DE102011082044A1 - Dynamic bone mounting device for joints, particularly vertebral column segments, has section to be mounted with bone, head area and fixing block which is suitable to receive bar - Google Patents

Abstract

The dynamic bone mounting device has section (20) to be mounted with the bone, a head area (30) and a fixing block (40) which is suitable to receive a bar (5). The head area is connected with the fixing block over an articulated joint kinematic mechanism (10). The components of the articulated joint kinematic mechanism have two non-coincident rotating axes. The articulated joint kinematic mechanism is provided for connecting head area and the fixing block that is formed as coupling linkage with four elements. An independent claim is included for a method for dynamic stabilization of vertebral column.

Description

Technical area

The invention relates to an anchoring device which can preferably be implanted for stabilization of the spine and has dynamic properties for maintaining a residual mobility. The dynamics are made possible by the special design of the anchoring element, wherein this is designed so that a physiological center of rotation is set in the thus treated joint.

State of the art

For the surgical treatment, in particular for the stabilization of spinal diseases using pedicle screw rod constructs, a variety of implants are known. Due to the problem of increased movement and concomitant accelerated degeneration of adjacent spinal segments as a result of a stiffening operation ( Park, 2010 ) implant systems have been developed that allow dynamic stabilization instead of rigid stiffening. In addition to dynamic rod systems where flexibility is created in the rod, some approaches are based on allowing flexibility in the pedicle screws. From the patent ( DE 4110002 C1 , 1991), a dynamic pedicle screw is known which has a rotational degree of freedom and thus allows rotation between the screw head and screw shaft. The idea of such a one-point camp was in ( WO 2008085369 A1 , 2006) and revisited in ( WO 0167973 A2 , 2000) has been extended to a biaxial version. These versions have in common that the movements of the components can take place unhindered and without stabilizing effect in the axes of movement. Possibilities for establishing a stabilizing effect are in ( EP 1388323 B1 , 2002; WO 2005000135 A1 , 2003). There elastic materials were used between the anchoring devices or the hinge points in order to limit the movement elastically and progressively. Recent proposals are for the approach to achieve movement in the pedicle screw head by using softer materials on and in the pedicle screw head ( US 2008021465 A1 , 2006; WO 2010027967 A1 , 2008; WO 2010045453 A1 , 2008). Since the space for the accommodation of elastic elements in or under the Pedikelschraubenkopf is very limited, and this space must transmit high forces and bending moments simultaneously, the possible flexibility is severely limited and the risk of mechanical overloading of such versions large.

All of the above-mentioned pedicle screw systems have a flexible portion which is to be made possible by one-point bearings (axles or balls), spring mechanisms or by the selection of elastic screw head materials. Together, they have the disadvantage that the center of rotation of the anchoring device is in each case within the screw geometry, whereas the physiological center of rotation of the treated joint is located elsewhere. In the case of a spinal column segment, the center of rotation is located, for example, in the region of the intervertebral disk and thus approximately 20-30 mm from the center of rotation of the anchoring element according to the current state of the art. The use of such dynamic pedicle screws thus does not lead to a correction of the often pathologically changed center of rotation, but exerts a negative influence on the segment to be treated. The deviation of the center of rotation from its physiological location leads to increased stress on other structures and joints (eg the facet joints) and adjacent vertebrae. Therefore, from a biomechanical point of view, it is necessary for a dynamically stabilizing implant to be able to reconstruct and maintain the center of rotation.

The application ( WO 2007115108 A1 , 2006), the stabilization with consideration of a defined center of rotation by the combination of two pedicle screws and an articulated rod trying to form the joint axes - in a certain position - a common point of intersection. However, this arrangement tends to self-locking with a change in the segment angle because the hinge axes do not intersect at a different position. If one were to replace one of the joints with a ball joint, the arrangement would become ineffective in terms of stabilization.

In ( WO 03094699 A2 , 2002) and ( WO 2006020530 A2 , 2004) posterior rod systems are presented which can also be used to generate a turning center outside the anchoring device. Here the combination of different lever arms, preferably arranged in a four-joint kinematics, is described. This requires a relatively large structure and often the space between the pedicle screws to be connected to each other is limited, so that these rod systems are difficult or impossible to use. Furthermore, the kinematic elements are designed so that only linear to progressively elastic stabilization properties result from the movement of the bar system. From biomechanical investigations it is known that instability is associated with the laxity of a movement segment of the spinal column and this is particularly detectable in the increase of the "neutral zone" ( Wilke, 2002 ). Therefore, an implant should be the have the greatest stabilizing effect, especially in the middle position (neutral position, neutral position) of a segment, in order to relieve the structures and muscles involved. This finding was made in ( WO 2004098452 A2 , 2003), the proposed technical implementation achieves the goal of a high stabilization effect in the middle position and a decreasing stabilization with increasing movement but not. The actual course of the stabilizing effect even increases progressively with the technical solution presented there and the increasing range of motion.

From the application ( US 20080243194 A1 , 2008) is a four-joint mechanism is known, which creates one or more pivot points as a connection between two bone screws. It is described that one or more degrees of freedom of the treated segment can be blocked. However, a significant disadvantage of this application is that the rotation center view and the interpretation of the invention is limited only to the sagittal plane, ie in the direction of flexion and extension. Side tilt and axial rotation movements are transferred to the joint mechanics. If the joint mechanism is not aligned parallel to the direction of movement, a high edge pressure in the joint axes would be very likely, which could lead to high abrasion or even blockage of the entire implant. Furthermore, a stabilization of the spinal column with the aid of a resilient element and the use of an angle-adjustable pedicle screw were dispensed with.

Summary: Rigid or dynamic implants according to the current state of the art exhibit, starting from the neutral position, a linear or progressive increase in the stabilizing effect. This means a restriction of movement of the joint and often overuse of the implant and the connection to the bone. A degressive course of the implant stiffness relative to the movement or deflection of the implant would correspond to the biomechanical requirements of the dynamic stabilization much more physiological. Solutions that allow a dynamic stabilization of a joint and simultaneously bring the center of rotation in accordance with the physiological center of rotation are not known or very space-consuming integrated into a connecting rod.

Brief description of the invention

Technical task

The object of the present invention is therefore to improve the stabilization effect of an implant system consisting of bone anchoring elements and at least one connecting element between the bone anchoring elements, which are used for the treatment of joint diseases, preferably of spinal diseases or injuries. The improvement is achieved either by restoring the physiological center of rotation of the joint with the aid of the implant according to the invention, stabilizing the joint with an implant which has a degressive stabilization characteristic, or with an implant which has both properties simultaneously.

Technical solution

The first aspect of the object is achieved in that the bone anchoring element is provided with an articulated connection, which makes it possible to correct the path of movement of a diseased joint or to direct it into its physiological path. The proposed kinematics includes a joint construction or gear arrangement with which can be defined degrees of freedom. Thus, in a preferred embodiment, for example, a four-joint kinematics can be used. With appropriate design, this describes the movement path around the physiological center of rotation while stabilizing in other levels of motion. Furthermore, the invention proposes a solution for stabilizing the "neutral zone" of a joint. This is achieved by arranging the joint mechanism so that a non-linear relationship arises between the relative movement of the bone joint and the movement of the implant. For example, the implant joint mechanism may include a spring with a linear characteristic in a non-linear toggle mechanism, and the implant according to the invention thus exerts a degressive stabilizing effect on the joint to be treated. Furthermore, the use of ball joints in joint mechanics is proposed to specifically allow spinal movements in lateral tilt and axial rotation.

Advantageous effects

An advantage of the present invention is that it can be used with a simple connecting rod between the vertebrae and thus no additional dynamic rod systems are required. Simultaneously improving biomechanical properties and simplifying implantation reduces the overall cost of patient care. The implant according to the invention provides precisely one defined path of movement about a center of rotation whose position is close to the physiological center of rotation. This is a prerequisite for preventing further progressive degeneration of already degenerative altered spinal segments. Other movements (translation or axial loads) are prevented so that, for example, the facet joints can be relieved and the position of the vertebrae can be corrected. Another advantage is that the differences in stiffness between treated and untreated segments in the main movement direction flexion-extension are low. Thus, the invention can help to reduce terminal segment degeneration. Due to the degressive stabilization effect, the loading of the implant in the extreme positions is lower than in the current state of the art, which helps to avoid undesired implant loosening or fractures. The implant system is preferably of a modular design, so that the surgeon has the option after the placement of the screw shaft to decide to assemble a kinematic attachment or to proceed with a rigid variant (for example, to achieve a fusion). An additional advantage of the invention is to stabilize the so-called "neutral zone" of a joint without significantly limiting the total possible range of motion.

Short description of the drawing figures

1 shows a spine segment with inventive anchoring device.

2 shows examples of the different joint kinematics that can be used in inventive design.

3 explains the operation of a nonlinear motion kinematics on the embodiment of a toggle mechanism and the possible generation of degressive stabilization effect.

4 shows the extreme positions of the anchoring device according to the invention and the position of the resulting center center of rotation.

5 describes the relevant components of the joint kinematics and exemplifies an angle-adjustable and lockable connection mechanism.

6 shows a further application of the invention essential kinematics between two bars.

7 shows the use of ball joints to reduce edge pressure between the hinge axes and the shaft guides. This embodiment allows spinal movements in all three main anatomical movement directions.

8th illustrates an alternative embodiment of the invention in which a joint mechanism is combined with a gear so as to generate a physiological movement path.

9 illustrates the various possible arrangements of the anchoring device according to the invention for different treatment scenarios.

10 shows the toggle mechanism and the combination of the toggle mechanism with a four-bar mechanism between two articulated rods.

Description of the embodiments

The technical solutions are often described below by way of example. This should be understood as a means of explaining the underlying idea and should not be construed as limited to the particular concrete representation.

The implant system according to the invention consists of at least one connecting element ( 5 ), which may be formed as a rod or plate, as well as at least one bone anchoring element according to the invention ( 1 ), wherein in an essential embodiment either in the bone anchoring element ( 1 ) or in the connecting element ( 5 ) a joint kinematics ( 8th . 10 ) or a transmission ( 10 ) is located.

A motion segment is the smallest biomechanical unit of the spine and is defined as consisting of two adjacent vertebrae ( 2 and 4 ) and an intermediate intervertebral disc ( 3 ) consists. The bone anchoring element ( 1 ) consists of a screw shaft ( 20 ) with screw head ( 30 ), a joint kinematics attached thereto ( 10 ) and at least one fixation block ( 40 ) ( 1 ). At the bone anchoring element ( 1 ), also called pedicle screw in the further description, a fixing rod ( 5 ), which also with conventional pedicle screws ( 7 ) can be combined. The pedicle screw ( 1 ) is characterized in that the integrated joint kinematics ( 10 ) gives a defined mobility and the screw shaft ( 20 ) together with the screw head ( 30 ) around a defined center of rotation ( 6 ) ( 2 ).

The joint kinematics ( 10 ) is constructed so that it consists of at least two joint axes ( 102 ) and at least one connecting element ( 101 ) and the screw head ( 30 ) with the fixation block ( 40 ) connects flexibly ( 2 ). The joint axes or their bearings ( 102 ) or the connecting elements ( 101 ) can be flexible or made of flexible material, to allow a certain flexibility in the planes outside of the main plane of motion defined by the kinematics. In addition, the depositories ( 102 ) may be formed as a ball joint bearing. The joint kinematics according to the invention may consist of various arrangements: a two-joint ( 11 and 111 ), Three-jointed ( 12 ), Four-jointed ( 13 and 131 ), Five ( 14 ) - or six-joint arrangement ( 15 ). The connecting elements ( 101 ) can also be stored in themselves, as shown by way of example for two- and four-joint kinematics ( 111 and 131 ) ( 2 ). The following is the 4-joint kinematics ( 13 ), for example, to define a specific center of rotation ( 6 ) is - depending on the position of the center of rotation - one of the other joint arrangements more advantageous.

The rotational center which can be influenced by the bone anchoring element according to the invention is selected by appropriate choice of the joint kinematics ( 10 ) and their dimensions adjusted to correspond to the physiological center of rotation of the joint to be treated. For a specific influencing of the center of rotation, it is advantageous first to determine the actual center of rotation of the diseased joint (eg radiographically via functional recordings), then to compare the position of the measured rotational center with the physiological position, and on the basis of the difference and the anatomical dimensions to select appropriate joint kinematics, or if this is adjustable, to adjust according to the desired influence.

To achieve an increased stabilizing effect, an elastic element ( 160 ) in the joint kinematics ( 16 ) to be built in ( 3 ). The elastic element may consist of a spiral, plate, leaf, or leg spring and is between at least two (not necessarily adjacent) fasteners ( 101 ), Joint axes ( 102 ), or at least one point of a body ( 30 . 40 ) assembled. It has the task of moving the joint kinematics ( 10 ), in which case - in conjunction with the joint kinematics - preferably a non-linear relationship should be achieved. The elastic element ( 160 ) can, for example, at a connecting element ( 161 . 162 ) are mounted, or the connecting elements ( 161 . 162 ) are chosen in their dimensions so that in the middle position ( 82 ) requires the greatest increase in power in order to generate a movement deflection ( 1600 ). For this example, the three-joint kinematics ( 12 ) are designed as a toggle mechanism, which converts linear motion sequences into non-linear ones. This allows, for example, using a linear spring ( 160 ) with the characteristic 1601 , together with a toggle mechanism, the generation of the desired degressive stabilization effect ( 1600 ), which is required for the stabilization of the "neutral zone". The degressivity can also be improved by the use of a spring ( 160 ) are generated or amplified with non-linear characteristic. For the design of the kinematics for degressive stabilization effect, for example, a short connecting element ( 161 ) with a longer connecting element ( 162 ) together in a hinge point ( 164 ) connected. The so-called toggle kinematics can be constructed in that at least one short articulated rod ( 161 ) with a longer articulated rod ( 162 ) is connected at an angle of about 90 °. This angle is achieved in the middle or neutral position ( 82 ). In 3 is a torsion spring ( 160 ) at the joint joint ( 164 ), which on a fastening device ( 163 ) at the fixation block ( 40 ) is mounted. The joint arrangement ( 16 ) has the advantage that during a movement ( 81 - Flexion and 83 - Extension) an increased resistance in the middle position ( 82 ) prevails and this must be overcome first. With increase of movement ( 81 or 83 ), in the arrangement shown, the force increase required for this purpose is lower ( 1600 ) ( 3 ). It is thus achieved that an implant according to the invention in the starting position, ie in the mentioned "neutral zone", gives the treated joint a high stability, without the stabilization effect greatly increasing with a further movement excursion.

Mechanical stops can be placed so as to prevent the movement from being exceeded. In the (in 16 ), the mechanical stop is generated by the toggle mechanism itself, by the maximum extension of both fasteners ( 161 and 162 ) the way in both directions ( 81 and 83 ) limited. In order to obtain a non-linear force-displacement path as possible and at the same time to memorize the kinematics of a defined center of rotation, it may be useful to fix the sides of the fixation block ( 40 ), each with different joint arrangements ( 101 . 161 . 162 ) to provide. For example, a page with the layout ( 13 ), the other side with a toggle mechanism as in ( 16 ).

The dynamic pedicle screw ( 1 ) has a screw shaft ( 20 ) with a bone thread ( 21 ) ( 5 ). A passage opening ( 23 ) can optionally be inserted in the screw shaft ( 20 ) to permit implantation over a guidewire or to permit the injection of bone cement. The proximal end of the screw shaft ( 20 ) has a head ( 22 ), which is located within the receptacle of the screw head ( 30 ) is located. In principle, the screw shaft head can be designed in three different versions, so that the head setting differ in the rotational degrees of freedom. Here there is monoaxial ( 220 ), biaxial ( 221 ) and polyaxial ( 222 ) Arrangements of the head ( 22 ). On the screw shaft head ( 22 ) can be an assembly aid ( 223 ) or be introduced to achieve the fit with an assembly tool. The screw head ( 30 ) is the connecting element between screw shank ( 20 ) and the kinematic unit ( 10 ). Inside, the screw head ( 30 ) have a cavity in which the screw shaft head ( 22 ) is stored (for 221 . 222 ) or forms a unit (for 220 ). At the proximal end of the screw head ( 30 ) is an opening through which the screw shaft head ( 22 ) to be led. An exemplary locking mechanism is by means of a screw ( 31 ) ( 5 ). After tightening the screw ( 31 ) is the screw head ( 30 ) angle stable with the screw shank ( 20 ) connected. The combination with other locking mechanisms z. B. by means of a mold insert between ( 22 and 31 ) or by a slotted version of the head ( 30 ) with a circumferential clamping is equivalent executable.

In another embodiment, a mounting rod ( 5 ) into a hollow ( 33 ) of the screw head ( 30 ) and fixed above ( 31 ) ( 6 ). This has the purpose that several of these screws according to the invention can be connected in series.

Furthermore, at the screw head ( 30 ) Storage locations ( 321 . 322 ). The positions of the storage points ( 321 and 322 ) influence the course of movement of the joint kinematics ( 10 ). A targeted change of the distance or the spatial arrangement to each other changes both the possible range of motion and the center of rotation of the kinematics. Thus, for example, different turning centers can be defined by a different arrangement of the bearings, or they can be adjusted by one or more adjustment suitable. Alternatively, the center of rotation and the range of motion can be adjusted by length adjustment or by changing the joints ( 101 . 161 . 162 ) are adapted to the respective anatomical requirements.

In the fixation block ( 40 ) the fixing rod ( 5 ) either directly inserted and fixed, or by means of a fixation block ( 40 ), angle-adjustable and lockable bearing unit ( 41 ) associated with it. The fixation block ( 40 ) or the storage unit ( 41 ) is characterized in that it has a recess ( 42 ) for receiving the rod own. The rod receiving recess ( 42 ) may have an opening through which an assembly tool can be inserted, with which the screw shaft ( 20 ) can be screwed into the bone. At the fixation block ( 40 ) or the storage unit ( 41 ) is also a locking mechanism ( 43 ) with which the mounting rod ( 5 ) with the rod receiving recess ( 42 ) is firmly connected. The storage unit ( 41 ) has a similar function as the screw head bearing unit ( 32 ) and allows the compensation of differences in alignment between the bars ( 5 ). The positions of the storage points ( 411 and 412 ) influence the course of movement of the joint kinematics ( 10 ). A change in the distance between 411 and 412 can be used to change the range of motion and the center of rotation. Between the screw head ( 30 ) and the fixation block ( 40 ) are the connecting elements ( 101 ) of joint kinematics ( 10 ). The arrangement and number of connecting elements is determined by the kinematic configuration ( 10 ) dependent.

The mounting rod ( 5 ) may have different geometric cross sections (eg in the form of straight or curved bars or plates), or a different axial and bending stiffness, so that an additional dynamics of the mounting rod can be achieved.

7 represents an alternative embodiment of the invention. The pedicle screw consists, similar to the previous constructions, of a screw shaft ( 20 ), a lockable ( 31 ) Screw head ( 30 ) and a rod holder ( 40 ), which by means of a fixing device ( 43 ) on a rod ( 5 ) is attached. The joint mechanism consists of at least one connecting element ( 101 ) and one or more joint axes ( 102 ). In this embodiment, the connecting elements ( 101 ) via ball joints ( 103 ) with the joint axes ( 102 ) connected. This has the goal that the joint mechanism allows more degrees of freedom. Thus, in addition to the flexion and extension movements, movements such as axial rotation and lateral tilt are now possible alone and in combination.

In a further embodiment variant of the invention, the joint mechanism ( 10 ) with a transmission ( 34 . 44 ) to create a physiological movement path ( 8th ). This is achieved with the pedicle screw according to the invention, which has a screw shaft ( 20 ), a screw head ( 30 ) and a rod holder ( 40 ) owns. The screw head ( 30 ) is with the rod holder ( 40 ) via a joint mechanism ( 10 ) movably connected. In the simplest case, this joint mechanism consists of a connecting element ( 101 ), which at joint axes ( 101 ) is attached or stored. So that the movement sequence of rotation and translation of the screw head ( 30 ) in relation to the rod holder ( 40 ), the screw head ( 30 ) via a toothing ( 34 . 44 ) with the rod holder ( 40 ) connected. The gearing ( 34 . 44 ) may be configured as part of a gear cutout.

In 9 Different treatment scenarios with dynamic and rigid pedicle screws are shown ( 70 ). If a single segment is supplied, the supply with the dynamic pedicle screw according to the invention ( 1 ) with a conventional pedicle screw ( 7 ), for example in a cranial ( 71 ) or caudal arrangement ( 72 ). In the case of a bisegmental care ( 73 ) can each be a dynamic screw ( 1 ) superior and inferior to a centrally located conventional pedicle screw ( 7 ) be used. In the case of a multisegmental supply with a desired fusion section, the middle part of the long-range supply can be left rigid and the superiore and / or the inferior end can be left with the pedicle screw according to the invention ( 1 ) in order to reduce the risk of terminal segment degeneration ( 74 ). For purely dynamic care there is the possibility of dynamic pedicle screws ( 1 ) according to 6 to use ( 75 ).

The mechanism ( 16 ) can be used to initiate a degressive stabilization effect in a further embodiment between two fixing blocks ( 40 ) ( 10 ), which are then located between the pedicle screws. An advantage of this arrangement is that conventional pedicle screws and simple mounting rods can be used.

List of specified documents

• DE 4110002 C1 and Ulrich, H. (1991). Implant for the correction and stabilization of the spine, Heinrich Ulrich.
• EP 1388323 B1 BIEDERMANN, L. and JESZENSKY, D. (2002). DYNAMIC STABILIZING ARRANGEMENT FOR BONES, IN PARTICULAR FOR THE SPINAL COLUMN, BIEDERMANN MOTECH GMBH.
• Park, DK, Lin, EL and Phillips, FM (2010). "Index and Adjacent Level Kinematics After Cervical Disc Replacement and Anterior Fusion: In Vivo Quantitative Radiographic Analysis." Spine (Phila Pa 1976) ,
• US 2008021465 A1 , SHADDUCK, JH, TRUCKAI, C. and LUZZI, R. (2006). SPINE TREATMENT DEVICES AND METHODS SHADDUCK JOHN H.
• US 20080243194 A1 , LOTZ, J. and BRADFORD, D. (2008). Articulating Instrumentation for Dynamic Spinal Stabilization, University of California.
• Wilke, HJ, Kavanagh, S., Neller, S. and Claes, L. (2002). "[Effect of artificial disk nucleus implant on mobility and intervertebral disk high at L4 / 5 segment after nucleotomy]." Orthopedic 31 (5): 434-440 ,
• WO 0167973 A2 , CRANDALL, D., MORRISON, MM and STROHKIRCH, T. (2000). MULTIDIRECTIONAL PIVOTING BONE SCREW AND FIXATION SYSTEM, SDGI Holdings Inc.
• WO 03094699 A2 and RITLAND, S. (2002). DYNAMIC FIXATION DEVICE AND METHOD OF USE, RITLAND STEPHEN.
• WO 2004098452 A2 and PANJABI, MM (2003). DYNAMIC SPINE STABILIZER, UNIV YALE.
• WO 2005000135 A1 , CLEMENT, J.-L., FIERE, V., TAYLOR, J., ADAM, Y. and VILLARET, B. (2003). VERTEBRAL OSTEOSYNTHESIS EQUIPMENT, Medicrea Technologies.
• WO 2006020530 A2 , COLLERAN, D., ROGERS, C., SPITLER, J. and SCHORER, S. (2004). System and method for dynamic skeletal stabilization, INNOVATIVE SPINAL TECHNOLOGIES.
• WO 2007115108 A1 , COLLERAN, D., OYOLA, A., PERRIELLO, M. and CARTER, S. (2006). DYNAMIC MOTION SPINAL STABILIZATION SYSTEM, Innovative Spinal Technologies.
• WO 2008085369 A1 , UPAL, AM, LOPEZ, EA, HAWKINS, JR, BORGSTROM, A., ARNOLD, B., KWAK, SD, BARTISH, CM and DUNBAR, WL (2006). SPINE STABILIZATION SYSTEM WITH DYNAMIC SCREW, DEPUY SPINE INC.
• WO 2010027967 A1 , HEIGES, BA and LANE, DE (2008). MODULAR PEDICLE SCREW SYSTEM, BHDL HOLDINGS LLC.
• WO 2010045453 A1 DEWEY, JM, JUSTIS, JR and PROTOPSALTIS, DK (2008). DYNAMIC ANCHOR ASSEMBLY FOR CONNECTING ELEMENTS IN SPINAL SURGICAL PROCEDURES, WARSAW ORTHOPEDIC INC.

QUOTES INCLUDE IN THE DESCRIPTION

This list of the documents listed by the applicant has been generated automatically and is included solely for the better information of the reader. The list is not part of the German patent or utility model application. The DPMA assumes no liability for any errors or omissions.

Cited patent literature

• DE 4110002 C1 [0002, 0036]
• WO 2008085369 A1 [0002, 0036]
• WO 0167973 A2 [0002, 0036]
• EP 1388323 B1 [0002, 0036]
• WO 2005000135 A1 [0002, 0036]
• US 2008021465 A1 [0002, 0036]
• WO 2010027967 A1 [0002, 0036]
• WO 2010045453 A1 [0002, 0036]
• WO 2007115108 A1 [0004, 0036]
• WO 03094699 A2 [0005, 0036]
• WO 2006020530 A2 [0005, 0036]
• WO 2004098452 A2 [0005, 0036]
• US 20080243194 A1 [0006, 0036]

Cited non-patent literature

• Park, 2010 [0002]
• Wilke, 2002 [0005]
• Park, DK, Lin, EL and Phillips, FM (2010). "Index and Adjacent Level Kinematics After Cervical Disc Replacement and Anterior Fusion: In Vivo Quantitative Radiographic Analysis." Spine (Phila Pa 1976) [0036]
• Wilke, HJ, Kavanagh, S., Neller, S. and Claes, L. (2002). "[Effect of artificial disk nucleus implant on mobility and intervertebral disk high at L4 / 5 segment after nucleotomy]." Orthopedic 31 (5): 434-440 [0036]

Claims (14)

A dynamic bone anchoring device for joints, and in particular spinal column segments, consisting of at least one section to be anchored to the bone ( 20 ), a header ( 30 ) and a fixation block ( 40 ), which is suitable for a rod ( 5 ), characterized in that the head area ( 30 ) via a joint kinematics ( 10 ) with the fixation block ( 40 ) connected is. The invention according to claim 1, characterized in that the components of the joint kinematics ( 10 ) have at least two non-congruent axes of rotation. The invention according to one of the preceding claims, characterized in that the articulated kinematics for connecting head area ( 30 ) and fixation block ( 40 ) is constructed as a coupling gear with at least four members. The invention according to one of the preceding claims, characterized in that the arrangement of the individual hinge points ( 102 ) and the lengths of the connecting elements ( 101 ) are coordinated so that the one or more of the resulting fulcrums ( 6 ) of kinematics ( 10 ) Coincide with the physiological fulcrum of the joint to be treated. The invention according to one of the preceding claims, characterized in that the fulcrum ( 6 ) of kinematics ( 10 ) by adjusting the length of the connecting elements ( 101 ) or changing the position of the pivot points ( 102 ) is adjustable. The invention according to one of the preceding claims, characterized in that the fixing block ( 40 ) an angularly adjustable and lockable bearing unit ( 41 ) for receiving the rod ( 5 ) includes. The invention according to one of the preceding claims, characterized in that the joint kinematics ( 10 ) on both sides of the fixation block ( 40 ) between one and six connecting elements. The invention according to one of the preceding claims, characterized in that the non-linear joint kinematics ( 16 ) an elastic element ( 160 ), so that a non-linear, preferably degressive stiffness characteristic of the stabilization effect of the bone anchoring element ( 1 ) is achieved. The invention according to one of the preceding claims, characterized in that the dimensions of the connecting elements ( 101 . 161 . 162 ) and the arrangement of the hinge points ( 102 ) of kinematics ( 10 . 16 ) allow only a defined range of motion. The invention according to one of the preceding claims, characterized in that articulation points ( 102 ) and connecting elements ( 101 ) by a ball joint ( 103 ) are interconnected. The invention according to one of the preceding claims, characterized in that articulation points ( 102 ) with the screw head ( 30 ) are interconnected by one or more ball joints. The invention according to one of the preceding claims, characterized in that the screw head ( 30 ) and the fixation block ( 40 ) are interconnected via at least one intermeshing toothing point and with the joint mechanism ( 10 ) is combined. A method for the dynamic stabilization of the spine, consisting of the steps: Determination of the position of the center of rotation ( 6 ) at least the segment to be treated; Determining the correction requirement of the position of the center of rotation by comparing the actual center of rotation determined in the previous step with the position of the desired center of rotation after the operation has taken place; Based on the previously determined need for correction Selection of at least one bone anchoring element ( 1 ), which is suitable for the location of the center of rotation ( 6 ) of the segment to be treated; Implantation of the previously selected bone anchoring element ( 1 ). A method for the dynamic stabilization of the spine, consisting of the steps: Determination of the position of the center of rotation ( 6 ) at least the segment to be treated; Determining the correction requirement of the position of the center of rotation by comparing the actual center of rotation determined in the previous step with the position of the desired center of rotation after the operation has taken place; On the basis of the previously determined need for correction Selection of bone anchoring elements ( 7 ) and at least one bar connection kinematics ( 8th ), which is suitable for the location of the center of rotation ( 6 ) of the segment to be treated; Implantation of previously selected bone anchoring elements ( 7 ) and the bar connection kinematics ( 8th ).

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