• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Bone graft of a cortical bone material for surgically operative osteosynthesis with a cylindrical screw shaft (1) which is provided with an external thread, and a screw head (2) for initiating a driving torque, is proposed in the invention that the screw head (2) to a a screw head axis (S) has rotationally symmetrical outer circumferential surface, which is provided with an external thread, and at least two distributed around the screw head axis (S), in the direction of the screw head axis (S) extending axially and in the end face of the free end of the screw head (2) Recesses (3) for receiving a screwing tool, wherein the recesses (3) in each case by itself from the outer lateral surface in the direction of the screw head axis (S) extending side surfaces (4) are formed, which merge into each other in a surface area close to the axis. Due to the inventive design of the screw head (2) the introduction of the insertion torque are optimized and new surgical applications such as intramedullary splinting, an arthroscopic use and deep sinking of the graft in the bearing bone allows.
    公开号:AT520250A1
    申请号:T50672/2017
    申请日:2017-08-14
    公开日:2019-02-15
    发明作者:
    申请人:Surgebright Gmbh；
    IPC主号:
    专利说明:

    The invention relates to a bone graft made of a cortical bone material for the surgical operative osteosynthesis with a cylindrical screw shaft, which is provided with an external thread, and a screw head for introducing a screwing torque, according to the preamble of claim 1.
    Screws for the surgical operative osteosynthesis are conventionally made of metal or metal alloys. Screws made of resorbable material, such as polyglycolide and polylactide, are also known. However, screws of this type have several disadvantages in surgical practice. For example, screws made of metal or metal alloys have to be removed by a second operation and are subject to changes due to corrosion. This increases the costs in the health system and the health risks for each patient through a new operation. Most bone fractures are operated on using a plate and a variety of screws that have to be removed later.
    All resorbable materials in the human or animal body, in turn, form a more or less solid bridge between the bones to be osteosynthesized, depending on the material, but are dissolved, which negatively affects the strength of the osteosynthesis of the affected bones. Furthermore, some resorbable synthetic materials lead to large osteolyses in the surrounding bone during their degradation, that is to say the recipient bone escaping from the screw.
    Allogeneic bone screws (femur and tibia-corticalis), however, have several advantages. They are vascularized and rebuilt without rejection, and are particularly suitable for osteosynthesis where small bone fragments have to be joined, since the screw creates a load-bearing bone bridge during the operation, which improves from the time of the operation / 18 by is rebuilt and fully integrated and built into the living bones. Screws with a diameter of 3-4 mm are completely covered with tubes within 2 months. These bone screws can therefore also be referred to as bone grafts. In contrast, metal screws are more of an obstacle to new bone formation; in particular, their mere presence reduces the surface area that would be available for bone healing. Degradable materials in turn have their maximum strength at the time of the operation. The same disadvantages apply to them as to the metal screws, furthermore the strength decreases rapidly as soon as the breakdown process begins, whereby the bone site to be osteosynthesized is at least temporarily weakened again.
    Furthermore, a second operation to remove the osteosynthesis material is not necessary for bone screws made from allogeneic bone, since the bone is completely transformed into its own bone (not resorbed!). The risk of surgery for the patient is reduced, and the costs for the health care system are reduced. Allogeneic bone screws also do not interfere with the use of imaging methods, in contrast to metal screws, which leave disruptive artifacts in MRI and CT. Follow-up examinations are also possible without any problems and allow a better assessment of the healing success. Therefore, screws made of bone material are also suitable for being completely sunk in the bone, for example also in the context of an intramedullary placement of the screw in the medullary cavity, for example of tubular bones.
    However, when using screws made of allogeneic bone in surgical practice, it must be borne in mind that they differ significantly from metal screws in terms of screwing resistance and strength. Since they are obtained from allogeneic, human corticalis, it is not to be expected that knowledge of thread forms, screwing resistance or strength, as is known from screws made of metal, is readily transferable / 18. In fact, there is also a reason why screws made from autologous or allogeneic bone have so far not been widely used in surgical practice.
    In addition, it has been shown to produce screws made of cortical bone material that are unlike difficult tension or compression screws, especially with self-tapping threads. Tension or compression screws pull the two bone parts to be connected to each other during screwing in. For this purpose, the surgeon inserts the screw into a prefabricated bore, which advantageously has a self-tapping thread, the screw pressing both bone parts against one another after passage through the first bone part and entry into the second bone part. If the screw does not have a self-tapping thread, a thread must first be pre-cut in the pre-drilled hole before the screw can be screwed in. Not least because of this, the use of screws made of bone material has so far not been widely used, since the production of tension or compression screws, especially with self-tapping threads, was considered impossible because the required screwing-in torque could not be guaranteed.
    It is therefore the aim of the invention to improve screws made of cortical bone in such a way that the maximum possible screwing-in torque is increased and an optimal strength of the bone connection is achieved. In particular, applications such as the production of a tension or compression screw or the production of an intramedullary splint should be facilitated.
    These goals are achieved by the features of claim 1. Claim 1 relates to a bone graft made of a cortical bone material for the surgical operative osteosynthesis with a cylindrical screw shaft, which is provided with a thread, and a screw head for / 18
    Initiation of a torque. It is proposed according to the invention that the screw head has an outer circumferential surface which is rotationally symmetrical about a screw head axis and is provided with an external thread, and at least two recesses which are arranged distributed around the screw head axis and extend axially in the direction of the screw head axis and open into the end face of the free end of the screw head Receiving a screwing tool, the recesses are each formed by extending from the outer surface in the direction of the screw head axis side surfaces which merge into one another in a surface section near the axis.
    According to the invention, the screw head is thus also provided with an external thread and thus contributes to the strength of the bone connection. In particular, the screw head can also be screwed into the bone, for example, as part of an intramedullary splint without having to be cut off. The external thread is only interrupted by the axially extending recesses provided according to the invention for introducing a screwing-in torque, the side surfaces of which extend from the outer lateral surface in the direction of the screw head axis and merge into one another in a surface section close to the axis. Bone material thus remains in the area of the screw head axis; only axial recesses are milled into the outer surface of the screw head, which open into the end face of the screw head. Axial extensions of a screw-in tool can be axially inserted into these recesses on the end face. The insertion torque is subsequently exerted on the side surfaces of the recesses. Due to the design of the screw head according to the invention, however, the maximum final torque can be increased, since the strength of the screw head is increased by removing the smallest possible amount of bone material. In addition, the screwing-in torque is introduced in a kinematically favorable manner in the outer peripheral region of the screw head. The maximum screwing-in torque can be increased sufficiently in this way / 18 to enable the use of bone screws as tension or compression screws. In addition, the applicant was able to show that even a self-tapping thread for use in the cancellous bone area is possible and the bone screw made of cortical bone material is therefore able to be used in the cancellous bone without having to pre-cut a thread in the cancellous bone.
    The screwing-in torque can be additionally increased by the side surfaces of the recesses running from the outer surface area in the direction of the screw head axis being made convex and the surface portion near the axis being made concave. In this way, the contact area for the extensions of the insertion tool and the remaining amount of bone in the screw head can be increased. Both increase the torque. This also increases the bone surface area in the screw head area and improves ingrowth in the bearing bones.
    Furthermore, to increase the screwing-in torque, it is proposed that four recesses arranged symmetrically around the screw head axis are provided. In the course of the axial insertion of the extensions of the screwing tool, in the case of four recesses arranged symmetrically around the screw head axis, the screw head regions remaining between the recesses are grasped by the extensions of the screwing tool and, so to speak, “clamped” in the single digit millimeter range, thereby breaking off is prevented by bone material.
    Furthermore, it is proposed according to a preferred embodiment that the recesses have at their axial end facing away from the end face a region in which the depth of the recesses measured in the radial direction is steadily decreasing. If axial extensions of a screw-in tool are inserted axially into the recesses, these areas of reduced depth form a frictional connection to the extensions in addition to the positive engagement formed between recesses and extensions, as a result of which the coupling forces are increased. This also enables endoscopic or arthroscopic use of the screw. Another advantage of this design is that the production of the bone screw is made very easy, since it has to be sterilized in the course of production and undergoes a small amount of shrinkage, which could impair the form fit to the screwing tool. Due to the additional frictional connection, high coupling forces can be guaranteed, even if the bone material has shrunk during the course of sterilization.
    To carry out a tension or compression screw, it is proposed that the external thread running over the screw shaft and screw head have two sections of different thread pitch. These two sections each lie in the bone areas to be connected. Due to the different thread pitch, the bone areas to be connected are pressed together at a certain angle of rotation, which is of course the same for both sections.
    To carry out a screw with a self-tapping thread, it is proposed that the external thread running over the screw shaft and screw head have two sections with different thread outer diameters. The screw head is in the area with the larger thread outer diameter. With such a screw, in the course of the operative osteosynthesis, a core hole for the larger outer thread diameter in a first bone part can be prefabricated, and through the larger core hole a core hole for the smaller outer thread diameter in a second bone part, which is to be connected to the first bone part. The screw can now cut the respective core hole without having to first cut a thread with the section with the smaller outer thread diameter through the core hole for the larger / 18
    Insert the outer thread diameter until it can be screwed into the core hole of the second bone part. Subsequently, the screw with its section with a larger thread outer diameter enters the core hole of the first bone part and automatically cuts the thread there.
    Due to the design of the screw head according to the invention, the introduction of the screw-in torque is optimized, that is to say the transmission of the torque exerted on the screw head via a screw-in tool. The recesses according to the invention also allow the outer screw head diameter to be aligned with the outer diameter of the screw shaft and with the outer diameter of the screwing tool, and thereby also enable new surgical fields of application, such as, for example, in intramedullary splinting or in arthroscopic use. Another big advantage is that the screw graft can be sunk to any bone depth. The outer thread diameter of the bone graft is preferably between 6.0 mm and 3.5 mm.
    The invention is described below with reference to
    Exemplary embodiments explained in more detail with the aid of the accompanying figures. Here show the
    Fig. 1 shows an embodiment of an inventive
    Bone graft,
    2 shows the detail A of FIG. 1,
    3 shows a cross section along the sectional plane B-B of FIG.
    2,
    4 shows an embodiment of a further embodiment of a bone graft according to the invention, / 18
    5 shows the detail A of FIG. 4,
    6 shows the detail C of FIG. 4,
    7 shows a cross section along the sectional plane B-B of FIG. 5,
    Fig. 8 is a side view of an embodiment of a screwing tool for an inventive
    Bone graft,
    Fig. 9 shows the detail A of Fig. 8, and the
    10 shows a cross section along the sectional plane B-B of FIG. 9.
    1-3, which show a first embodiment of a bone graft made of a cortical bone material for the surgical operative osteosynthesis. The bone graft has a cylindrical screw shaft 1, which is provided with an external thread, and a screw head 2 for introducing a screwing-in torque, which also heals and does not have to be cut away like conventional screw heads. The screw head 2 also has an outer circumferential surface which is rotationally symmetrical about a screw head axis S and is likewise provided with an external thread, and four recesses which are arranged distributed around the screw head axis S and extend axially in the direction of the screw head axis S and open into the end face of the free end of the screw head 2 3 for receiving a screwing tool (see Fig. 2 and 3). The axially extending recesses 3 are each formed by side surfaces 4 which extend from the outer lateral surface in the direction of the screw head axis S and which merge into one another in a surface section near the axis. (see Fig. 3). The recesses 3 have at their axial end facing away from the end face an area in which the depth of the recesses 3 measured in the radial direction is steadily decreasing (see FIG. 2). As can be seen in particular from FIG. 3, the side surfaces 4 of the recesses 3, which extend from the outer circumferential surface in the direction of the screw head axis S, are convex, and the surface section near the axis is concave.
    As can be seen in FIGS. 1-3, the external thread with unchanged thread parameters extends both over the screw shaft 1 and over the screw head 2. The screw head 2 thus contributes to the strength of the bone connection. In particular, the screw head 2 can also be screwed into the bone, for example, as part of an intramedullary splint without having to be cut off. The external thread is only interrupted by the axially extending recesses 3 provided for introducing a screwing-in torque. Bone material with a core diameter D thus remains in the area of the screw head axis S, as shown in FIG. 3, since only axial recesses 3 are milled into the outer surface of the screw head 2, which open into the end face of the screw head 2. Axial extensions 5 of an insertion tool 6 (see FIG. 8) can be axially inserted into these recesses 3 on the end face. The insertion torque is subsequently exerted on the side surfaces 4 of the recesses 3. Due to the inventive design of the screw head 2, the maximum final torque can be increased, however, since the strength of the screw head 2 is increased by removing the smallest possible amount of bone material. In addition, the insertion torque is introduced in a kinematically favorable manner in the outer peripheral region of the screw head 2. In this way, the maximum insertion torque can be increased sufficiently to enable the use of bone screws as tension or compression screws. In addition, it is even possible to carry out a self-tapping thread for use in the cancellous bone area, so that the bone screw made of cortical bone material is therefore able to be used in cancellous bone without having to pre-cut a thread in the cancellous bone beforehand.
    4-7 show a further embodiment of a bone graft according to the invention, in which the external thread running over screw shaft 1 and screw head 2 has two sections of different thread pitch and external thread diameter. The screw head 2 lies in the area with the larger outer thread diameter, which has a thread pitch of 0.8 mm, for example. The area with the smaller outer thread diameter has, for example, a thread pitch of 1 mm. Such an embodiment is particularly suitable for executing a tension or compression screw. In their surgical application, the two sections each lie in the bone areas to be connected. Due to the different thread pitch, the bone areas to be connected are pressed together at a certain angle of rotation, which is of course the same for both sections.
    To carry out a screw with a self-tapping thread, it is proposed that the external thread running over screw shaft 1 and screw head 2 have two sections with different thread outer diameters. With such a screw, in the course of the operative osteosynthesis, a core hole for the larger outer thread diameter in a first bone part can be prefabricated, and through the larger core hole a core hole for the smaller outer thread diameter in a second bone part, which is to be connected to the first bone part. The screw can now be inserted into the respective core hole without having to cut a thread beforehand, with the section with the smaller outer thread diameter through the core hole for the larger outer thread diameter until it can be screwed into the core hole of the second bone part. Subsequently, the screw with its section with a larger thread outer diameter enters the core hole of the first / 18th
    Part of the bone and automatically cuts the thread there.
    8-10 shows a possible embodiment of a screwing tool for the bone graft according to the invention. It has four projections 5 projecting axially from a cylindrical shaft, which can be inserted axially into the recesses 3 of the bone graft on the face side until they engage the recesses 3 with a large friction fit. The frictional engagement is increased by the side surfaces 4 of the recesses 3, which run convexly from the outer circumferential surface in the direction of the screw head axis S, and by the depth of the recesses 3, which decreases continuously in the radial direction, at its axial end facing away from the end surface.
    Due to the inventive design of the screw head 2, the introduction of the screw-in torque is optimized, that is, the transmission of the torque exerted on the screw head 2 via a screw-in tool. The recesses 3 according to the invention also allow the outer screw head diameter to be aligned with the outer diameter of the screw shank 1 and with the outer diameter of the screwing tool, and thereby also enable new surgical fields of application, such as, for example, in intramedullary splinting.
    权利要求:
    Claims (6)
    [1]
    claims:
    1. Bone graft made of a cortical bone material for the surgical operative osteosynthesis with a cylindrical screw shaft (1), which is provided with an external thread, and a screw head (2) for introducing a screwing-in torque, characterized in that the screw head (2) one by one Screw head axis (S) rotationally symmetrical
    Has outer surface, which is provided with an external thread, and at least two recesses (3) arranged around the screw head axis (S), axially extending in the direction of the screw head axis (S) and opening into the end face of the free end of the screw head (2) of a screwing tool, the recesses (3) being formed in each case by side surfaces (4) which extend from the outer circumferential surface in the direction of the screw head axis (S) and which merge into one another in a surface section close to the axis.
    [2]
    2. Bone graft according to claim 1, characterized in that the side surfaces (4) of the recesses (3) extending from the outer lateral surface in the direction of the screw head axis (S) are convex and the surface section close to the axis is concave.
    [3]
    3. Bone graft according to claim 1 or 2, characterized in that four symmetrically around the
    Screw head axis (S) distributed recesses (3) are provided.
    [4]
    4. Bone graft according to one of claims 1 to 3, characterized in that the recesses (3) have at their axial end facing away from the end face a region in which the depth of the recesses (3) measured in the radial direction is continuously reduced.
    13/18
    [5]
    5. Bone graft according to one of claims 1 to 4, characterized in that the screw thread (1) and screw head (2) extending external thread has two sections of different thread pitch.
    [6]
    6. Bone graft according to one of claims 1 to 5, characterized in that the screw thread (1) and screw head (2) running external thread has two sections with different thread outer diameter.
    类似技术:
    公开号 | 公开日 | 专利标题
    EP1082063B1|2004-09-01|Surgical blind rivets with closing elements
    DE102004027881B4|2006-06-01|Bone screw and osteosynthesis device
    EP1096892B1|2004-11-10|Osteosynthesis screw, especially for application by a translaminar vertebral screw
    EP1440664A2|2004-07-28|Implant for osteosynthesis
    DE3541597A1|1986-06-05|BONE TREATMENT DEVICE
    EP2124783A2|2009-12-02|Implant for fracture care
    DE2454181B2|1979-06-28|Ceramic implant
    DE102006054534A1|2008-05-21|Fixation element for bone fragment
    AT520250B1|2019-11-15|bone screw
    DE10356920B4|2007-02-22|In a human jaw endostal einschraubbares dental implant for receiving and fixing a denture
    EP1527749A2|2005-05-04|Dental implant screwable in the human jaw for receiving and fixing a dental restoration
    EP2384712B1|2014-03-12|Bone screw
    EP3209232B1|2019-10-09|Anchor implant
    DE102019000965B4|2020-12-24|Bone anchoring device for pedicle access
    DE4129724A1|1993-03-18|Hip joint prosthesis for femur with multiple fracture - has prosthesis shaft secured to femur by transverse pins
    AT522112B1|2021-01-15|Bone graft
    DE102007029090A1|2008-12-24|Device for osteosynthesis, particularly bone fracture near joint, has pin for implantation into abarticular bone, and proximal longitudinal ring element provided for implantation into bone fragment near joint
    AT517141B1|2019-08-15|bone screw
    WO2013164106A1|2013-11-07|Bone screw
    AT500081A1|2005-10-15|IMPLANT FOR THE MUTUAL FIXATION OF TWO BONE FRAGMENTS
    EP1654989A2|2006-05-10|Pin for the fixation of an implant under load
    EP2844170B1|2017-02-01|Bone screw
    AT507407B1|2010-05-15|THREADED BOLTS FROM ALLOGENIC BONE MATERIAL
    EP0408696A1|1991-01-23|Osteosynthesis implants
    同族专利:
    公开号 | 公开日
    EP3668427A1|2020-06-24|
    AT520250B1|2019-11-15|
    WO2019034522A1|2019-02-21|
    CN110996821A|2020-04-10|
    US20190307496A1|2019-10-10|
    AU2018317718A1|2020-02-20|
    CA3071682A1|2019-02-21|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    WO2001064141A1|2000-03-02|2001-09-07|Regeneration Technologies, Inc.|Cervical tapered dowel|
    AU696997B2|1994-09-15|1998-09-24|Howmedica Osteonics Corp.|Conically-shaped anterior fusion cage and method of implantation|
    US6045554A|1996-07-16|2000-04-04|University Of Florida Tissue Bank, Inc.|Cortical bone interference screw|
    WO2000066011A1|1999-05-05|2000-11-09|Michelson Gary K|Screws of cortical bone and method of manufacture thereof|
    EP1110510B1|1999-12-23|2002-03-27|Karl Storz GmbH & Co. KG|Screw driven non-centrally|
    EP1257219B1|2000-02-24|2012-01-18|Stryker Instruments|Device for heating bioabsorbable plates|
    US7670362B2|2003-06-13|2010-03-02|Tyco Healthcare Group Lp|Multiple member interconnect for surgical instrument and absorbable screw fastener|
    JP2013534149A|2010-07-28|2013-09-02|ジンテスゲゼルシャフトミットベシュレンクテルハフツング|System or bone fixation using biodegradable screw with radial cutout|
    CN203988326U|2014-07-10|2014-12-10|苏州吉美瑞医疗器械有限公司|A kind of hollow forcing screw|
    CN204468171U|2014-12-26|2015-07-15|北京大清生物技术有限公司|Biological extruding nail|AT517141B1|2015-04-15|2019-08-15|Pastl Klaus|bone screw|
    US11264430B2|2016-02-18|2022-03-01|Chengdu Boe Optoelectronics Technology Co., Ltd.|Pixel arrangement structure with misaligned repeating units, display substrate, display apparatus and method of fabrication thereof|
    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    AT506722017A|AT520250B1|2017-08-14|2017-08-14|bone screw|AT506722017A| AT520250B1|2017-08-14|2017-08-14|bone screw|
    CN201880052478.5A| CN110996821A|2017-08-14|2018-08-09|Bone screw|
    PCT/EP2018/071619| WO2019034522A1|2017-08-14|2018-08-09|Bone screw|
    AU2018317718A| AU2018317718A1|2017-08-14|2018-08-09|Bone screw|
    US16/470,837| US20190307496A1|2017-08-14|2018-08-09|Bone screw|
    EP18752488.9A| EP3668427A1|2017-08-14|2018-08-09|Bone screw|
    CA3071682A| CA3071682A1|2017-08-14|2018-08-09|Bone screw|
    [返回顶部]