fig1 and 2 illustrate a representative uhmwpe tibial bearing insert according to the present invention , generally denoted as 10 . the tibial insert 10 comprises an anterior surface 11 including a locking wire 12 and locking tab 13 and a posterior surface 14 including an intracondylar recess 18 and locking recesses 15 , shown in fig3 ( not in fig2 ). the insert also has a bearing surface 100 . in an alternative embodiment , an additional locking recess 15 may be placed within the intracondylar recess 18 . locking recess 15 engages a protrusion 24 a , 34 a formed on the posterior surfaces 23 , 33 of the tibial trays 20 , 30 as shown in fig5 and 9 . fig3 and 4 illustrate a cross - sectional view of the tibial insert 10 along line 3 - 3 of fig1 . referring to fig3 , the locking wire 12 is located above the locking tab 13 along the anterior surface 11 , whereas the locking recess is disposed along the lower portion of the posterior surface 14 . fig4 is an enlarged view of detail a of fig3 , showing the anterior surface 11 of the tibial insert 10 , illustrating the placement of the locking wire 12 in a groove 12 a formed above the locking tab 13 . as shown , the locking wire 12 is disposed above the locking tab 13 , with a space between the two parts . furthermore , the locking wire 12 is disposed along a slot which allows the wire 12 to resiliently and posteriorly deflect into the groove 12 a when a compressive force is applied during insertion of the insert 10 into the tray . additionally , fig3 shows a view of the posterior surface 14 including locking recess 15 and a flange 17 extending outwardly of the tray contacting surface 19 . fig5 illustrates a representative polymeric tibial tray 20 according to the present invention . the polymeric tray 20 comprises an anterior wall 21 including a bead 22 running along an inner posteriorly facing surface of anterior wall 21 and a posterior wall 23 including undercuts 24 located below protrusion 24 a and receiving flange portion 17 of the insert 10 , and an intracondylar recess 25 . alternately the bead 22 can be discontinuously spaced along the wall 21 such as at the medial corner 21 a and lateral corner 21 c of the anterior surface 21 and optimally along the central anterior surface 21 b . the polymeric tray 20 further comprises a keel 206 ( not shown ) which is implanted into the tibia and a bone contacting surface 208 ( fig1 ). an additional undercut 24 may also be placed within the intracondylar recess 25 for engaging a flange portion 17 located on the insert 10 . fig6 illustrates a front view of a representative metallic tibial tray 30 . the metallic tray 30 comprises an anterior wall 31 including a plurality of barbs 32 ( fig7 , 8 , and 9 ), disposed alongside and protruding posteriorly , and a posterior wall 33 including undercuts 34 and an intracondylar recess 35 ( fig9 ). an additional undercut 34 may also be placed within the intracondylar recess 35 ( fig9 ). the metallic tray 30 further comprises a keel 306 which is implanted into the tibia and a bone contacting surface 308 . fig7 illustrates a cross - sectional side view of the metallic tray 30 along line 7 - 7 of fig6 . as shown , the barbs 32 protrude posteriorly and run continuously along a substantial portion of the anterior wall 31 . furthermore , the intracondylar recess 35 is centrally disposed on a sagittal plane bisecting the posterior wall 33 with the undercuts 34 and protrusions 34 a on the anteriorly facing surface of the posterior wall 33 ( fig9 ). fig8 is an enlarged view of detail b of fig7 , the anterior wall 31 of the metallic tray 30 , illustrating the placement of the barbs 32 along the anterior wall 31 . as shown , the barbs 32 include a chamfer 32 a which extends posteriorly , a tip 32 b , an underside 32 c which faces distally , and a proximally facing surface 32 d on which tibial insert 10 is mounted . the barbs 32 are placed along an upper portion of the anterior wall 31 so as to leave space below for insertion of the tibial bearing insert 10 . furthermore , the locking wire is sufficiently thin to be capable of resiliently deflecting in the anterior - posterior direction when a force is applied against it by the barbs 32 during insertion of the insert 10 . fig9 is a top view of the metallic tibial tray 30 according to the present invention . as shown , a plurality of barbs 32 are disposed alongside the anterior wall 31 and extend posteriorly for engaging the anterior surface of the tibial insert 10 . furthermore , the posterior wall 33 includes undercuts 34 , protrusions 34 a , and an intracondylar recess 35 . an additional undercut 34 and protrusion 34 a may also be placed within the intracondylar recess 35 . the posterior wall undercuts 24 , 34 and protrusions 24 a , 34 a of the polymeric tray 20 and metallic tray 30 may be identical in design so that the same tibial insert 10 can be used in either tray . fig1 is an enlarged schematic cross - sectional side view along line 10 - 10 of fig5 of the engagement between the tibial insert anterior surface 11 and the polymeric tray posterior surface of the anterior wall 21 . the tibial insert is first engaged with the polymeric tray 20 through insertion of the flanges 17 into the posterior undercuts 24 , wherein the protrusions 24 a engage with the locking recesses ( in fig5 ). afterwards , the insert anterior surface 11 is snap - fit into engagement with the tray anterior wall 21 , wherein the locking tab 13 forces the anterior wall 21 to resiliently deflect anteriorly and snap posteriorly back into place with the bead 22 fitted between the locking wire 12 and locking tab 13 . accordingly , the bead 22 should be sufficiently sized to protrude past the locking wire 12 and the locking tab 13 when the tibial insert 10 is snap - fit into the polymeric tray 20 . thus , the tibial insert 10 is held in secure engagement with the polymeric tray 20 through connections at their posterior and anterior portions . fig1 is an enlarged cross - sectional side view of the engagement between the tibial insert anterior surface 11 and the metallic tray anterior wall 31 . the tibial insert 10 is first engaged with the metallic tray 30 through insertion of the flanges 17 into the posterior undercuts 34 , wherein the protrusions 34 a engage with the locking recesses 15 ( in fig9 ). afterwards , the insert anterior surface 11 is snap - fit into engagement with the tray anterior wall 31 , wherein the plurality of barbs 32 forces the locking wire 12 to resiliently deflect posteriorly into the groove 12 a and then snap anteriorly back into place underneath the barbs 32 . accordingly , for each barb 32 , the chamfers 32 a must be sufficiently angled to extend posteriorly past the locking wire 12 such that the tips 32 b may push the wire 12 into the groove 12 a and , upon the wire 12 snapping back into place , the undersides 32 c may subsequently prevent the locking wire 12 from moving in an upward direction . thus , the tibial insert 10 is held in secure engagement with the metallic tray 30 through connections at their posterior and anterior portions . in a preferred embodiment of the present invention , the polymeric tray 20 is formed from polyether ether ketone ( hereinafter “ peek ”), preferably with a crystallinity of less than 30 percent . due to its relative inertness and nonporousness , peek biomaterials have been found to be an attractive platform upon which to develop implants such as the present invention . benefits include lower stiffness which results in reduced stress shielding , sustained bonding strength to bone cement in body fluid , reduced backside wear between the polymeric tray 20 and the tibial insert 10 , ease of manufacture , and lower costs . furthermore , in the preferred embodiment , the polymeric tray &# 39 ; s 20 bone - contacting surface 208 is grit - blasted to a high surface roughness in order to increase its initial bond strength with bone cement . preferably , the blast media used is sodium bicarbonate or a water - soluble grit of similar hardness . the polymeric tray 20 is grit - blasted at a pressure between 105 and 110 psi to a high surface roughness in order to enhance its initial bond strength with bone cement . the grit - blasting method comprises the steps of loading the tray into a masking fixture , masking areas of the tray that will be subjected to high bending stresses , blasting an abrasive powder against the tray to achieve an average surface roughness of between 4 and 6 micrometers , submerging the tray in water having a temperature between 60 and 70 degrees celsius for 2 minutes , and allowing the tray to air dry . in a preferred embodiment of the grit - blasting method , the grit - blasting machine is a suction - type or equivalent and has a 5 / 32 inch air jet and a nozzle having a 5 / 16 inch diameter orifice . the machine may be automated or manually operated . furthermore , the preferred method includes focusing the nozzle perpendicular to the intended blasting area from a distance of 3 to 4 inches . if a perpendicular angle is impossible , the minimum allowable angle should be no less than 45 degrees . blasting is continued until the desired surface roughness of 4 to 6 micrometers is reached . preferably , the blast media used is sodium bicarbonate or another abrasive nonmetal , water - soluble , and noncorrosive powder having a particle size of distribution of less than 10 percent 210 micrometer particles , less than 25 percent 270 micrometer particles , less than 50 percent 350 micrometer particles , less than 75 percent 430 micrometer particles , and less than 90 percent 510 micrometer particles . in addition , the grit - blasting technique is performed below the glass transition temperature of the polymer being roughened by the technique . below the glass transition temperature polymers are more brittle than they are above their glass transition temperature . as a result , it is easier to create a roughened surface on a polymer when it is below its glass transition temperature . accordingly , there is a disadvantage to creating a roughened polymeric surface by grit - blasting the mold into which a polymer material could be injected . as a consequence of both material flow inherent to the molding ( injection or compression ) process and the molding process taking place above the glass transition temperature , the surface roughness achieved by molding roughness into a part is generally not equivalent to the surface roughness achieved by grit - blasting the part after molding . it has been discovered that grit - blasted polymeric surfaces of a given roughness have better adhesion to bone cement than molded polymeric surface of the same roughness . thus , according to the invention , the tibial insert is shaped to lockingly engage with either the polymeric tibial tray 20 or the metallic tibial tray 30 , albeit through differing means of engagement . during implementation , either the polymeric tray 20 or metallic tray 30 may be chosen for implantation into the resected tibia and receive the same uhmwpe bearing insert 10 . the interchangeability of a polymeric tray 20 or metallic tray 30 provides the option of choosing between implantation with or without the use of bone cement . implementing the polymeric tray 20 , particularly in the preferred embodiment in which the bone - contacting surface 208 is grit - blasted to a certain roughness , allows for a stronger bond with bone cement than metallic tibial trays . however , use of a metallic tray 30 would still be appropriate where bonding through cementless bone tissue ingrowth would be preferable to using bone cement . because all cementless tibial trays are currently made of metal , a polymeric tray 20 which is compatible with an already - existing line of tibial inserts would reduce design and manufacturing costs and allow for the option of using bone cement without the need for a new tibial insert design . in addition , the interchangeability of the present invention allows for consideration of a patient &# 39 ; s bone stock . polymeric trays are more flexible than their metallic counterparts and are therefore less likely to shield from stress areas of the bone where bone resorption has occurred with metallic trays . thus , a younger patient with relatively strong bone stock would benefit from the loading pattern provided by a polymeric tray whereas a metallic tray would be more appropriate for an older patient with weaker bone stock . thus , the compatibility of both types of tibial trays with the same tibial insert provides more options and increases design and manufacturing efficiency . lastly , the interchangeability between the polymeric and metallic trays would allow a provider to offer a more competitively priced implant system because a polymeric tray can be significantly less expensive to manufacture than a metallic tray . thus , the company would be able to offer a less expensively priced polymeric tray in value markets while still being able to offer a metallic tray without having to design a different tibial insert for each tray . although the invention herein has been described with reference to particular embodiments , it is to be understood that these embodiments are merely illustrative of the principles and applications of the present invention . it is therefore to be understood that numerous modifications may be made to the illustrative embodiments and that other arrangements may be devised without departing from the spirit and scope of the present invention as defined by the appended claims .
a method for improving the bond between a peek joint component and bone cement comprising roughening a surface of the peek component by air - blasting abrasive water - soluble particles against the component until an average surface roughness of 4 to 6 micrometers is attained and subsequently submerging the component in water to dissolve any residual particles .