fig1 is one embodiment of the lag screw implant . in the lag mode it is mainly in tension along its axis and other force vectors are neutralized by the basic construct . it comprises : 1 being the tip at the first end , with guide wire 7 in the central canal . the tip shown is self tapping , but optionally a non - self tapping tip may be used . 2 is the short threaded section at the first end , the thread not extending to the head 4 . 3 being the smooth screw shaft section meant for gliding through the drill hole in the fragment nearer to head , allowing lag screw compression . 4 is the spherical head for engaging a countersunk surface of the fragment nearer to head . the head may be integral with the rod or may be mobile for fixation at a desired level to rod 5 . such refixation is provided by means of a transverse screw through the head and drive shaft possessing holes 15 , at intervals for screw passage . 5 is the unthreaded drive shaft , which serves for driving the device in or out , also for being secured to an external fixator construct through a clamp ; as well as for subsequent turning of device to renew the torque , in case of loosening . it has transverse holes 15 , at intervals to accommodate a screw through a mobile head for refixation of head . the holes may be spirally arranged , instead of linear as shown . 6 is the second end which is outside , with a means for gripping , shown as a milled surface in the figure . the grip can optionally be quick coupling , or faceted by triangulation , to suit the gripping handle or chuck . 7 is the guide wire passing from any one end , through the entire rod and out at the other end . it helps to direct the device at the best angle across the fracture plane . fig2 shows the cross - section 11 of a prior art schanz screw driven into a drill hole of a suitably smaller diameter , in bone b . this generates a radial preload 8 at the implant / bone interface . such a preload should not be excessive as judged by those skilled in the art , otherwise micro - fractures in the drill hole wall will occur , with quick loosening . fig3 shows the preferred basic implant inserted in bone b . it is for gripping a fragment , not for lag - screw mode . 1 is the non - self tapping tip at the first end . pre - tapping the thread with tap is known to prolong the durability of a screw against loosening . 2 is the fully threaded section from the first end to the head , providing maximum interface with bone . 4 is the conical head with base towards the bone , with a blunt serrated basal surface for making blunt limited contact on bone at 14 . the head exerts a surface preload 9 on bone surface and on tightening the screw the implant is axially tensioned in direction shown at 10 , within the bone b . the vertex of the cone where the cone converges to a point , is incorporated in the shaft , as the conical head is fixed to the shaft and is continuous with it . when it became known that bone plates in intimate contact with bone surface interfere with the surface nutrition , limited contact plates were designed with better results . the same principle had not been applied to screw heads . now , to allow blood supply to reach the drill - hole margin under the conical screw head , a limited contact surface is incorporated where it engages the bone surface , in the preferred device . sharp serrations are avoided , to prevent too much stress concentration on bone . nutrition favours bone integrity . the two preloads , surface 9 and axial 10 , are in addition to radial preload 8 of prior art . the head is integral to the rod for stability , disallowing any micro - movement . basic implants are driven at right angles to bone surface , in a single fragment , when the leading base of the head 4 makes all round even contact on bone b . the device is not canalised , for greater strength against lateral bending . the overall dimensions of the device and its parts are made to suit the size of bone , the size of fragments and the depth of bone from skin . thus in a superficial bone like the tibia , the conical head will be squat , to contain it within the skin . in a deeper bone like the femur the cone will taper taller , for easy removal by spreading the soft tissues . fig4 shows a common variety of hip fracture with fracture plane f , giving rise to two fragments b and b ′. a frequently used two - piece device , a sliding hip screw x in barrel y , is holding the fracture reduced and compressed by screw z at the time of operation . this compression wears off in time after the skin s is closed , with no possibility of recompressing . the screw may fail to slide causing a persisting gap and non - union . fig5 is the same fracture f as in fig4 , held with prior art external fixator comprising pins p , clamps 12 and tube 13 . the fragments b and b ′ are splinted over the upper two schanz screws , but no compression can be achieved , because fragment b ′ can slide out on the smooth pin section . the lower two schanz screws are the basic implants , which can be inserted with radial preload . when radial preload tapers off , it cannot be renewed unless screw is reinserted at a new site . no other preloads are possible in this prior art design . persisting gap at fracture site may lead to delay or failure of union . fig6 is the same fracture f between b and b ′, stabilized with an external fixator using the preferred device . the upper two screws in lag mode help active compression at fracture site , which can be renewed by loosening one screw at a time at the clamp , turning it tighter , and retightening the clamp . the lower two screws are the basic implants for completion of the construct , driven with radial preload . the head exerts surface preload on the bone , adding to the lateral stability of the implant . in addition , there is an axial preload created along the length of the screw , tensioned on driving it tight . these preloads are same as shown in fig3 . thus , there is a wider distribution of stresses compared to the prior art schanz screw in which all stress is borne at the rod / drill hole interface . the axial and surface preloads are renewable at intervals , without any repeated anaesthesia or exposures . the preloads are also mutually protective . clamps 12 connect to tube 13 . fig7 shows a multiple fracture in the lower one third of the femur , involving the knee joint , reduced and held by a fixator using the implants of invention . the fragments are b , b ′, b ″, b ′″ and b ″″. the fracture planes are f , f ′, f ″, f ′″, f ″″; of which f ″ involves the joint surface . the lower five implants are in lag mode , the partial thread engaging only one fragment near the first end . the lag screws are at right angles to the fracture planes , except the third from below . since this is compressing three fragments b ″″, b ′ and b ″ across two fractures f ″″ and f ′, it is at best possible angle that the situation permits . the detail of the head and countersink are shown at fig9 . the upper two implants are in basic mode to control b , the upper two - thirds of the bone . they are at right angles to the bone surface for best mechanical advantage . all implants are connected through clamps 12 to the tube 13 . all the implants have capability of renewable stability and compression , which gives quicker union . this protects against instability , biological failure , and sepsis . the lowest two lag screws compress the articular fragments b ″ and b ′″ to each other and stabilize them to the rest of the bone . the screws need not all be in the same plane as shown in the figure . they may tilt into different planes and require creative interconnection to other construct components . fig8 shows one prior art device of taylor et al seated in bone b . the fracture plane f runs at about 45 - degrees to the outer surface of bone . for optimum compression , the force vector should be at 90 - degrees to fracture plane . when their device is so driven , the head 4 gets tilted , being flat at the engagement surface . this leads to much localized pressure on a small area and will lead to mechanical failure of bone by micro fractures . taylor et al have patented heads of many shapes , all of which have the same flat engagement plane to engage the bone surface . fig9 shows the preferred lag screw device with a sphere - like head 4 , driven at 90 - degrees to fracture plane f . being tilted at about 45 - degrees to the surface , it still has a wide concentric contact with the countersink in bone . wide distribution of compressive load of sphere - like head reduces likelihood of mechanical failure of bone . fig1 shows an undistorted enlargement of the head of taylor et al , which appears in fig4 of their application . enlargement has rendered more noticeable the smaller irregularities of the original drawing but the geometry is preserved . the head , when examined for attributes of being spherical , may vie for the category of “ spherical , being a segment of a sphere enclosed by two parallel planes ”. the two parallel planes of the head being equal , they must lie at equal distance on either side of an equatorial plane of the original sphere , the segment in question being bisected lengthwise by the diameter of the parent sphere / circle . the diameter of the original sphere from which the segment is derived , would then be the diameter of the segment . if a circle o is described with its centre i and diameter d the same as that of such a sphere segment , then this circle should represent the original sphere from which the segment is derived . the surface of the sphere and the peripheral curve of the segment should then exactly coincide . this is not the case with the head under scrutiny . the curved periphery of the head is part of a much smaller circle / sphere than the curvature of the circle / sphere from which it should have been derived . the head can then at best be described as “ discoid , with rounded periphery ” rather than as “ spherical , being segment of a sphere ”. this prior art therefore does not qualify for anticipating the present claim of a device , with spherical head shaped like a sphere . even if it had qualified for the definition of being spherical , being a segment of a sphere , different segments of a sphere will have such varying mechanical attributes , that many other claims would still be admissible depending on how the segments are derived and what are their engagement surfaces . different segments of the same sphere can look and mechanically function very differently . it can only be a proper sphere like the preferred head , which can present the same spherical surface all round , with the same mechanics all round . the segments of that do not share all qualities of a sphere . fig1 shows compression applied to fracture surface of bone b not at 90 - degrees to fracture plane f , but at 90 - degrees to the outer surface of bone . the fracture surfaces are sliding instead of being compressed .
an external fixator implant screw with an intercalated head , of which one embodiment for lag screw mode has a spherical head , and a partial thread . the spherical head in countersunk bone exerts concentric wide contact on insertion at various angles to surface . optional canalization of central rod allows guide wire technique and optional mobility of head allows variable shaft length between head and thread . another embodiment for use in basic implant mode , in a single bone fragment , at right angles to bone surface , has a conical head with limited basal contact on bone , the head being integrated to a solid rod and is fully threaded from head to leading tip . in both embodiments , the load transmission is renewable from outside in case of loosening , without reopening any wound . the implant is made of biocompatible material .