the present invention comprises a self tapping implant which requires substantially less torque to install than devices currently in use . the reduction in effort is achieved by the inclusion of at least one cutting surface on each rotation of the thread and by including a spiral groove which runs in an opposite direction to the threads . this enables the implant of the present invention to corkscrew into an opening instead of cutting course threads . referring to fig1 - 3 , according to one dental implant embodiment , the implant comprises a substantially cylindrical body 1 having a proximal end 2 and a distal end 3 . the proximal end contains a prosthetic platform 7 onto which a prosthesis will be fitted . the body contains at least one external helical thread 9 which runs from the distal end 3 to the proximal end 2 . the helical thread 9 maybe right or left handed and contains at least one cutting edge 6 for each turn of the cutting head . the implant further comprises a second helix 10 running in the opposite direction of the helical thread . the second helix can be seen more clearly in fig4 in which the helical thread 9 has been omitted for clarity . the helical thread 9 is further comprised of an inner diameter 11 and an outer diameter 12 . the outer diameter 12 forms a ridge 4 having a plateau 5 on the outermost thread surfaces which engages with the bone during insertion . it is preferred that the plateau 5 be as narrow as possible subject to the structural limitations of the material comprising the implant . thinner diameters allow for smaller pilot holes , easier drilling and reduce the torque required for insertion . larger plateaus may be required for softer bone . the thread pitch 15 is not critical to the invention and may be increased or decreased depending on the mechanical needs for the application . thread pitch can be constant or variable . the cutting edge 6 located within the helical thread 9 comprises a recess 13 and a beveled surface 14 . the angle of the bevel is not critical but should be as narrow as possible to facilitate cutting into the bone , but not so narrow that the structural integrity of the cutting surface and thread . the cutting edge 6 is formed by cutting the second helix 10 into the body of the implant and is contiguous with the helical thread 9 . in a preferred embodiment the plateau 5 adjacent to the cutting edge has a chamfer 30 to form the initial cutting surface . the chamfered edge 30 makes the initial contact with the bone followed by the cutting edge 6 . the second helix 10 in addition to creating the cutting edge 6 also serves to assist in clearing bone debris created by the cutting edge . in the main body 1 , the main body may be straight or tapered , with a straight body being most preferred . when the main body is straight is preferred that the initial turn of the helix 16 be of a smaller diameter than the rest of the main body 1 to facilitate easy insertion into the pilot hole . in yet another embodiment a secondary thread 20 ( not shown ) may be included inside the helical thread 9 . fig5 is an engineering drawing of one embodiment in which the implant is 4 mm in length and has an outer diameter 12 of 0 . 1540 cm and an inner diameter 11 of 0 . 12 cm . the distance between the leading edges of the thread 9 is 0 . 0354 and each thread has a 15 degree undercut on the bottom side and a cut having a radius of 0 . 015 cm on the top side . the secondary helix 9 is cut at a depth of 0 . 130 cm . the top of the secondary helix is cut at a 60 degree angle and the bottom of the helix is cut at a 15 degree angle with a radius of 0 . 005 cm in the valley . one of skill in the art will appreciate that the surface of the implant can be further processed to aid in growth of new bone around it . such processing can include the use of coatings or modifying the surface textures of the implant as is known in the art . the prosthetic platform may be structured to accommodate any form of implant . it can comprise internal threads 26 ( not shown ) which are inside the body of the implant or external threads 25 ( not shown ) or comprise any type of stud or ball upon which a prosthesis can be mounted . the thread pitch is not critical and may be selected for the application . in yet other embodiments , the implant may contain surfaces suitable for bonding the prosthesis to the implant . the implant of the present invention is used in a conventional manner . the dentist or surgeon will drill a pilot hole for the implant . the implant is attached to an insertion tool and turned into the pilot hole . upon turning , the cutting edge 6 will cut a groove into the bone into which the helical thread 9 will follow . because cutting edge 6 has a sharp edge leading into a narrow plateau on the helical thread 9 , less bone debris is generated . this debris is pushed towards the proximal end of the body through the second helical groove 10 . this movement of debris keeps the pilot hole relatively free from debris thereby preventing debris from filling the pilot hole and jamming the implant . this reduces incidences of the implant prematurely bottoming out in the pilot hole because of debris filling the hole and reduces the debris caught in the helical groove thereby reducing friction on the cutting surfaces which reduces the torque required for insertion . implants of the present invention can be manufactured from any structural material suitable for dental implants , including but not limited to stainless steels , titanium , ceramics , polymers and any other material with appropriate mechanical characteristics which is biocompatible . titanium is most preferred . implants of the present invention can be readily manufactured using a modern lathe capable of cutting screw threads . the unfinished stock is mounted in the lathe at the proximal end . the cutting blade of the lathe cuts a helical groove in the stock leaving the desired primary thread . the direction of rotation is then changed and the desired secondary helical groove is cut across the primary thread thereby creating the cutting surfaces . the shape of the helices are determined by the cutting head on the lathe and different cutting heads can be used to create different helices . it will be appreciated that both straight and tapered implants can be created in this manner . alternatively , depending on the manufacturing materials , the implant can be formed by passing the stock comprising the body through one or more cutting dies as is known in the art or by the use of molds or forging . for implants made of plastics , ceramics or polymers , molding is the preferred method of manufacture . as long as the properties of the implant materials are taken into account any thread pitch , thread thickness and cutting edge are possible up the point where the material is too thin to support the load placed on it . threads and cutting edges that are too thin may break under higher torques or distort during insertion . experiments were performed comparing the insertion of the implant of the present invention with an equal diameter implant using classic cutting flukes . in the test protocol , high density polyurethane was used to simulate bone . a block of polyurethane was secured to a work station and 3 . 2 mm holes drilled in the block . the implants were then inserted using a digital torque wrench ( tohnichi , japan ). the insertion torque was recorded in newton centimeters after each complete turn and the data recorded . these data are shown in tables 1 and 2 below . the data in tables 1 and 2 show that the insertion torque of the implant of the present invention is comparable to the insertion torque of the classic design for shallower insertion depths . however , as depth of insertion increases , the classic implant design requires significantly more torque to insert in contrast to the implant of the present invention . these same data are graphed in fig6 and 7 . referring to fig8 which is a line graph comparing the average torques recorded for each turn in tables 1 and 2 above . fig8 shows that the cutting flukes of the present invention require substantially less torque as the implant is turned deeper into the socket . the present invention only required an average of 16 . 75 ncm of torque during insertion of turn 8 compared with 27 ncm of torque for the version of the implant having classic cutting flukes . the results are even more dramatic at 13 turns in which the present invention only required 44 . 75 ncm of torque compared to 75 . 5 ncm of torque for the version of the implant having classic cutting flukes . the present invention will allow easier insertion by a surgeon and reduce the discomfort felt by the patient . while the invention is susceptible to various modifications and alternative forms , specific embodiments thereof have been shown by way of example in the drawings and will herein be described in detail . it should be understood , however , that it is not intended to limit the invention to the particular forms disclosed but , on the contrary , the intention is to cover all modifications , equivalents , and alternatives falling within the spirit and scope of the invention as defined by the appended claims .
the invention relates to bone implants , namely screw - type implants and , more particularly , to a self tapping dental implant having at least two helical grooves running in opposite directions around the implant .