal-most half, dorsal-most quarter). In other applications, bone plate  10  may be positioned at other locations along the surface of the two bones, such as a medial side of the two bones (e.g., medial-most half, medial-most quarter), and/or on a dorsal-medial side of the two bones. 
     Continuing with  FIG. 11 , a first driving pin  120 A can be inserted through a first fixation hole  30  positioned closest to a region of bone plate  10  defining an apex of the bend. Driving pin  120 A can be rotationally driven through the first fixation hole into an underlying bone (cuneiform  70 ). As the driving pin bores axially down into the bone, the enlarged region of the driving pin can contact the top surface of the bone plate (e.g., the top surface of the drill guide extending above the bone plate). Continued rotation of driving pin  120 A can cause the enlarged region of the driving pin to press against the bone plate and at least partially deform the bend by compressing the bend, resulting in a comparative flattening of the bone plate. 
     As shown in  FIG. 12 , a second driving pin  120 B can be inserted through a second fixation hole  34  positioned on an opposite side of the joint from first driving pin  120 A. Second fixation hole  34  may be positioned closest to the region of bone plate  10  defining an apex of the bend on the opposite side of first fixation hole  30 . Second driving pin  120 B can be rotationally driven through the second fixation hole into an underlying bone (metatarsal  72 ). Again, as the driving pin bores axially down into the bone, the enlarged region of the driving pin can contact the top surface of the bone plate (e.g., the top surface of the drill guide extending above the bone plate). Continued rotation of driving pin  120 B can cause the enlarged region of the driving pin to press against the bone plate, further deforming the bend in the bone plate initially deformed upon insertion of the first driving pin  120 A. Complete insertion of second driving pin  120 B may complete deformation of bone plate  10  to a desired degree of compression. 
     To retain bone plate  10  for insertion of a screw, a third fixation pin  150  can be inserted into an adjacent fixation hole of the bone plate to the fixation hole in which the screw is desirably inserted, as shown in  FIG. 13 . In this example, third fixation pin  150  is inserted through third fixation hole  32  of bone plate  10  into the underlying bone. Third fixation pin can be configured the same as driving pin  120  or can be a different configuration of pin such as, e.g., a threaded plate tack, in olive drive, or other pin. Third fixation pin  150  can be applied to hold the deformation and compression of bone plate  10  (and the position of the bone plate). In other examples, the technique may proceed without installation of third fixation pin  150 . First driving pin  120 A may be removed while second fixation pin  120 B (or a screw through the opposite fixation hole) remains in place. 
     In either case, first driving pin  120 A can be removed from first fixation hole  30  to open the fixation hole for installation of a locking screw, as illustrated in  FIG. 14 . After first driving pin  120 A is removed, a locking screw  50  (or other type of fixation element as described herein) can be screwed through first fixation hole  30  into the underlying bone. 
     With locking screw  50  installed through first fixation hole  30  to secure bone plate  10  to cuneiform  70 , third fixation pin  150  (when used) can be removed from the cuneiform. In addition, second driving pin  120 B can be removed from metatarsal  72  and a screw screwed through second fixation hole  34  to secure the bone plate to the metatarsal. The screw inserted through second fixation hole  34  can be locking screw  50  or a different type of screw structure or other fixation element as described herein. In some examples, a fixation pin (e.g., third fixation pin  150 ) is inserted through fourth fixation hole  36  before removing second driving pin  120 B. 
       FIG. 15  illustrates bone plate  10  attached across the tarsometatarsal joint separating medial cuneiform  70  from first metatarsal  72 . The bone plate is attached to medial cuneiform  70  and first metatarsal  72  with screws inserted through first and second fixation holes  30 ,  34  of the bone plate. Depending on the configuration of bone plate  10  in the procedure being undertaken, the clinician may proceed to complete attachment of the bone plate, e.g., by installing screws through third fixation hole  32  and fourth fixation hole  36  into the underlying bones. 
     In some applications, however, the clinician may desire to install multiple bone plates across the joint rather than only installing a single bone plate. The multiple bone plates may be positioned at different locations about the perimeter of the joint so as to provide a biplanar plating construct. In these applications, each bone plate and/or screws may be configured and installed according to the present disclosure, or one bone plate system may be different than the other bone plate system. In some such applications, the clinician may proceed to begin installing the second bone plate before completing installation of the first bone plate. For example, the clinician may proceed to begin installing the second bone plate after securing the first bone plate through the first and second fixation holes  30 ,  34  but prior to installing screws through other fixation holes (e.g., the third and/or fourth fixation holes  32 ,  36 ). 
     For example,  FIGS. 16-22  illustrate example procedural steps that may be performed before, after, or in lieu of the procedure steps described with respect to  FIGS. 10-15 . As shown in  FIG. 16 , a bone plate  10 B can be positioned across the tarsometatarsal joint separating a metatarsal  72  from cuneiform  70 . In the illustrated orientation, bone plate  10 B is positioned on the medial side of the two bones (e.g., medial-most half, medial-most quarter) although can be positioned at other locations about the bones. 
     Continuing with  FIG. 17 , a first driving pin  120 A can be inserted through a first fixation hole  30  positioned closest to a region of bone plate  10 B defining an apex of the bend. Driving pin  120 A can be rotationally driven through the first fixation hole into an underlying bone (cuneiform  70 ). As the driving pin bores axially down into the bone, the enlarged region of the driving pin can contact the top surface of the bone plate (e.g., the top surface of the drill guide extending above the bone plate). Continued rotation of driving pin  120 A can cause the enlarged region of the driving pin to press against the bone plate and at least partially deform the bend by compressing the bend, resulting in a comparative flattening of the bone plate. 
     As shown in  FIG. 18 , a second driving pin  120 B can be inserted through a second fixation hole  34  positioned on an opposite side of the joint from first driving pin  120 A. Second fixation hole  34  may be positioned closest to the region of bone plate  10  defining an apex of the bend on the opposite side of first fixation hole  30 . Second driving pin  120 B can be rotationally driven through the second fixation hole into an underlying bone (metatarsal  72 ). Again, as the driving pin bores axially down into the bone, the enlarged region of the driving pin can contact the top surface of the bone plate (e.g., the top surface of the drill guide extending above the bone plate). Continued rotation of driving pin  120 B can cause the enlarged region of the driving pin to press against the bone plate, further deforming the bend in the bone plate initially deformed upon insertion of the first driving pin  120 A. Complete insertion of second driving pin  120 B may complete deformation of bone plate  10 B to a desired degree of compression. 
     To retain bone plate  10  for insertion of a screw, a third fixation pin  150  can be inserted into an adjacent fixation hole of the bone plate to the fixation hole in which the screw is desirably inserted, as shown in  FIG. 19 . In this example, third fixation pin  150  is inserted through third fixation hole  32  of bone plate  10  into the underlying bone. Third fixation pin can be configured the same as driving pin  120  or can be a different configuration of pin such as, e.g., a threaded plate tack, in olive drive, or other pin. Third fixation pin  150  can be applied to hold the deformation and compression of bone plate  10 B (and the position of the bone plate). In other examples, the technique may proceed without installation of third fixation pin  150 . First driving pin  120 A may be removed while second fixation pin  120 B (or a screw through the opposite fixation hole) remains in place. 
     In either case, first driving pin  120 A can be removed from first fixation hole  30  to open the fixation hole for installation of a locking screw, as illustrated in  FIG. 20 . After first driving pin  120 A is removed, a locking screw  50  (or other type of fixation element as described herein) can be screwed through first fixation hole  30  into the underlying bone. 
     With locking screw  50  installed through first fixation hole  30  to secure bone plate  10  to cuneiform  70 , third fixation pin  150  (when used) can be removed from the cuneiform. In addition, second driving pin  120 B can be removed from metatarsal  72  and a screw screwed through second fixation hole  34  to secure the bone plate to the metatarsal. The screw inserted through second fixation hole  34  can be locking screw  50  or a different type of screw structure or other fixation element as described herein. In some examples, a fixation pin (e.g., third fixation pin  150 ) is inserted through fourth fixation hole  36  before removing second driving pin  120 B. 
       FIG. 21  illustrates bone plate  10 B attached on the dorsal side across the tarsometatarsal joint separating medial cuneiform  70  from first metatarsal  72 . The bone plate is attached to medial cuneiform  70  and first metatarsal  72  with screws inserted through first and second fixation holes  30 ,  34  of the bone plate. 
     Securing a first bone plate  10  with a single screw connecting the bone plate to an underlying bone portion (e.g., metatarsal  72 ) and then attaching the second bone plate  10 B prior to completing attachment of the first bone plate  10  may be useful for a variety of reasons. With only a single screw securing the first bone plate  10  to the bone portion, the bone portion may be further manipulable during installation of the second bone plate  10 B. For example, the clinician may be able to pivot metatarsal  72  around the single screw connecting the first bone plate  10  to the metatarsal. This can provide some degree of mobility or freedom for the clinician to adjust the position of the first metatarsal in the transverse plane, frontal plane, and/or sagittal plane prior to or concurrent with attaching the second bone plate  10 B. Additionally or alternatively, this arrangement provides mobility to allow the bend  40  in the second bone plate  10 B (when so configured) to be deformed to provide additional reinforcing correction of the bone portion (e.g., biasing the metatarsal laterally to close the intermetatarsal angle). 
     Once second bone plate  10 B is attached to medial cuneiform  70  and first metatarsal  72  with screws inserted through first and second fixation holes  30 ,  34  of the bone plate, the clinician can proceed to complete attachment of the first bone plate  10  and/or second bone plate  10 B. For example, the clinician may install screws through third fixation hole  32  and fourth fixation hole  36  of the first bone plate  10  and/or second bone plate  10 B into the underlying bones to complete installation as shown in  FIG. 22 . 
     It should be appreciated that the foregoing discussion of example procedural steps described in connection with  FIGS. 10-22  our exemplary and the procedure may be varied according to disclosure. For example, a clinician may attach a medial bone plate prior to attaching a dorsal bone plate or may only attach a single bone plate. As another example, the clinician may insert an initial driving pin and/or locking screw through a first fixation hole into the first metatarsal  72  instead of the medial cuneiform  70  as discussed in the example. As a still further example, the installation procedure may be modified to incorporate one or more additional fixation elements that can be used in addition to or in lieu of the described bone plating system and techniques. Example additional fixation elements that may be used include, but are not limited to, a lag screw, pin, and/or staple that is inserted across the separation between the two bone portions, such as across the tarsometatarsal joint (e.g., through the first tarsometatarsal joint and into the second metatarsal) and/or a staple that is inserted across the tarsometatarsal joint. 
     In instances where a bone plating system according to the disclosure is applied to both a dorsal side and a medial side of a metatarsal and cuneiform, the two bone plates may reinforce a realignment introduced during a bone realignment procedure. For example, bone plate attached the dorsal side of the metatarsal and cuneiform may apply an asymmetrically distributed force that is greater on the plantar side of the joint than the dorsal side of the joint, which may have a tendency to plantarflex the metatarsal. The bone plate attached the medial side of the metatarsal and cuneiform may apply an asymmetrically distributed force that is greater on the lateral side of the joint than the medial side of the joint, which may have a tendency to bias the distal end of the metatarsal laterally to close an intermetatarsal angle between the metatarsal to which the bone plate is attached and an adjacent metatarsal. 
     As described above, bone plate  10  may be positioned over two bone portions to be fixated together with the plate. The bone plate may be positioned over the bone portions in an undeformed state, e.g., prior to compressing bend  40 . Once positioned over one or both bone portions, the bone plate can be deformed, for example, by inserting one or more locking screws and/or driving pins or equivalent compressive threaded elements through the fixation hole(s) of the bone plate. This can cause the bend in the bone plate to deform toward a more flattened profile. 
     In yet additional examples, bone plate  10  with bend  40  may be pre-tensioned (e.g., pre-compressed) before or concurrent with being positioned over a joint between two adjacent bone portions to be fixated. For example, using hand manipulation and/or a bending instrument, bend  40  of the plate may be compressed toward a more planar shape and held in compression while placed spanning the join between the bone portions being fixated. While held in compression, one or more driving pins and/or fixation elements (e.g., screws) can be inserted through the fixation holes of the bone plate into the underlying bone portions. 
     In these examples, bone plate  10  may have a configuration and may be deformed according to any of the shape profiles and configurations discussed above, albeit with the deformation occurring at least partially prior to attachment of the bone plate to one or both underlying bone portions. In these applications, at least one (and optionally all) fixation elements used to secure the pre-deformed bone plate to the underlying bone portion(s) may be non-locking screws or locking screws configured with a lower compression ratio (e.g., one not effective to substantially deform the plate upon installation, such as compression ratio less than 1.5, or a compression ratio of 1.0). That said, in some implementations, locking screw  50  with an enhanced compression ratio may be installed (e.g., through one or both fixation holes closest to joint  74 ) to help affix the pre-deformed bone plate to the underlying bone portions. 
       FIGS. 23 and 24  show one example implementation in which an instrument is used to pre-deform bone plate  10  prior to installation.  FIG. 23  illustrates bone plate  10  connected to a bending instrument  160  prior to compression which, in the illustrated example, is shown as plate bending arms. The plate bending arms  160  are inserted through drill guides  140  and/or fixation holes of the bone plate on opposite sides of bend  40 . The handles can be squeezed together as shown in  FIG. 24  to deform the bend in bone plate  40  and pre-compress the bone plate. The handles can be squeezed together in a direction indicated by force vector arrows  162 , e.g., with one hand of the clinician grasping both handles and squeezing them together. 
     Once pre-compressed, the comparatively flat plate can be positioned over the two bone portions to be fixated together and held to one or both bone portions with a driving pin or other fixation feature. Plate bending arms  160  can then be removed, the screw holes prepared, and screws plated through the fixation holes of the plate and into underlying bone. 
     When bone plate  10  is pre-compressed prior to installation, the screws used to fixate the plate to the underlying bone portions may or may not include a locking screw  50  as described above with comparatively high compression ratio. In some implementations, all the screws utilized to fixate the bone plate to the underlying bone portions may be non-locking screws or locking screw with lower compression ratio. 
     In some implementations, the components of the bone plate systems described herein (e.g., one or more bone plates, screws and/or other fixation elements) may be provided as part of a kit. The kit may be a disposable single-use surgical kit. The terms “disposable” and “single-use” are meant to convey that the surgical kit, in addition to all components included in the surgical kit, is intended for use on only one surgical patient. After the surgical procedure on the one surgical patient is completed, any components that are not implanted into the one surgical patient can be discarded using conventional methods. 
     The kit can include a sterile container in which various surgical items can be contained. The container can be sterilized using any appropriate sterilizing means (e.g., exposure to ethylene oxide, steam autoclave, gamma radiation). In one example, the various surgical items can be placed into the container, and the container and the various surgical items included in the container can be sterilized in a single step. The sterile container may be partially or wholly enclosed in a packaging that can serve to protect the container as well as seal and maintain a sterility of the container. The packaging and/or the sterile container can be made of a transparent material, such as an appropriate polymer, to allow viewing of the surgical items included in the container. 
     The disposable single-use kit can include all or any combination of one or more of the described surgical items. The items to be included in the kit may vary depending on the specific surgical procedure for which the kit is intended to be used. Other embodiments of the kit can include two or more sterile packages with different components in each sterile package. For example, a first sterile package containing the bone plates, fasteners, and pins may be provided along with a second sterile package containing instruments such as plate manipulation and/or bone preparation instruments. Such a kit can also be provided in modular form with components grouped together in separate sterile packages to be selected to provide a complete kit for the desired surgical procedure. 
     Various examples have been described. These and other examples are within the scope of the following claims.