AU2012201417B2

AU2012201417B2 - Angularly stable fixation of an implant

Info

Publication number: AU2012201417B2
Application number: AU2012201417A
Authority: AU
Inventors: Klaus Dorawa; Jorg Mayer; Andrea Muller; Robert Sonntag; Urs Weber; Nils Zander
Original assignee: Woodwelding AG; Stryker European Operations Holdings LLC
Current assignee: Woodwelding AG; Stryker European Operations Holdings LLC
Priority date: 2007-09-18
Filing date: 2012-03-08
Publication date: 2012-09-20
Anticipated expiration: 2027-09-18
Also published as: AU2012201417A1

Abstract

ANGULARLY STABLE FIXATION OF AN IMPLANT Abstract The invention provides a system and method of angularly stable fixation of an implant on a bone. The method includes the following steps: making at least one hole in the bone by means of a bone drill, placing an implant on the bone in a desired position and joining the implant with the bone, such that the implant is prevented from rotation about its attachment point. A system for use in the above described method comprises a bone drill (40), an implant (20) and a sonotrode (50) for angularly stable fixation of the implant on the bone (10). The system can further comprise a joining element (60) to join the implant with the bone.

Description

S&F Ref: 942821D1 AUSTRALIA PATENTS ACT 1990 COMPLETE SPECIFICATION FOR A STANDARD PATENT Name and Address Stryker Trauma GmbH, of Prof.-KOntscher-Str. 1-5, of Applicant : 24232, Sch6nkirchen/Kiel, Germany Actual Inventor(s): Nils Zander Klaus Dorawa Robert Sonntag Jorg Mayer Urs Weber Andrea Muller Address for Service: Spruson & Ferguson St Martins Tower Level 35 31 Market Street Sydney NSW 2000 (CCN 3710000177) Invention Title: Angularly stable fixation of an implant The following statement is a full description of this invention, including the best method of performing it known to me/us: 5845c(6098270_1) Il ANGULARLY STABLE FIXATION OF AN IMPLANT BACKGROUND OF THE INVENTION 5 Field of the Invention The invention relates to a system and method of fixation of an implant to a bone.. The invention particularly relates to a system and method of angularly stable fixation of an implant to a bone. Brief Description of the Prior Art 10 It is generally known that fractures are treated by fixation of the broken bones. The individual fragments of the bone are lined up to each other so that the separated parts can grow together again. It is necessary that the parts remain relatively stable with respect to each other over a time period to allow the healing. It is possible in many cases to fix the fragments of the fractured bone via a rigid cast such as a plaster cast 15 on the outside of the broken part of the body. The broken bone pieces are aligned with each other and held in position by the rigid cast. In some cases, particularly for more complicated fractures, it is necessary to connect the individual broken bone pieces directly with each other. In these cases, the fracture is fixed or reduced via an invasive procedure wherein an implant is installed within the body with screws or 20 nails. It has turned out, however, that fixed bone parts do not always grow together as desired. In addition, the conventional invasive methods of fracture fixation are accompanied by relatively high trauma and loss of blood. Furthermore, there is a need for a device for fixation of periprothetic fractures in immediate proximity of 25 implants, particularly joint implants. Fixing plates have been suggested for use in the methods mentioned above. Plates are first pre-formed according to the individual fracture situation outside the patient and then connected via an operation to the fractured bone or the bone fragments by nails or screws. These plates have the additional advantage that they can fix 2 particularly smaller fragments and stabilize the fracture. This way in case of more complicated fractures, the fractured pieces can be reliably connected with each other or with several fragments. However, these fixing plates cannot be fastened ideally. Particularly when the fracture involves the musculoskeletal system and the fractured pieces are exposed to different shearing forces in the course of the movement. Thus, there is a need for implants with improved fixation for fractures involving musculoskeletal system. Object of the Invention It is the object of the present invention to substantially overcome or ameliorate one or more of the above disadvantages. Summary of the Invention The present invention provides a system for fracture fixation comprising: a plate, the plate having an opening, the opening being adapted to align with a hole in a bone, and the opening being rotationally non-symmetric; and a pin insertable in the opening and the hole; the pin and the plate being liquefiable so that at least a portion of the pin melts together with at least a portion of the plate thereby attaching the pin in the bone and to the plate, to prevent a rotational movement of the plate. Preferably, the system further comprises: a drill, the drill being adapted to form the opening and the hole in the bone adjacent the plate; and a jig, the jig being adapted to guide the drill. Preferably, the pin is selected from a group consisting of a conical pin, a dowel, a snap-fit dowel, a toothed dowel, a screw, a conical screw, a double pin, a stepped pin, a triangular pin, an asymmetrical pin and a pin having a thickened head. Preferably, the shape of the pin and the hole are complimentary and the pin is sized to be a close fit in the hole.

3 Preferably, the drill is selected from a group consisting of a bone drill, a conical bone drill, a threaded bone drill, a conical threaded bone drill, a double bone drill, a stepped bone drill, a bone drill with a triangle cross section, a bone drill with an asymmetrical cross section, and a Kirschner wire. Preferably, the system further comprises a sonotrode being adapted to apply energy to the pin and the plate. Preferably, the drill and the sonotrode are combined in a single hand held instrument. Preferably, the plate is made from a material selected from PLLA or PLDLA. Preferably, the pin is made from a material selected from PLLA or PLDLA. Preferably, the pin has a bore along its longitudinal axis. Preferably, the bore is threaded and adapted to receive a threaded tip of a sonotrode. Preferably, the pin has a head and a body, and at least a portion of the body is conical and at least a second portion of the body is cylindrical. Preferably, the pin has a head and a body, and at least a portion of the body has projections. Preferably, a slot is formed in the body of the pin. Preferably, the shape of the pin and the opening are complimentary and the pin is sized to be a close fit in the opening. The present invention also provides a method of using the system, the method comprising the steps of: placing a plate on a bone; forming at least one opening in the plate and the bone, the opening being rotationally non-symmetric; inserting a pin in the opening; and applying energy to the pin to melt at least a portion of the pin thereby attaching the pin in 4 the bone and melting the pin together with the plate such that rotational movement of the plate is prevented. Preferably, the method further comprises the steps of: placing ajig on the plate to guide a drill to form the opening; and marking the bone to locate the jig on the plate. Brief Description of the Drawings The invention is explained by means of exemplary embodiment and with reference to the following drawings. Fig. 1 shows schematically, in four frames, a method of angularly stable fixation of an implant on a bone in accordance with a first exemplary embodiment of the invention.

-5 Fig. 2 shows schematically a second exemplary embodiment of a method in accordance with the invention. Fig. 3 shows schematically a third exemplary embodiment of a method in accordance with the invention. 5 Fig. 4 shows schematically a fourth exemplary embodiment of a method in accordance with the invention. Fig. 5 shows schematically a fifth exemplary embodiment of a method in accordance with the invention. Fig. 6 shows schematically a sixth exemplary embodiment of a method in accordance 10 with the invention. Fig. 7 shows schematically a seventh exemplary embodiment of a method in accordance with the invention. Fig. 8 shows schematically an eighth exemplary embodiment of a method in accordance with the invention. 15 Fig. 9 shows schematically a ninth exemplary embodiment of a method in accordance with the invention. Fig. 10 shows schematically a tenth exemplary embodiment of a method in accordance with the invention. DETAILED DESCRIPTION 20 Fig. I shows an implant plate 20 mounted directly on cortical bone 10. The implant plate 20 may be made from materials such as medical grade plastic, for example, from a polylactid material (PLLA, PLDLA). The used material might be resorbable. Each one of the Figures 1 -10 has four frames showing the steps of the method illustrated in each of the figures. The implant plate 20 and the bone 10 are drilled -6 through with the help of a Kirschner wire 40 such that the drilled openings I I and 12 cross each other. The drilled openings II and 12 should preferably cross at the interface of the implant plate 20 and the bone 10. A drill jig 30 or other suitable guiding device can be used to guarantee that the crossing point is at the interface of 5 the plate 20 and the bone 10. As represented in frame I in Fig. 1, the implant plate 20 is placed on the bone 10. The jig 30 is placed on the plate 20. The jig 30 has two channels 31 and 32 through which a Kirschner wire or alternatively a drill can be advanced to drill openings I1 and 12. Furthermore, the jig 30 has a through hole 33, which accepts and guides a sonotrode. 10 First the Kirschner wire 40 is reciprocated back and forth through the channel 31 of the jig 30 to form a first opening I1 both through the implant plate 20 and through the bone 10. Next, the Kirschner wire 40 is reciprocated back and forth, as seen in frame 2 in Fig. 1, through the second channel 32 of the jig 30 so that a second opening 12 is formed in the implant plate 20 and the bonelO. The two openings 11, 15 12 cross at the interface plane between the implant plate 20 and the bone 10. As shown in frame 3 in Fig. I the jig 30 is located on the implant plate 20. Next, by means of a sonotrode 50 led in the through hole 33, a pressure force F and a vibration U is applied, so that the implant material of the implant plate 20 liquefies in the area of the drilled openings 11, 12 and a part of the material flows into these openings. 20 By virtue of the material flowing in the openings I I and 12, the plate 20 is fixed to the bone 10 as shown in frame 4. The plate 20, fixed to the bone 10, in the above described manner is angularly stable, i.e., the plate cannot rotate. The inclination of the channels 31, 32 in the jig 30 are dependent on the thickness of the implant plate 20. The bone plate 20 is received in the bone 10 like the root of a tooth in the jaw. A 25 variation of this exemplary embodiment of the method may have four drillings/openings placed at 90 degrees from each other instead of the two opposite drillings. The thickness of plate 20 may be thicker or thinner as required. This way more polymer can flow into the openings I I and 12 in the bone 10. The aim is to -7 have sufficient plate thickness left after the impact of the pressure force F and the ultrasound vibrations U has produced ample melting of the plate 20. Through this shear stress can be avoided at later load. Fig. 2 shows a second exemplary embodiment of the invention. Here the implant 5 plate 20 is connected with the bone 10 in an angularly stable manner. Framel shows a drill jig 30 placed on the bone 10. Next, a marking 15 is placed on the bone 10. Then a tapped hole 13 is cut into the bonelO by means of a screw drill 40 as shown in frame 2 in Fig. 2. The screw drill 40 is inserted in and guided by opening 35 in the jig 30 to form the tapped hole 13 in the bone 10. The marking 15 is then used to 10 place the implant 20 together with the jig 30 in the desired location. Next the sonotrode 50 is aligned with the opening 35 in the jig 30 which was already used for making hole 13 using the screw tap 40. Frame 3 in Fig. 2 shows use of the sonotrode 50 to melt (i.e., liquefy) the material of the implant plate 20 and flow the melted material into the threaded hole 13 in the bone 10. The melting is done by applying 15 pressure F and the vibrations U to the implant 20 via the sonotrode 50. Frame 4 of Fig. 2 Shows the implant 20 attached to bone 10 using the method illustrated in Fig. 2. Unlike the first exemplary embodiment no opening/hole is cut into the implant plate 20 itself and consequently formation of polymer debris is prevented. Here only the 20 bone 10 is provided with a threaded hole 13. The drilling point and the point to which the sonotrode 50 is attached is defined by a jig 30 which is aligned with the marking 15. The process described above may be repeated to form more than one holes, in which the implant material then flows into and stiffens,. The sonotrode 50 produces the energy by means of ultrasound vibrations U and a force F which is 25 suitable to liquefy the implant material in the area of the threaded opening 13. The location of the threaded hole 13 is visible as a slight depression 25 in the implant plate 20 where the sonotrode 50 was in contact with the implant plate 20. This -8 depression 25 can be avoided or at least the expression reduced by strengthening the material of the plate 20 at the respective impact point of the sonotrode. Fig. 3 shows a third exemplary embodiment that illustrates the method according to the invention. The third embodiment uses pre-formed implant plate 20. The plate 20 5 has the geometry that also fulfils the functions of the polymeric pins of other exemplary embodiments. The implant plate 20 of the third exemplary embodiment comprises protrusions 22 that are sized to be slid into holes 13 in the bone 10. The location of the protrusions 22 in the implant plate 20 requires a very exact and corresponding positioning of thread holes 13 in the bone10. This can be managed, for 10 example, by means of a jig 30. As shown in frame I in Fig. 3, first the jig 30 is placed on the bone 10. Next, threaded openings 13 are formed in the bone 10 using screw tap 40. The holes 35 in the jig 30 are used to guide screw tap 40 during formation of openings 13. Next, the implant plate 20 is placed on bone 10 such that protrusions 22 project into each 15 drilled hole (i.e., opening) 13. The implant material is now liquefied by means of a sonotrode 50 which is formed with a pointed front end that is inserted in the protrusions 22. This results in the implant material being melted and conforming to the threads formed in the opening 13 in the bone 10, as shown in the frames 2 and 3 in Fig. 3. In this third exemplary embodiment a preliminary stabilization of the 20 fracture is achieved by inserting the protrusions 22 of the implant plate 20 into the openings 13 in the bone 10. The protrusions 22 may be formed in shape of a cone with a central through hole 23, i.e., a through hole 23 may be formed through the implant plate 20 and lengthwise through the protrusions 22. The tip of the sonotrode 50 fits into this hole 23. The tip is greater in diameter than the opening in the plate 25 20 and does exert a pressure on the implant material not only in axial but also in radial direction within the threaded openings 1 3 in the bone 10 so that the material flows reliably into the threads of the screw thread in the bone 10. The implant 20 of -9 the third embodiment represents a very stable system because it only consists of a single component. Exemplary embodiments described hereafter use an additional joining element 60. The joining element 60 is used to connect the implant plate 20 with the bone 10. The 5 fourth exemplary embodiment of the present invention is schematically represented in four frames of Fig. 4. A conical screw tap 40 which makes a conical threaded hole 13 in the implant plate 20 and through the bone 10 simultaneously is shown in frame I in Fig. 4. Next, in frame 2, a'conical pin 60 is shown inserted into the hole 13. The cone angle of the conical pin 60 matches the angle of the screw tap 40. Frame 3 in 10 Fig. 4 shows the pin 60 being liquefied by means of the sonotrode 50. The liquefied material of the pin 60 fills out the cavities in the threaded opening 13 and also melts together with the implant material of the implant plate 20. The penetration depth of the screw tap 40 depends on the plate thickness and is correspondingly defined by a stop 41. The threaded opening 13 offers a simple possibility for the structuring of the 15 bone 10 and at the same time supports the melt process by creation of defined places with high local energy density. Fig. 5 shows successive frames of the fifth, exemplary einbodiment-of-the-invention. Similar to the fourth exemplary embodiment, here a hole (alternatively referred to as an opening) 13 is drilled by means of a screw tap 40 through the implant plate 20 and 20 the bone 10 simultaneously. A screw 60 is screwed into this hole 13. This way the implant plate 20 is preliminarily stabilized in the bone 10. A final angularly stable attachment of the implant to the bone 10 is achieved by applying a force F and an ultrasound vibration U by means of a sonotrode 50 to the screw 60. Thereby, the screw thread of the screw 60 is liquefied and the liquefied material moulds to 25 conforms to the threads in the hole 13 in the bone 10. Further the screw head 61 is melted together with the adjacent surface of the implant plate 20. Since the material of the inserted screw 60 liquefies due to the application of the ultrasound vibration U and the force F, the shaft of the inserted screw may be made -10 smooth in a variation of this embodiment, i.e. the threads of the threaded pin are optional. In addition, the processing of the implant plate 20 and the bone 10 can be done by a drill-tap-combination. The drilling depth is provided by means of a drilling stop 41. The front tap part 43 produces the threaded hole 13 in the bone 10 and the 5 following drill part 42 of the drill-tap-combination produces a smooth hole in the implant plate 20. The material of the polymeric pin 60 melted and then stiffened in the threaded hole 13, offers a good anchorage of the implant plate 20 in the bone 10. By welding together the pin head 61 or the screw head 61 with the implant plate 20 an angularly stable fixation of the implant in the bone 10 is ensured. 10 The sixth exemplary embodiment of the invention is shown in Fig. 6. This method practiced using the sixth embodiment is similar to the method in accordance with the fifth exemplary embodiment. The difference here is that in place of the threaded hole 13, a through hole 14 is formed in the bone 10. The through hole 14 is drilled through the implant plate 20 and cortical portion of the bone 10. The simple 15 procedure for preparing of the bone 10 and the implant plate 20 represents a principal benefit of this solution. This simple procedure of making a smooth hole 14 is performed using a drill 40 as shown in frame 1 in Fig. 6. Next the surgeon inserts a polymeric pin 60 in the hole 14 and pushes it by means of a sonotrode 50. The diameter of the polymeric pin 60 is slightly greater than that of the hole 14 in the 20 bone 10. The diameter difference ideally is about 0.1 to 0.2 mm. The application of the ultrasound energy via the sonotrode 50 melts the material of the pin 60 where the pin 60 comes in contact with the bone 10. The melted material is transported by the movement of the pin 60 through the hole 14 and below the cortical portion of bone 10. The melted material stiffens there again and provides a 25 thickening 62 below the cortical portion of bone 10 as a result of which a reliable anchorage is achieved. The polymeric pin 60 is also welded with the polymeric material of the implant plate 20 by virtue of the fact that the opening in the implant - 11 plate 20 and the head 61 of the polymeric pin 60 are conical and form a close fit and are welded together under the action of the ultrasonic energy. The seventh exemplary embodiment of the invention is shown in Fig. 7. In the seventh embodiment, a plug 60 is used instead of a polymeric pin or a screw of the 5 previous embodiments. As shown in frame I in Fig. 7, a hole 14 is formed into the implant plate 20 and the bone 10 simultaneously. A drill 40 is used to form the hole 14. A plug 60 is inserted in hole 14 as shown in frame 2 in Fig. 7. At first, latches 63 which are formed at the leading end of the plug 60 are pressed against the shaft 64 of the plug. As soon as the leading edge has penetrated through the cortical portion of 10 the bone 10 the latches 63 expand away from the shaft 64 and anchor the plug 60 in the bone 10. As illustrated in frame 3 in Fig. 7, the back end of the plug 60 can then be liquefied by subjecting it to the ultrasonic energy via the sonotrode 50 and thereby welding it to the implant material. The result is a snap-in connection of the plate 20 with the 15 cortical part of bone 10. To prevent the polymeric plug 60 from being pushed during the process of welding and consequently becoming loose in the bone 10, a cord (not shown) can be provided which is integrated into the plug. Using the cord, the plug 60 can be drawn towards the sonotrode 50 during the melting process. This way the plug 60 can be used so that the elastic latches are held under tension against the 20 cortical portion of bone 10 at the leading edge of the plug 60. Fig. 8 shows the eighth exemplary embodiment of the invention. In the eighth exemplary embodiment a plug 60 is used for the anchorage of the implant plate 20 on the bone 10. In this case the plug 60 includes teeth 65 on the surface of the shaft portion of the plug 60. The shaft of the plug 60 has a longitudinal slit that allows the 25 shaft to be pressed in radial direction. This allows the plug 60 to be pushed through a hole 14, which is smaller in diameter than the shaft diameter of the plug 60 in its non-compressed state.

- 12 Ideally, a hole is drilled both into the implant plate 20 and into the bone 10 by means of a conical bone drill 40. A stop 41 at the drill 40 limits the depth of the hole 14 and prevents it from being formed too deeply in the bone 10. The implant plate 20 is anchored in the bone 10 by inserting the plug 60 deeply into the hole 14. The teeth 5 65 located adjacent to the head of the plug 60 act as hooks which abut the inside of the bone 10. On the other hand, the teeth which are formed along the shaft lodge into the bone within the drilling 14. The plug 60 is welded, by means of a sonotrode 50, with the implant plate 20. The conical shape of the hole 14 allows anchoring of the plug in the hole 14. A suitably fine geometry of the teeth 65 or lamellae for the 10 anchorage of the plug 60 can reduce a play which may arise when the sonotrode 50 is pushed on the plug 60 to weld it together with the implant plate 20. Fig. 9 shows schematically the ninth exemplary embodiment of the invention. One feature of this embodiment is the triangular hole 16 formed in the bone 10. A hole without rotational symmetry and larger than the triangular hole 16 is formed in the 15 implant plate 20. Alternatively, non-rotational-symmetric holes of any other shape may be formed in the implant plate 20 and the bone 10. Non-rotational-symmetric holes (or alternatively rotationally non-symmetric holes) are holes in which a pin of complimentary shape can not be rotated by virtue of the shape and matching size of the pin and the hole. An example of the rotationally non-symmetric hole would be 20 an oblong hole or a triangular hole. The matching pins would be oblong or triangular respectively and would be sized to be a close fit in the hole. The holes may be formed, for example, by means of a drill 40 which is ground on one side or is swinging eccentrically, as shown in frame I in Fig. 9. Other known methods available to one skilled in the art may be used to make the holes. A polymeric pin 60 25 is then introduced in the hole 16 with a cross section similar to that of the hole 16. The polymeric pin 60 has a threaded hole 66 extending in longitudinal direction in the centre portion of the pin 60. An appropriately formed tip of the sonotrode 50 is connected to the threaded hole 66. The polymeric pin 60 is completely screwed on the tip of the sonotrode such that it cannot be screwed any further.

- 13 Furthermore the length of the pin 60 is such that the pin 60 projects into the bone 10 beyond the cortical bone layer. In this position a torque M is applied together with the ultrasound vibration U from the sonotrode 50 and the assembly of sonotrode and polymeric-pin is rotated by about 60 degrees. Here, a tool combination of a 5 sonotrode and a drill is conceivable. Finally, the pin 60 would melt in the area that is in the cortical bone layer of the bone 10. However, the polymeric pin would encounter much less resistance to rotation in the areas of the pin 60 that extend beyond the cortical layer of bone 10 at both ends. Since the leading edge of the pin 60 is in the softer portion of the bone located next 10 to the cortical bone layer, the rotation of the assembly of sonotrode 50 and the pin 60 results in dislocation of the pin portion that is located in softer bone and seen in frame 3 of Fig. 9. Similarly, the portion of the pin 60 that is located in the implant plate 20 is also dislocated in relation to the portion of the pin 60 that is adjacent the cortical portion of the bone 10. This way the polymeric pin 60 is locked from below 15 the cortical bone layer and on top in the implant plate 20. Therefore, the pin 60 is prevented from being pulled out of the bone 10. Additional locking of the polymeric pin 60 is achieved by melting the pin 60 together with the material of the implant plate 20. As a result an angularly stable connection of the implant plate 20 to the bone 10 is achieved. 20 Frame I of Fig. 9 illustrates the method step in which a hole 16 is formed in the implant plate 20 and the bone 10. The detail A shows the cross-section of the hole 16. The polymeric pin 60 which is screwed on to the tip of the sonotrode all the way up to the stop and put into the hole 16, is shown in frame 2 of Fig. 9. Detail B shows a cross-sectional view of the hole 16 with the polymeric pin 60 inserted therein. 25 Frame 3 of Fig. 9 shows the condition of the polymeric pin 60 after a torque M was applied by the sonotrode 50. Distortion of the end regions of body of the pin 60 relative to the central region is visible in the area of the implant plate 20 and below the cortical portion of the bone 10. Detail C shows a bottom view of the leading end - 14 of the polymeric pin 60 which is twisted by 60 degrees relatively to the hole 16. Frame 4 of Fig. 9 finally shows the polymeric pin 60 in its final position welded together with the implant plate 20. Fig. 10 shows the tenth exemplary embodiment of the invention. In contrast to the 5 embodiments described above, the openings 13 of the tenth embodiment are formed in pairs. Fig. 10 shows an instrument 40 with two parallel drills which are synchronized contrarily by means of a one-level gear transmission with the translation relationship of 1:1. The drills are used to make openings 13 through the implant plate 20 and the bone 10 simultaneously. The drills are inserted in the bone 10 10 until a stop 41 touches the implant plate 20 and prevents the drills from going any further. Openings 13 may be threaded. Next a pin 60 having cylindrical arms 67 coupled by a bridge 68 is inserted in openings 13. Arms 67 are sized for insertion in the openings 13. Next, a sonotrode 50 is brought in contact with the polymeric pin 60. 15 Sonotrode 50 applies a force F and an ultrasound vibration U to the polymeric pin 60 as shown in frame 3 of Fig. 10. The ultrasonic energy melts the material of the bracket 60 and the melted material flows into the threaded holes 13 formed in the bone 10. The pin also melts at the interface of the pin 60 and the implant plate 10. The melting together of the pin 60 with the implant plate 20 forms a stable system 20 with a double anchorage in the bone 10. To promote the process of melting, spikes 69 are provided on the bridge 68. The spikes create areas of high energy density and thereby promote melting. The method and system according to the present invention, allows fracture stabilization wherein an implant plate is mounted on a bone. The implant plate is 25 angularly stable, i.e., the plate is attached such that it would not rotate around the attachment point. The fracture stabilization using the system and method of the invention can be carried out in combination with use of minimally invasive technology. A comparatively small operation trauma and small loss of blood as well - 15 as the reliable anchorage-in an-osteoporotic bone can-be achieved by angularly stable fixation of implant plates on the bone. The implants keep their retention force despite unfavourable conditions encountered in case of complicated fractures until the conclusion of the healing of the fractures in the osteoporotic bone. The firm 5 angularly stable connection between implant, joining element and the bone contributes to a considerably higher primary stability as well as to a lower rate of loosening. It is noted that the various aspects of the system and method of the invention described in context of one embodiment can also be used in combination with the 10 other embodiments of the system and method in which they were not explicitly mentioned. The bone can be provided with one, two, three or more holes depending on the situation of the fracture and the size of the implant plate. The use of a mark to control the positioning of the implant plate and/or the use of a jig on the implant plate or directly on the bone, for the preparing of the bone holes can be principally 15 incorporated into each of the described exemplary embodiments. Additionally, a variation of the form (or shape) of the drilling in the implant plate and in the bone and of the form (or shape) of the implant plate itself or the polymeric pins coordinated with it, is freely eligible (and envisioned) in each of the mentioned exemplary embodiments. The bores (or holes or openings or drillings) and thus also 20 the form (or shape) of the polymeric pin can be conical, stepped, straight, threaded or smooth or any combination thereof The material of the implant plate as well as the pins of each embodiment might be resorbable. Further, the material might be selected from a polylactid material family, for example from PLLA or PLDLA. Although the invention herein has been described with reference to particular 25 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 -16 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.

Claims

2. The system of claim 1, further comprising: a drill, the drill being adapted to form the opening and the hole in the bone adjacent the plate; and a jig, the jig being adapted to guide the drill.
3. The system of any one of claim 1 to 2, wherein the pin is selected from a group consisting of a conical pin, a dowel, a snap-fit dowel, a toothed dowel, a screw, a conical screw, a double pin, a stepped pin, a triangular pin, an asymmetrical pin and a pin having a thickened head.
4. The system of any one of claims I to 3, wherein the shape of the pin and the hole are complimentary and the pin is sized to be a close fit in the hole.
5. The system of claim 2, wherein the drill is selected from a group consisting of a bone drill, a conical bone drill, a threaded bone drill, a conical threaded bone drill, a double bone drill, a stepped bone drill, a bone drill with a triangle cross section, a bone drill with an asymmetrical cross section, and a Kirschner wire.
6. The system of claim I or 2, further comprising a sonotrode being adapted to apply energy to the pin and the plate.
7. The system of claim 6, wherein the drill and the sonotrode are combined in a single hand held instrument. 18
8. The system of any one of claims I to 7, wherein the plate is made from a material selected from PLLA or PLDLA.
9. The system of any one of claims I to 8, wherein the pin is made from a material selected from PLLA or PLDLA.
10. The system of any one of claims I to 9, wherein the pin has a bore along its longitudinal axis.
11. The system of claim 10, wherein the bore is threaded and adapted to receive a threaded tip of a sonotrode.
12. The system of claim 1 or 11, wherein the pin has a head and a body, and at least a portion of the body is conical and at least a second portion of the body is cylindrical.
13. The system of claim 1 or 11, wherein the pin has a head and a body, and at least a portion of the body has projections.
14. The system of claim 12 or 13, wherein a slot is formed in the body of the pin.
15. The system of any one of claims I to 14, wherein the shape of the pin and the opening are complimentary and the pin is sized to be a close fit in the opening.
16. A method of using the system according to claim 1, the method comprising the steps of: placing a plate on a bone; forming at least one opening in the plate and the bone, the opening being rotationally non-symmetric; inserting a pin in the opening; and applying energy to the pin to melt at least a portion of the pin thereby attaching the pin in the bone and melting the pin together with the plate such that rotational movement of the plate is prevented.
6046226-1:EEB 19 17. The method of claim 16, further comprising the steps of: placing a jig on the plate to guide a drill to form the opening; and marking the bone to locate the jig on the plate. 18. A system for fracture fixation substantially as hereinbefore described with reference to the accompanying drawings. Dated 7 March 2012 Stryker Trauma GmbH Patent Attorneys for the Applicant/Nominated Person SPRUSON & FERGUSON