referring now to the drawings , and more particularly to fig1 , there is shown an orthopaedic implant 30 which generally includes a base device 32 and a fixation material 34 attached to the base device 32 . the base device 32 shown is a bone pin that can reside within a patient for a short period of time . the base device 32 can be constructed of metals commonly used in orthopaedic implants such as titanium , cobalt chrome and stainless steel . alternatively , the base device can be constructed of biocompatible polymers such as polyether ether ketone ( peek ), polylactic acid ( pla ), polyglycolic acid ( pga ), polyethylene ( pe ) and blends thereof . the fixation material 34 attached to the base device 32 is shaped as a thin band wrapped around the circumference of the base device 32 . the fixation material 34 can be a porous polymer or metal that has a roughened surface 36 to provide immediate fixation of the device 30 due to frictional forces and to encourage quick tissue ingrowth into the fixation material 34 . the roughened surface 36 can have customized surface properties for a specific tissue type and desired tissue ingrowth amount or rate . such surface properties can include a surface energy density , wettability and electrostatic charge . polymers and metals that can act as the fixation material 34 include peek , pla , pga , pe , titanium , cobalt chrome and stainless steel . pores 38 of the fixation material 34 can be sized to allow or prevent ingrowth of tissue into the fixation material 34 . additionally , biologically active substances can be included in the pores 38 to encourage or limit tissue ingrowth into the fixation material 34 , as well as provide other useful properties such as antimicrobial activity to reduce the risk of infection . as the orthopaedic implant 30 is a small diameter bone pin that will likely be removed within a few weeks of implantation , a strong interface between surrounding tissue and the orthopaedic implant 30 is undesirable as it will cause removal of the orthopaedic implant 30 to be unnecessarily difficult . as can be seen in fig2 and 3 , only a relatively small band of fixation material 34 is necessary to provide a minimally sufficient adhesive force that will resist pull out of the orthopaedic implant 30 while it is implanted in a patient while not causing excessive adhesive force that could make the device 30 difficult to remove . as shown in fig3 , the fixation material 34 has a relatively low thickness t ( 0 . 010 ″) and a width w (“ 0 . 050 ”) significantly greater than the thickness t . for the orthopaedic device 30 shown , a thickness t range of about 0 . 005 ″ to 0 . 015 ″ and a width w range of about 0 . 020 ″ to 0 . 125 ″ can be appropriate dimensions for the fixation material 34 shaped as a band to provide the minimally sufficient adhesive force . it is also contemplated that there can be multiple fixation materials attached to the base device 32 , which would alter the dimensions of each fixation material region . an additional design consideration when shaping and placing the fixation material 34 on a small diameter pin is that the pin won &# 39 ; t provide much leverage to apply torque and overcome the adhesive force provided by the fixation material 34 . referring now to fig4 and 5 , an orthopaedic implant 40 is shown which includes a base device 42 , shown here as a large diameter pin , with a fixation material 44 attached to the pin 42 . the fixation material 44 can be the same as the fixation material 34 described previously . when utilizing a large diameter pin 42 , the amount and geometry of the fixation material 44 will need to be changed to provide a minimally sufficient adhesive force that will resist natural pull out of the pin 42 , due to increased size of the pin 42 . as shown in fig4 and 5 , the fixation material 44 can be shaped as a band around the circumference of the pin 42 , similar to the previously described small diameter pin 32 . the band of fixation material 44 can have a thickness t ranging from about 0 . 015 ″ to 0 . 050 ″ and a width w ranging from about 0 . 020 ″ to 0 . 125 ″. as can be seen in fig5 , the pin 42 can also have a groove 46 formed on the outer surface 48 of the pin 42 where the fixation material 44 attaches to the pin 42 . the groove 46 can have a varying depth that changes how proud an outer surface 50 of the fixation material 44 is relative to the outer surface 48 of the pin 42 . as seen in fig5 , the fixation material 44 has a thickness t of 0 . 020 ″, but the outer surface 50 only elevates 0 . 010 ″ relative to the outer surface 48 of the pin 42 . having the groove 46 in the pin 42 allows for a thicker fixation material 44 , which will increase the potential bone ingrowth and adhesive force , with a smaller increase in the overall diameter of the device 40 . the groove 46 also provides more surface area of the pin 42 to utilize for attachment to the fixation material 44 . as opposed to a small diameter pin , a large diameter pin can have a larger minimally sufficient adhesive force but still be easily removed because the large diameter pin 42 provides more leverage to apply torque and overcome the adhesive force provided by the fixation material 44 . referring now to fig6 and 7 , an orthopaedic implant 60 is shown which includes a base device 62 , shown as a bone screw , and a fixation material 64 attached to the bone screw 62 . the bone screw 62 can be constructed of biocompatible metals and polymers , similar to previously described base devices , and the fixation material 64 can be made of a material similar to that of previously described fixation materials . the bone screw 62 has a head end 66 , a distal end 68 and a plurality of threads 70 formed on a surface 72 of the bone screw 62 . the fixation material 64 forms a small patch on the distal end 68 of the bone screw 62 . the threads 70 of the bone screw 62 will provide some adhesive force to keep the bone screw 62 in place during implantation , so the fixation material patch 64 acts to provide additional adhesive force at the distal end 68 , if necessary , to resist natural pull out of the bone screw 62 . referring now to fig8 , an orthopaedic implant 80 is shown which includes a bone screw 62 similar to that shown in fig6 and 7 having a fixation material 82 attached to the distal end 68 of the bone screw 62 . the fixation material 82 can be formed from any fixation material previously described . in this embodiment , the fixation material 82 is formed as a “ dot ” of material on the distal end 68 of the bone screw 62 to provide additional adhesive force to the bone screw 62 . referring now to fig9 and 10 , an orthopaedic implant 90 is shown which includes a bone screw 92 similar to that shown in fig6 , 7 and 8 having a fixation material 94 attached to a surface 96 of the bone screw 92 between threads 98 formed on the surface 96 of the bone screw 92 . the fixation material 94 can be formed from any fixation material previously described . as can be seen , the fixation material 94 has a helical shape that wraps around the circumference of the bone screw 92 between the threads 98 . in this configuration , the fixation material 94 provides a substantial amount of adhesive force to resist natural pull out of the device 90 . such a configuration may be desirable for bone screws that are intended to have a longer implantation period , where additional fixation of the bone screw is desirable . referring now to fig1 and 12 , an orthopaedic implant 100 is shown which includes a bone screw 101 similar to that shown in fig6 , 7 , 8 and 9 having a fixation material 102 attached near a distal end 103 of the bone screw 101 between the distal end 103 and threads 104 and 106 . the fixation material 102 can be formed from any fixation material previously described . this configuration allows for the fixation material 102 to provide less fixation force than orthopaedic implant 90 , previously described . such a configuration is better suited for bone screws that are intended to have shorter implantation periods , where too much additional fixation of the bone screw would make removal unnecessarily difficult . referring now to fig1 and 14 , an orthopaedic implant 110 is shown which includes a base device 112 , shown as a bone screw , with holes 114 formed through a surface 116 of the bone screw 112 between threads 118 . the holes 114 are located axially in valleys 120 between the threads 118 and go through to the centerline of the screw 112 . the holes 114 can be placed along the full length of the screw 112 . the screw 112 is a cannulated screw having an inner chamber 120 that has a fixation material 122 bonded inside the inner chamber 120 . by having holes 114 and the fixation material 122 inside the inner chamber 120 , tissue will be chemoattracted to the fixation material 122 and fill in the holes 114 , forming a strong interface with the orthopaedic implant 110 . a wall thickness ( not shown ) between the minor diameter of the bone screw 112 and the inner wall of the inner chamber 120 should be in a range of approximately 1 mm to 1 . 5 mm . studies have shown that bone will bridge a gap of approximately 1 mm to 1 . 5 mm to grow into a porous material , such as the fixation material 122 . fig1 and 16 show a similar embodiment , with fewer holes 114 formed through the bone screw 112 and the holes 114 being concentrated near a distal end 126 of the bone screw 112 . referring now to fig1 , a base device 130 is shown before and after being prepared into an orthopaedic implant 132 of the present invention . as can be seen , the base device 130 is a screw blank that has had elongated pockets 134 machined within . these elongated pockets 134 are filled with a fixation material 136 , which can be any fixation material previously described . following filling of the elongated pockets 134 with the fixation material 136 , threads 138 can be cut into the base device 130 and fixation material 136 to form the completed orthopaedic implant 132 . in this configuration , the threads 138 will be composed of approximately half fixation material 136 and half material of the base device 130 , giving the orthopaedic implant 132 a substantial amount of fixation material 136 to provide adhesive force during implantation and also placing the fixation material 136 into intimate contact with surrounding anatomy structures during implantation . such a configuration can be particularly useful when the orthopaedic implant 132 is intended to be a long - term implant . referring now to fig1 , a base device 140 is shown before and after being prepared into an orthopaedic implant 142 . the base device 140 is a screw blank with a minor diameter d1 between a head end 144 and a distal end 146 . a fixation material 148 , which can be any fixation material previously described , is bonded to a section of the base device 140 having minor diameter d1 to create a diameter d2 similar to that of the head end 146 and distal end 148 . threads 150 are then formed into the fixation material 148 to create the completed orthopaedic implant 142 . referring now to fig1 and 20 , an orthopaedic implant 160 is shown that includes a base device 162 , shown as a bone plate , and a fixation material 164 attached to the bone plate 162 . the bone plate 162 has a bare surface 166 and multiple openings 168 that are sized to allow bone screws ( not shown ) to be passed through . the openings 168 are shaped so that when the bone screws are driven into a bone , they will hold the bone plate 162 in place . the bone plate 162 can be made of biocompatible metals such as titanium , cobalt chrome and stainless steel , but can also be made of a biocompatible polymer such as peek . a polymer bone plate 162 could offer advantages over more common metal bone plates , such as higher compression and adjustable stiffening . the fixation material 164 is attached to a bottom surface ( not shown ) that is opposed to the bare surface 166 and will be in contact with the bone during implantation . the fixation material 164 can be any fixation material previously described . in this embodiment , the fixation material 164 forms a layer on the bottom surface of the bone plate 162 . since bone screws will be going through the openings 168 , the fixation material 164 does not cover the openings 168 . if the bone plate 162 had a bare bottom surface , the only fixation that the bone plate 162 would have when implanted would be provided by friction from the bone screws implanted in the bone . by attaching the fixation material 164 to the bottom surface of the bone plate 162 , the bone plate 162 is provided with adhesive force of its own : initially from the roughness of the fixation material and later from bone ingrowth into the fixation material 164 . although the fixation material 164 is shown covering the entire bottom surface of the bone plate 162 , the amount of fixation material 164 could be altered to provide a desired amount of adhesive force to the bone plate . referring now to fig2 , an orthopaedic implant 170 is shown that includes the bone plate 162 of fig1 and 20 with a fixation material 172 attached at one end 174 of the bone plate 162 . the fixation material 172 is shaped as a patch and can be any fixation material previously described . by attaching the fixation material 172 to only one end 174 of the bone plate 162 , bone ingrowth and fixation will only occur at the end 174 of the plate with the fixation material 172 , allowing an opposite end 176 to float to whatever degree the attached bone screws allow . such a configuration allows for a dynamic bone plate 170 . referring now to fig2 , an orthopaedic implant 180 is shown that includes the bone plate 162 of fig1 , 20 and 21 with two regions of a fixation material 182 attached at both ends 184 , 186 of the bone plate 162 . the regions of fixation material 182 are shaped as dots of material and can be any fixation material previously described . attaching the fixation material 182 to both ends 184 , 186 of the bone plate 162 provides bone ingrowth , and therefore fixation , at both ends 184 , 186 of the bone plate 162 . referring now to fig2 , an orthopaedic implant 190 is shown that includes the bone plate 162 of fig1 , 20 , 21 and 22 with three regions of a fixation material 192 surrounding the openings 168 of the bone plate 162 . the fixation material 192 can be any fixation material previously described . bone ingrowth into the fixation material 192 around the openings 168 provide additional fixation to the bone plate 162 in those regions . such a configuration could be desirable if the bone screws are to be removed after implantation or do not provide enough fixation of the bone plate 162 on their own . while this invention has been described with respect to at least one embodiment , the present invention can be further modified within the spirit and scope of this disclosure . this application is therefore intended to cover any variations , uses , or adaptations of the invention using its general principles . further , this application is intended to cover such departures from the present disclosure as come within known or customary practice in the art to which this invention pertains and which fall within the limits of the appended claims .
the present invention provides an orthopaedic implant including a base device having a device surface and a fixation material attached to at least one portion of the device surface . the fixation material is configured to provide a minimally sufficient adhesive force to resist natural pull out caused by forces acting on the base device after implantation and bone growth . also provided is a method of manufacturing an orthopaedic implant . a base device with a device surface is provided and a minimally sufficient adhesive force , that can resist natural pull out caused by forces acting on the base device after implantation and bone growth , is determined . a proper amount of fixation material sufficient to provide an adhesive force equal to the minimally sufficient adhesive force is determined and fixation material is applied to the device . when the proper amount of fixation material is applied to the device surface , application is stopped .