• 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:
    Intramedullary fixation device, with an intramedullary stem (2) provided for its introduction into a bone (1) formed by a central screw (4) with a first free end that has a stop (7) and a second free end with a nut of prestressing (8) and in between an alternate series of expanders (3) and bolts (5) whose contact surfaces with the expanders (3) are wedge-shaped. The bolts (5) or expanders (3) may have none, or one or more of a variation of the dimensions of the different geometrical parameters, in accordance with the adjacent expanders, along the length of the implant, as well as the screw central (4) be of variable section. The device can have different additional components, such as an osteotomic base (9) for muscle attachment (m). (Machine-translation by Google Translate, not legally binding)
    公开号:ES2599389A1
    申请号:ES201631220
    申请日:2016-09-19
    公开日:2017-02-01
    发明作者:José EXPÓSITO OLLERO；José ALBELDA VITORIA；Juan Víctor HOYOS FUENTES；Ana VALLÉS LLUCH；Antonio SILVESTRE MUÑOZ
    申请人:Universidad Politecnica de Valencia；
    IPC主号:
    专利说明:

    Intramedullary fixation device SECTOR OF THE TECHNIQUE
    The present invention relates to a non-cemented intramedullary fixation device, which is inserted into the medullary canal of the long bones and allows internal or external prosthetic elements to be arranged or assist in the reconstruction of fractures, among other uses. STATE OF THE TECHNIQUE
    For the fixation of elements by intramedullary stems there are several ways. The most common is the insertion of a rigid, threaded rod (in exoprotetization applications) or percussed inside the bone. This method can cause damage to the bone wall or even breakage.
    From US2012065638 a nail or flexible system is known for the treatment of fractures that can be introduced by parts into the medullary canal of the bone before producing the expansion of its ends and thus the interlocking.
    This solution is improved by better distributing the stresses in all or most of the length of the bone, as well as to facilitate the operation in traction and compression. BRIEF EXPLANATION OF THE INVENTION
    The invention consists of an intramedullary fixation device according to the claims.
    The device comprises a rod that improves and facilitates the method of implantation and initial fixation of the prosthesis to the medullary canal, as well as the transmission of tensions and deformations to the bone with the aim of restoring the physiological processes of bone apposition and resorption.
    It is a device with interference distributed along the medullary canal, and with variable stiffness of the stem, which reduces the screening of tensions and improves the process of bone apposition, unlike systems with high modulus of elasticity that accumulate in an area Small transmission of the tensions to the bone derived from the loads to which the system is subjected during normal use.
    Unlike most of the current rigid systems that accumulate tensions and deformations in the bone at one end of the stem, stimulating excessive bone growth in said strip while bone resorption occurs in the rest of the cortical bone, It has been verified in simulations how the designed device is capable of transmitting to the bone the physiological levels of stresses and deformations in a homogeneous and extended way along the entire wall of the medullary canal, and adapted to the state of loads to which the system is subjected in every moment
    In particular, the intramedullary fixation device of the invention comprises an intramedullary stem intended for insertion into a bone, the rod being formed by a central screw with a first free end having a stop and a second free end with a prestressing nut. and in between an alternate series of expanders and bolts. The surfaces of the bolts in contact with the expanders decrease the cross section along the longitudinal direction progressively in both directions (what will be referred to as wedge form), becoming spindle-shaped, either round, square or any other section.
    Preferably, the rod bolts may have one or more variations of the dimensions of the geometric parameters, in accordance with the adjacent expanders, along the length of the rod, and / or the central screw may have a variable section in its length.
    This basic solution can be completed in several ways:
    Adding a solid cylinder between the stop and the prestressing nut, among the other bolts and expanders, replacing one or more of the latter. Preferably, the bolt adjacent to the solid cylinder will be replaced with a modified one so that the wedge faces only contact the adjacent expander.
    Adding at the second free end of the stem an osteotomic base with an anchor for an exo-prosthesis that can have a percutaneous collar. The osteotomic base may fix the free ends of part of the residual musculature by means of a series of handles formed by bars perpendicular to the axis of the stem.
    Arranging a prosthetic component at the second free end of the stem. For example a femur head.
    Incorporating at the second free end of the rod a perforated cylinder for the passage of fixing nails.
    Preferably, between each pair of adjacent expanders there is a space aligned with the central part of the bolts. That is, the expanders do not touch each other to allow greater play or freedom of movement between them, favoring bone deformation. If desired, this space can be filled with a soft silicone washer or a similar material with a very low elastic modulus.
    The load transfer from the rod to the bone by friction is controlled at each point by the relationship between the stiffness of the rod and the bone, and by the radial deformation of the expanders produced by the interlocking. In this system, the first effect is controlled by the variation of the central screw section, the expander elements and the bolts. The second is controlled by the inclination or conicity of the expanders and bolts in each zone and their length, which generates a summation effect of the frictional forces existing between the various components. This facilitates that bolts furthest from the load are introduced to a greater or lesser extent (depending on the geometric variation used) in the conical bore of the cylinder when subjected to loads, thus generating varying levels of interference along the length of the intramedullary canal, obtaining a rod of variable stiffness.
    In the case of exo-prosthesis fixation, the osteotomic base offers a series of longitudinal handles designed to house the functional suture of part of the residual musculature. This form of functional suture is intended to create a union that is strong and stable enough to be able to develop a program of pre and post-amputation muscle rehabilitation, aimed at reactivating the functionality of certain muscle groups avoiding the process of atrophy of these tissues, improving the proprioception function and transmitting to the bone the tension levels generated by the sutured residual muscle groups.
    DESCRIPTION OF THE DRAWINGS
    For a better understanding of the invention, the following figures are included.
    Figure 1: an exploded view of a first embodiment of the device.
    Figure 2: A) view of an example of osteotomic base applicable to the device. B) Cut an example of a device with osteotomic base. C) Examples of placement of the osteotomic base in the body of a patient.
    Figure 3: Section of a third embodiment, with an example of prosthetic component.
    Figure 4: Several examples of device applied to fractures.
    Figure 5: Examples of placement of central bolts, screws or cables and variable section expanders in custom applications. EMBODIMENTS OF THE INVENTION
    Next, an embodiment of the invention will be briefly described as an illustrative and non-limiting example thereof.
    The invention relates to an intramedullary wall fixation device of a bone (1), formed by a rod (2) and usually an additional component that will depend on the objective sought.
    The rod (2) is formed by a series of expanders (which can be decoupled from the central bar) (3) formed by biocompatible, polymeric or metallic modules or cylinders. For example, the expanders (3) will be coated with titanium alloy, hydroxyapatite or any other biocompatible coating material that promotes subsequent osseointegration with the bone (1). The modules will be arranged in a central screw (4) that passes through the expanders (3) through an internal shaft.
    Between each pair of consecutive expanders (3) there are two bolts (5), also mounted on the central screw (4) (although they may be disengaged from it), whose faces that contact the expanders (3) are wedge shaped so that the central part of each bolt (5) is of greater section than both ends. By bolts (5) it will have the complementary geometry, but a somewhat smaller section so that interference between the two occurs. The length of the conical zones, as well as the spaces between expanders (3), can also be variable.
    By arranging a wedge in both directions of the bolt (5), any tensile stress
    or compression on the rod (2) increases the interlocking or wedging thereof. In this way, the device is capable of generating additional stresses on the bone both in the lower limb, which works mainly in compression, and in the upper limb, which works mainly in tension.
    In this way, when two consecutive expanders (3) are approached, the wedged geometry of the elements will cause the progressive interlocking of said components with each other, causing the expansion of the expanders (3) radially and their diameter increase. The interlocking can be limited by differences in the inclination of the wedge, for example by making the bolts (5) with flat tip termination, including a final part of greater inclination or by a central step as will be discussed later. In this way, when the expander (3) and the bone (1) come into contact, a pressure is exerted on the latter which produces the initial anchoring by friction of the device to the bone (1).
    To facilitate this expansion, the expanders (3) may have lines of weakness (6), grooves or any solution that reduces their stiffness. These grooves also serve to obtain greater fixation of the implant to the bone and prevent relative rotation between both components.
    The central screw (4) will have a first stop (7) at a first free end, which will be the one that is first introduced into the medullary canal of the bone (1), which can be integral with the central screw (4), or be a independent element threaded or fixed by a pin. At the second free end of the central screw (4) a prestressing nut (8) will be arranged which can be threaded onto the second free end to produce the expansion of the expanders (3). It is also possible that the prestressing nut (8) is integral with the central screw (4), and its rotation produces its threading on the stop (7). In some applications the prestressing nut (8) will be cylindrical so that it can rotate within the medullary canal and perform the prestressing, while in others it may have a hexagonal shape or any other. Preferably it will have a step in its part oriented inwards to perform support and compression in the bone.
    The stop (7) may also have a wedge similar to that of the bolts (5), or comprise an anchoring system formed by an interlocking element, as will be described later.
    Generally, the central screw (4) passes through the additional component of the device, so that the prestressing nut (8) also makes the connection between the additional component and the rod (2). If desired, a conical surface may be provided,
    nearest expander (3). The same can be said of the top (7).Preferably, the additional component will have means to prevent rotation.
    an ad-hoc piece in the additional component, the contact surface not being cylindrical so that there is no possible axis of rotation.
    The system designed allows customization of the implant according to the specific needs of the patient's anatomy, the type of application (endo and exoprosthesis of the upper or lower limb) and the level and type of intervention to be performed. This is achieved thanks to a combination of different geometric variations of the components with the aim of controlling the progressive interlocking (figure 5):
    - Size and slope of the bolts (5) and their arrangement: from highest to lowest or
    Expanders (3) will vary their internal shape to fit the bolt (5).-Section of the central screw (4) along the longitudinal direction.-Control of the amount of interlocking or coining.
    Some examples of application of these variable geometries are: To obtain a uniform distribution of tensions in the bone, the most convenient option is that the stiffness of the central screw (4) and the locking angle of the bolts (5) and expanders (3 ) increase as we move away from the second free end of the stem. To fix an external prosthesis in the upper limb, it is convenient to increase the interference between the bolts (5) and the expanders (3) to maintain the same levels of interlocking on the bone. Because the maximum interlocking is limited by the geometry of the components, to achieve a greater maximum interlocking, the interference between both elements can be increased by increasing the bolt section (5) while maintaining the expander section (3) with original dimensions, or reducing the section of the expander (3) maintaining that of the bolt (5) with the original dimensions. This set of sections allows to select and optimize the areas of fixation of the implant and the transmission to the bone of tensions and deformations.
    On the other hand, in a lower limb, the stem will mainly bear loads of
    Compression and external load will add itself to the pretense effect.
    Figure 5 shows several ways to perform this variation:
    A. Central screw with variable cross-section and expanders and bolts with constant interlocking angle.
    B. Central screw with variable cross-section in the opposite direction to the previous one and the variable interlocking angles.
    C. Central screw with constant section and expanders and bolts with variable cross section.
    D. Similar to Figure 5C, but with symmetric bolts.
    Each of the above combinations, introduces changes in the transmission and distribution in the bone of tensions and deformations. The different levels and patterns of stresses and deformations that are generated on the bone with the use of one or another combination can be used to optimize the function of the implant based on the application, the dimensions of the bone section, the level of loads to endure etc.
    The combination shown in Figure 5A produces levels and a different pattern of stresses and deformations depending on the stage it is in. During the implantation and osseointegration stage without load, a pattern of tensions is observed that divide the bone (1) into two zones, the area of the upper half with higher tensions, and the area of the lower half with lower tensions. However, once the implant is completely osteointegrated and the bone (1) has adapted to the initial deformation of implantation, when the system is subjected to loads areas appear in the bone (1), coinciding with the spaces between expanders (3), with tensions above the physiological ones and the rest of the medullary canal is shown with tensions at the physiological level. This type of combination could be used, for example, in cases where a greater force of fixation of the implant to the bone (1) is required both in the osseointegration phase without load, as in the long term period. It could also be used in patients with greater bone wall thicknesses (1), who need a greater stimulus for bone apposition, or the characteristic pattern of initial tensions and deformations that divide the bone (1) into two tension zones can be used to stabilize fractures located in a specific half of the bone without exerting excessive force on said area, while achieving a greater force of fixing the nail in the other half of the bone (1).
    On the other hand, the combination shown in Figure 5B, during the implantation and osseointegration phase without loads, is capable of generating a homogeneous tension distribution along the entire wall of the bone channel. The stress levels generated in this phase are at the level of the lowest tensions generated by the previous combination for the same phase. This can be used in applications where the structural quality of bone (1) is poor or weakened throughout its length, or in smaller sections of bone (1). During the osseointegration phase with the combination of Figure 5B a tension pattern appears in which a division of the bone (1) into two zones (the same effect as with the previous combination for the initial phases) is shown. Half of the bone (1) closest to the prosthetic component or osteotomic base is under load levels greater than the upper area (always within the physiological load levels). This effect can be used depending on the member to be protected (upper or lower) and the type of load to be supported (traction or compression) to homogenize the total stresses (due to the bending moments and those due to the expansion of the elements) that are transmitted along the bone (1).
    Using other geometric combinations (not shown in Figures), such as the one shown in Figure 5A by adding the variation of the angles of the conical elements, a more similar and homogeneous stress pattern is achieved in all phases (initial implantation, osseointegration no load and long term).
    In Figures 5C and 5D two ways of varying the cross-section of the bolts (5) and the expanders (3) along the length of the implant are shown. In both figures the wedge section of the bolts (5) is decreased towards the first end of the central screw (4) while the section of the expanders (3) is widened. The difference between both embodiments lies in the element where the variation of the section is introduced. In an image, the section change is carried out within at least one bolt (5), the expanders (3) being symmetrical with respect to the transverse plane. In the other section varies within one or more expanders (3), the bolts (5) being symmetrical. The effect that introduces this geometric variation in the levels and distribution of stresses and deformations is the same in both images, however it is preferred to make the section changes within the expanders (3), instead of the bolts (5), to avoid the concentrations of tensions that appear in the changes of step in the bolts (5). This geometric combination produces a different pattern of tensions than those described above, promoting an increase in tensions progressively as it moves away from the load application area, regardless of the direction of decrease or increase in the section of the components.
    If the central screw (4) decreases its section as it approaches the first free end (figure 5C), it is not possible to insert the central screw (4) prior to the insertion of the bolts (5) and expanders (3). In this case, to prevent the elements from being misaligned and to be able to introduce the central screw (4), the stop (7), disengaged from the central screw (4), consists of a fixing system formed by a first half bolt (51) , combined with expander means (31), and a second half bolt (52). The second half bolt (52) has at its end without wedge a threaded pin that is inserted and threaded into the first half bolt (51), while on the side with wedge it has a threaded hole for the central screw (4). In this way, the stop (7) is locked in the proper position prior to the introduction of the other elements of the device, by threading the bolt means (51,52) by tightening the expander means (31). This stop (7) is also applicable to any other form of central screw (4), the threaded pin can be replaced by the central screw itself (4) when it is installed from the beginning.
    When the bolts (5) have different geometric characteristics, the expansion of each expander (1) or pair of expanders (1) is different, so that the fixation is variable along the bone. Likewise, bolts (5) with coined ends of different size or maximum section may be arranged, which implies a central step (such as that of the upper bolt (5) of Figure 5C), so that the change is more abrupt.
    By combining the intramedullary stem (2) with the different implant components, it is intended to cover different applications, as will be indicated in the examples described below.
    An example for exo-protetization of extremities by DSA technique (direct skeletal attachment) is shown in Figures 2A and 2B. Figure 2C shows two ways of attaching it to the bone (1), the musculature (M), the adipose tissue (A) and the epidermis (E).
    This case requires an osteotomic base (9), which can have handles (10) intended for the functional suture of the musculature (M) by means of pseudotendons surrounding these handles (10). As can be seen in the figures, each handle (10) consists of a curved or straight bar, without edges, perpendicular to the axis of the rod (2). The number of handles (10) will depend on the amount of muscles to be fixed, but will normally be 2
    5. Normally, the end of the osteotomic base (9) opposite the stem (1) will pass through the soft tissues and will preferably be threaded to provide a percutaneous collar such as those shown in US2007060891 (incorporated by reference). The collar will be below the epidermis (E) that is crossed by the end of the osteotomic base where said collar is fixed and that also serves as an anchor (11) of the exoprosthesis. It is also possible not to have handles (10) but a series of holes for the passage of suture thread from the musculature to the osteotomic base (9), as is already known in the art.
    The osteotomic base (9) will be connected to the last expander or bolt through the second free end of the rod (2), by means of tongue and groove, for example, so that the compression loads suffered by the prosthesis during daily activities are transmitted to the stem ( 2) and assist in the interlocking.
    Any tensile load will be transmitted from the osteotomic base (9) to the bone by two paths:
    Through the contact between the osteotomic base and the prestress thread fixed to the central screw (4), and through this screw to the bolts and the expander elements that exert pressure against the bone.
    Through the direct union between the intramedullary cylinder of the osteotomic base
    and the area of the bone in contact with said cylinder. Flexural stresses will pass directly from the osteotomic base (9) to the bone (1) through their direct contact, for example through a cylindrical end of the osteotomic base (9) partially inserted into the medullary canal. Moreover, by suturing the main muscles of each member to the handles (10), the muscles partially compensate for the stresses of the bone (1) due to the flectorial loads, which in turn allows them to keep the muscles active and avoid the distal tissue flaps.
    Figure 3 shows the application in endo-protetization of long bone joints. In this case, the additional component is a prosthetic component (12) for the joint replacement of the femoral head. It has a longitudinal through hole to house the central screw (4) and the prestressing nut (8).
    Several examples of application in fracture reconstruction are shown in Figure 4. The system is capable of compressing and stabilizing the different parts of the fractured bone (1) after the damage suffered in a simple, safe, direct way and without the need to machine and align through holes in the diaphyseal bone that weaken the structural section of the bone wall , entail a high technical difficulty and increased intervention time.
    For fractures it is proposed to include inside the rod (2), combined with the expanders (3) and bolts (5), a solid polymeric or metallic cylinder (13). As can be seen in Figure 4, the objective of the solid cylinder (13) is to stabilize the fracture zone, which corresponds to its place of placement in the rod (2). This way there is no expansion in the damaged area. Since it is not expandable, the introduction of the bolt (5) at the ends of the solid cylinder (13) will not affect its dimensions. In any case it is preferred to have a specific adapted bolt (14), with one wedge end for expansion of the expander (3) and the other with the relevant hitch for the solid cylinder (13). Depending on the position and length of the solid cylinder (13), the adapted bolt (14) will be arranged at one end or both.
    If the passage of nails (15) for fixing the bone head (1) is necessary, the element
    or prestressing nut (8) will be a perforated cylinder that allows the placement of these nails in the desired orientation.
    For fractures just below the greater trochanter or that are too close to the second free end of the central screw (4) (epiphyseal zone), it is proposed to dispense with the expander system (3) and bolt (5) at the second free end, and generate bone stabilization (1) (system prestressing) using a prestressing nut
    (8) (figure 4). In this case, the union between the cylindrical prestressing nut (8) (which can be drilled for the passage of fixing nails) and the solid cylinder (13) must allow its relative rotation by means of a cylindrical male-female joint. In this type of fractures, in
    If greater stability is required along the channel, expanders (3) can be added at the first free end of the screw to achieve greater tensile strength and better transmission and distribution of stresses and deformations along the medullary canal. .
    In general, the rod (2) of the device is adaptable to different prosthetic terminations by machining in them a longitudinal hole that allows prestressing and fixing said terminal to the rod (2) through the central screw (4) and the nut prestressing (8).
    As shown in Figure 1, preferably a space will be left between each pair of expanders (3), aligned with the bolts (5) in their central part. If applicable, a soft silicone washer (17) can be installed, which can be part of the bolt (5) or the expander (3). These spaces (with a negligible modulus of elasticity) are important in the way in which tensions and deformations are transmitted to the bone when the system is completely osteointegrated and subjected to loads, allowing the bone (1) to be compressed or compressed. stretch along its length.
    Normally, the procedure of initial implantation and fixation of the stem to the medullary canal, once evacuated inside the bone (1), begins with the introduction of the central screw (4), through the first free end where the stop (7) is arranged. ). Subsequently, the bolts (5) and expanders (3) are introduced without using interference with the bone in the initial insertion. If necessary by the application, a solid cylinder is introduced
    (13) in the desired position.
    The required additional component is added, and the prestressing nut (8) is introduced. When tightening this, the deformation of the expanders (3) that produce the progressive interlocking of the intramedullary components to the bone is produced. This avoids the use of implantation methods consisting of machining a thread in the medullary canal or pressuring the stem, which seriously damages the endostium and can lead to bone breakage during implantation.
    In the event that the bolts (5) and the expanders (3) are coupled to the central screw (4), for example by means of a thread, they must be inserted and threaded independently generating the wedging and fixing of each element in a way separated when introduced into the channel and fixed to the screw.
    Some geometric combinations of the developed intramedullary stem generate additional stresses and deformations on the bone during the osseointegration phase and once the system is completely osteointegrated, depending on the physiological loads acting, through the progressive interference generated by the interaction between the various components (active system). Due to the interlocking by coining in both directions of the load, all combinations of the rod (2) are capable of producing interference with the medullary canal and the consequent fixation to it during tensile and compression loads, even without the need for produce osseointegration.
    The anchorage is effective even when the bone adapts to the initial pressure and the prestressing of the assembly that the rod exerts on the walls of the canal disappears, but is not yet osteointegrated. Thus it is possible to start an early rehabilitation that improves the osseointegration process.
    Regarding the extraction method, the designed device allows the removal of the stem (2) from the spinal canal without damaging the structural integrity of the bone (1), by allowing the joint between the cylinders and the bone to be removed in a simple and straightforward way . The prestressing nut is removed and the stresses of the different elements are released. Once completely relaxed, the center screw (4) can be removed. Because, preferably, the expanders will be of a polymeric material, the union of these with the bone can be eliminated by using a crown drill with a diameter coinciding with that of the medullary canal.
    权利要求:
    Claims (1)
    [1]
    1-Intramedullary fixation device, with an intramedullary stem (2) intended for insertion into a bone (1) characterized in that the stem (2) is formed by a central screw (4) with a first free end having a stop (7) and a second free end with a prestressing nut (8) and in between an alternate series of expanders
    (3) and bolts (5) whose contact surfaces with the expanders (3) are wedge-shaped.
    2-Device according to claim 1, wherein the bolts (5) have different geometric dimensions, in accordance with the adjacent expanders (3), along the length of the rod (2).
    3-Device according to claim 1, wherein the rod (2) also comprises a solid cylinder (13) between the stop (7) and the prestressing nut (8), preferably connected to the expander (3) or adjacent element by a adapted bolt (14) with wedges at one end.
    4-Device according to claim 1, which at the second free end comprises an osteotomic base (9) with an anchor (11) for an ex-prosthesis and a percutaneous collar.
    5-Device according to claim 4, wherein the osteotomic base (9) can have a series of handles (10) formed by paths perpendicular to the rod (2).
    6-Device according to claim 4, wherein the osteotomic base (9) has a cylindrical end for partial insertion into the bone (1).
    7-Device according to claim 4, wherein the osteotomic base (9) has a cylindrical end designed to pass soft tissues, preferably threaded for the adaptation of a percutaneous collar and an ex-prosthesis.
    8-Device according to claim 1, which has a prosthetic component (12) at the second free end of the rod (2).
    Device according to claim 1, which has a space or zone with negligible elastic modulus between each pair of expanders (3), aligned with the central part of the bolts (5).
    Device 10 according to claim 9, having a soft silicone washer (17)
    or similar material in the space between expanders (3).
    11-Device according to claim 3, whose prestressing nut (8) is cylindrical and disposed adjacent to the solid cylinder (13) at the second free end of the rod
    10 (2) having a step in its part oriented inwards, and where the union between the prestressing nut (8) and the solid cylinder (13) allows the relative rotation between both components.
    12-Device according to claim 11, wherein the prestressing nut is perforated 15 for the passage of fixing nails (15) in the second free end of the rod (2).
    13-Device according to claim 1, wherein the central screw (4) is of variable section in the longitudinal direction.
    A device according to claim 1, wherein the stop (7) is disengaged from the central screw (4) and is formed by a first half bolt (51) on whose only wedge an expander means (31) is arranged, and a second half bolt (52) with a threaded pin in the first half bolt (51) and a threaded hole for the central screw (4).
    类似技术:
    公开号 | 公开日 | 专利标题
    ES2342828T3|2010-07-15|SPINAL FIXING DEVICE.
    US6551322B1|2003-04-22|Apparatus for implantation into bone
    US6544265B2|2003-04-08|Apparatus for implantation into bone related applications
    US7601167B2|2009-10-13|Apparatus for implantation into bone
    ES2236470T3|2005-07-16|INTERESPINOUS VERTEBRAL IMPLANT.
    US7658754B2|2010-02-09|Method for the correction of spinal deformities using a rod-plate anterior system
    ES2297487T3|2008-05-01|IMPLATE ORTHOPEDIC AND ASSEMBLY OF OSEO SCREW.
    JP5602735B2|2014-10-08|Bone anchor
    EP1024762B1|2003-07-30|Bone fixation device
    ES2252800T3|2006-05-16|APPARATUS FOR ANCHORING GRAPHICS OF AUTOGENOUS OR ARTIFICIALS IN BONE.
    US20070073293A1|2007-03-29|System and method for flexible correction of bony motion segment
    US20160296258A1|2016-10-13|Translaminar interspinous stabilization system
    US20090138051A1|2009-05-28|Device for creating a bone implant
    CN104244853A|2014-12-24|Bump cut on hole edge
    US20110040383A1|2011-02-17|Spinal column implant
    ES2599389B2|2017-12-29|INTRAMEDULAR FIXING DEVICE
    ES2763394T3|2020-05-28|Reinforcement implant for an elongated bone, especially a femur
    AU2020218873A1|2021-10-07|Bone-anchoring device for a pedicle access
    US10278745B2|2019-05-07|Interlaminar, interspinous stabilization devices for the cervical spine
    US10058357B2|2018-08-28|Connector for spinal implant system
    ES2872879T3|2021-11-03|Connecting sleeve for anchoring stems of two oppositely arranged prostheses
    JP5119165B2|2013-01-16|Face joint prosthesis
    DE10339600A1|2005-04-07|Device for securing acetabulum prosthesis to bone, comprising threaded segment for being joined to matching area at prosthesis
    同族专利:
    公开号 | 公开日
    PT3476320T|2021-11-16|
    US20190380751A1|2019-12-19|
    WO2018050944A1|2018-03-22|
    PL3476320T3|2022-01-03|
    US10568670B2|2020-02-25|
    ES2599389B2|2017-12-29|
    BR112018076496A2|2019-04-02|
    DK3476320T3|2021-10-18|
    EP3476320A1|2019-05-01|
    EP3476320A4|2020-03-04|
    EP3476320B1|2021-07-14|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US4492226A|1979-10-10|1985-01-08|Vsesojuzny Nauchno-Issledovatelsky I Ispytatelny Institut Meditsinskoi Tekhniki|Device for uniting bone fragments|
    US4453539A|1982-03-01|1984-06-12|The University Of Toledo|Expandable intramedullary nail for the fixation of bone fractures|
    WO2002058575A1|2001-01-27|2002-08-01|John Bruce Clayfield Davies|Improvements in or relating to expandable bone nails|
    US20070060891A1|2003-12-08|2007-03-15|Richard Skiera|Implant with a skin penetration section|
    US20120065638A1|2009-05-21|2012-03-15|Sonoma Orthopedic Products, Inc.|Snap and twist segmented intramedullary system, apparatus and associated methods|
    US4590930A|1983-06-22|1986-05-27|Lloyd A. Kurth|Fixation device and process for an intramedullary nail|
    WO2007008177A1|2005-07-12|2007-01-18|Nanyang Technological University|Intramedullary fixation device for fractures|
    US7785325B1|2006-02-03|2010-08-31|Milbank Miles C|Multi-articulated fracture fixation device with adjustable modulus of rigidity|
    法律状态:
    2017-03-15| PC2A| Transfer of patent|Owner name: UNIVERSITAT DE VALENCIA Effective date: 20170309 |
    2017-12-29| FG2A| Definitive protection|Ref document number: 2599389 Country of ref document: ES Kind code of ref document: B2 Effective date: 20171229 |
    优先权:
    申请号 | 申请日 | 专利标题
    ES201631220A|ES2599389B2|2016-09-19|2016-09-19|INTRAMEDULAR FIXING DEVICE|ES201631220A| ES2599389B2|2016-09-19|2016-09-19|INTRAMEDULAR FIXING DEVICE|
    PT178503439T| PT3476320T|2016-09-19|2017-09-18|Intramedullary fixation device|
    PL17850343T| PL3476320T3|2016-09-19|2017-09-18|Intramedullary fixation device|
    DK17850343.9T| DK3476320T3|2016-09-19|2017-09-18|INTRAMEDULAR FIXER|
    PCT/ES2017/070619| WO2018050944A1|2016-09-19|2017-09-18|Intramedullary fixation device|
    BR112018076496-5A| BR112018076496A2|2016-09-19|2017-09-18|intramedullary fixation device|
    US16/311,478| US10568670B2|2016-09-19|2017-09-18|Intramedullary fixation device|
    EP17850343.9A| EP3476320B1|2016-09-19|2017-09-18|Intramedullary fixation device|
    [返回顶部]