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Biomechanics Research

Hinged-Dynamic Posterior Device Permits Greater Loads on the Graft and Similar Stability as Compared with Its Equivalent Rigid Device: A Three-Dimensional Finite Element Assessment

Goel, Vijay K. PhD; Konz, Regina J. MS; Chang, H. T. MS; Grosland, Nicole M. PhD; Grobler, Leon J. MD; Chesmel, K. D.

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JPO Journal of Prosthetics and Orthotics: March 2001 - Volume 13 - Issue 1 - p 17-20
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Stabilization techniques have evolved to include a wide variety of internal fixation devices, including posterior pedicle screw rod/plate fixation devices to enhance biological fusion. These devices provide an effective way for correcting and stabilizing the spine, leading to an increased rate and degree of bony fusion. 1–8 The rigidity across a stabilized segment of the spine provided by a posterior fixation device and its ability to load share with the fusion mass are considered essential for fusion or bone healing to occur. 1,6,8–12 If the load transferred through the fusion can be increased without sacrificing its ability to impart stability to the decompressed segment, a more favorable environment for fusion may be created. In recent years, several such devices have appeared on the market. In vitro cadaveric studies including load-displacement experiments provide a means to delineate the stability afforded by the various stabilization systems (ie, dynamic vs. rigid system). 13 However, it is not practical to estimate the loads through the bone graft by using an experimental approach. Accordingly, this study uses a finite element analysis to compare the load sharing ability of a rigid versus a hinged pedicle screw-rod system. The Segmental Spine Correction System (SSCS) pedicle hinged screw-rod system (Osteotech, Inc., Eatontown, NJ 07724) was used for this study (Figure 1). The hinged screw allows ± 15° of movement about the axis A–A (Figure 2). As the hinge mechanism contacts the screw shaft, it is halted at its maximum range of motion, after which it acts in a manner similar to the rigid screw. This ±15° motion is what allows for the (theoretical) increase in load sharing capability of the device as compared with its equivalent SSCS rigid-screw system. Because the device designs were identical, except for the hinge aspect, direct comparisons could easily be made and inferences drawn about the biomechanical validity of any results determined in the study.

Figure 1
Figure 1:
The Segmental Spine Correction System (SSCS) pedicle-screw-rod device (Osteotech, Inc.) used to provide stability across two motion segments is shown.
Figure 2
Figure 2:
The hinged screw (HS) allows ± 15° of movement about the axis A–A. As the hinge mechanism contacts the screw shaft, it is halted at its maximum range of motion, after which it acts in a similar manner to the rigid screw. The rigid screw (RS) is also shown.


A three-dimensional nonlinear, experimentally validated finite element model of an intact L3–L4 motion segment was used for the analysis. 14,15 The capsular ligaments and part of the facets of the intact model were removed to simulate a facetectomy. From this model, two additional models were created to simulate stabilization across the L3–L4 segment for both the rigid-screw and hinged-screw devices. This was accomplished using 6-mm rigid and hinged pedicle screw-rod devices, including a cross bar at the L3–L4 disc interspace (Figure 3). The hinge part of the screw was modeled as a revolute joint between the screws and the hinges. The +15° and −15° constraints were defined by the contact elements between the nodes on the stoppers of the hinges and the surface of the screws in the model. In the model, the hinge axis was oriented perpendicular to the pedicular axis and was in the transverse plane. The initial hinge position was presumed to be 0°. The nucleus in these models was replaced with a graft (termed as nucleus) representing cancellous bone, cortical bone, or titanium (Table 1). The annulus was left intact in this simulation. Height of the graft equaled the disc/nucleus height. The interface between the graft/nucleus and the end-plate was simulated using gap elements so that the interface could transmit only compressive loads. This simulates the situation immediately after surgery and prior to the fusion of the graft.

Figure 3
Figure 3:
The model with the device in place. The axis system used for reporting the results is also shown. The nucleus of the intact model was replaced with cancellous bone, cortical bone, or titanium block (referred to as nucleus) to simulate varying degrees of stiffness of the graft material.
Table 1
Table 1:
The number and types of elements used to represent various spinal structures and the fixation device.

The models were fixed at the base, and axial compressive loads up to 800 N were applied to the superior end plate of the L3 vertebral body. It was evenly distributed across the end plate. The output was processed to determine axial displacement, flexion/extension rotation, and the loads transmitted through the graft material (nucleus) and the rods.


In the axial compression mode, the hinged device allowed for greater axial displacement, while it maintained angular stability similar to that of the rigid device (Table 2). The load transmitted through the nucleus increased with the use of hinged device as compared with the rigid device (Table 3). The amount of increase in the load through the nucleus was minimal for the titanium-graft case as compared with the cortical graft case (Table 4). Because load ratios were similar regardless of the load magnitude, only results for the 800 N are reported.

Table 2
Table 2:
The material properties assigned to various structures of the models.
Table 3
Table 3:
Axial displacement and angular rotation of L3 with respect to L4 for the 800N axial compression.
Table 4
Table 4:
Loads transferred through the “nucleus” and the device for the 800-N axial compression.


Two biomechanical issues are important in assessing the role of spinal devices in promoting successful fusion. First is the ability of a device to immobilize the injured segment for the fusion to occur, at least in the initial phase of the healing process. Second is the device’s ability to share the load with the fusion mass, thereby enhancing the fusion process. A reduction in the rigidity of the device can increase the amount of load shared by the fusion mass. However, such an approach will decrease the ability of the device to immobilize the decompressed segment in comparison with the rigid system. Patient-specific optimal rigidity of a device is not known. However, to be safe, the increase in load through the fusion mass should be achieved without an appreciable decrease in the ability of the device to provide stability. The hinge and rigid configurations afforded by the posterior system used in this study are both capable of achieving these objectives. The results of our in vitro investigation have shown that both designs provided similar stability across a severely destabilized spinal segment. 13 The present study was undertaken to test the hypothesis that the hinged screw design could also lead to increased load through the nucleus as compared with the rigid screw system.

The present finite element study has predicted the changes in load sharing due to alterations in the design of the device from a rigid to hinged system. Furthermore, the model predicted similar rotational stability for the two designs. Thus, the present study complements our in vitro investigation. 15 Under the conditions simulated in this model, the predicted results clearly show that the hinged system permits a greater load through the graft material used to replace the nucleus, as compared with the equivalent rigid screw design. Although the percent relative increase in load due to hinge screws is smaller, hinge screws permit greater axial displacements, as compared with rigid screws (Table 1). This increased axial displacement due to the hinge design of the screw has the potential to compensate for the settling of the bone graft during the initial phase of healing. Thus, the hinge design will ensure load transfer through the graft despite bone graft settling, as compared with the rigid design. The hinged screw-rod device, therefore, offers a design more likely to promote the fusion process by creating a more favorable environment. Additional studies are essential to address the issues of asymmetric placement of hinge screws and load sharing aspects in flexion, extension, lateral bending, and torsional modes to gain further insight into the mechanics of using hinge screws as opposed to conventional system.


This work was supported in part by Osteotech, Inc., Whitaker Foundation and the University of Iowa Spine Foundation Research Fund.

The work was undertaken at the University of Iowa.


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Posterior fixation device (hinged and rigid); biomechanics; load sharing; finite element modeling

© 2001 Lippincott Williams & Wilkins, Inc.