- Research article
- Open Access
Treatment of thoracolumbar burst fractures by short-segment pedicle screw fixation using a combination of two additional pedicle screws and vertebroplasty at the level of the fracture: a finite element analysis
BMC Musculoskeletal Disorders volume 18, Article number: 262 (2017)
Traditional one-above and one-below four-screw posterior short-segment instrumentation is used for unstable thoracolumbar burst fractures. However, this method has a high rate of implant failure and early loss of reduction. The purpose of this study was to use finite element (FE) analysis to determine the effect of treating thoracolumbar burst fractures by short-segment pedicle screw fixation using a combination of two additional pedicle screws and vertebroplasty at the level of the fracture.
An intact T11-L1 spine FE model was created from the computed tomography images of a male subject. Four fixation models with posterior fusion devices (pedicle screws, rods, cross-link) were established to simulate an unstable thoracolumbar fracture with different fusion surgeries: short-segment fixation with: 1) a link (S-L); 2) intermediate bilateral screws (S-I); 3) a link and calcium sulfate cement (S-L-C); 4) intermediate bilateral screws and calcium sulfate cement (S-I-C). Different loading conditions (flexion, extension, lateral bending, and axial rotation) were applied on the models and analyzed with a FE package. The range of motion (ROM), and the maximum value and distribution of the implant stress, and the stress in the facet joint, were compared between the intact and fixation models.
The ROM in flexion, extension, axial rotation, and lateral bending was the smallest in the S-I-C model, followed by the S-I, S-L-C, and S-L models. Maximum von Mises stress values were larger under lateral bending and axial rotation loadings than under flexion and extension loading. High stress was concentrated at the crosslink and rod junctions. Maximal von Mises stress on the superior vertebral body for all loading conditions was larger than that on the inferior vertebral body. The maximal von Mises stress of the pedicle screws during all states of motion were 265.3 MPa in S-L fixation, 192.9 MPa in S-I fixation, 258.4 MPa in S-L-C fixation, and 162.3 MPa in S-I-C fixation.
Short-segment fixation with two intermediate pedicle screws together with calcium sulfate cement at the fractured vertebrae may provide a stiffer construct and less von Mises stress of the pedicle screws and rods as compared to other types of short-segment fixation.
Burst fractures account for approximately 20% of thoracolumbar fractures, and occur due to an axial loading force that results in failure to support the anterior and middle column [1, 2]. Surgery is usually indicated when there is a severe deformity, and/or neurologic deficit. Whether anterior or posterior surgery is the most effective treatment for burst fractures remains controversial. Some authors advise anterior surgery to remove retropulsed fragments [3, 4], but posterior surgery is popular because it is an easier approach and allows clearance of the spinal canal by ligamentotaxis.
One-above and one-below posterior short-segment instrumentation with fusion has been widely used for unstable thoracolumbar burst fractures for the past 3 decades . Pedicular instrumentation enables kyphotic correction, indirect reduction of canal encroachment, and early mobilization. However, this method has a high rate of implant failure, and early loss of reduction because of loss of anterior support . Over the past decade, some studies have demonstrated that augmentation of the fractured vertebra with absorbable bone cement could enhance fracture union and prevent implant failure. Liao et al.  and Korovessis et al.  demonstrated that injectable calcium sulfate cement or injectable calcium phosphate cement used as a transpedicular grafting material in thoracolumbar fractures could obtain clinical and radiographic results equal to autogenous cancellous bone graft.
In recent years, biomechanical and clinical studies have suggested that two additional screws inside the fractured vertebra could improve stability and provide better kyphotic correction. In a biomechanical study, Norton et al.  showed that two additional screws in the fractured vertebra (a six-screw construct) of an unstable thoracolumbar burst fracture could increase the stiffness of the implant, and reduce stress on each pedicle screw, as compared to a four-screw construct. However, there have been no studies examining the effect of augmentation by a combination of screws and bone cement at the fractured vertebra, and comparing the effect of this fixation method with other types of posterior short-segment instrumentation for thoracolumbar burst fractures.
We hypothesize that posterior short-segment instrumentation with fractured vertebra augmentation by a combination of vertebroplasty and two additional screws can provide a stronger construct than other types of posterior short-segment instrumentation for thoracolumbar burst fractures. In the current study, we established a finite element (FE) model of thoracolumbar burst fractures, and four posterior short-segment fixation methods were tested. The purpose was to determine the most optimal methods for the treatment of thoracolumbar burst fractures.
Four fixation models with posterior fusion devices (pedicle screws, rods, cross-link) were established to simulate an unstable thoracolumbar fracture with different fusion surgeries: short-segment fixation with: 1) a link (S-L); 2) intermediate bilateral screws (S-I); 3) a link and calcium sulfate cement (S-L-C); 4) intermediate bilateral screws and calcium sulfate cement (S-I-C). Radiographs representing these four types of fixation are shown in Fig. 1.
Establishment of FE model of an intact normal thoracolumbar spine
A FE model of an intact normal spine was developed based on 1-mm-interval cross-sectional computed tomography (CT) spine images of a 55-year-old male provided by the US National Library of Medicine (NLM; NIH, Bethesda, MD). The FE model of the thoracolumbar section from T10 to L2 was established as follows. 1) A series of CT scans were imported into Amira 4.1 software (Visage Imaging, Carlsbad, CA). The vertebral boundaries as regions of interest (ROI) were identified on multiple images to form a three-node triangular surface model. 2) The surface model was imported into SolidWorks (SOLIDWORKS Corporation, Boston, MA), to further reconstruct a three-dimensional solid model of the thoracolumbar spine. 3) The solid model of the thoracolumbar spine was imported into HyperWorks 10.0 (Altair Engineering, Inc., Troy, MI) to form an eight-node hexahedral FE model. Since CT scanning does not provide the soft tissue contours of the intervertebral discs, the geometric characteristics of intervertebral discs were created as previously described . The volume ratio of the annulus fibrosus to the nucleus pulposus was set to 6:4, the thickness of the cortical bone was set to 1 mm, and the endplate was set to 0.5 mm . 4) The final FE model was imported into Abaqus FE analysis software (Abaqus/CAE v.6.10; Simulia Corp., Providence, RI) for analysis (Fig. 2).
Establishment of FE models of injured vertebra
In this study, the vertebral resection (corpectomy) method was used to simulate a vertebra fracture. Briefly, one-half of the sponge bone of the T12 vertebra was removed to weaken the vertebral strength; the structure of the posterior portion was reserved to establish a FE model of an unstable thoracolumbar fracture (Fig. 3).
Establishment of solid internal fixator models
Pedicle screw system
The pedicle screw system in this study was modeled based on the SmartLoc Spinal Fixation System (A-SPINE Asia Co., Ltd.). Using physical measurements and 3D reverse engineering, a solid model was created using Solidworks. The length of the screw was 45 mm, the radius was 2.4 mm, and the cross-sectional area was 18.1 mm2. The length of the vertical connecting rod was 80 mm, the radius was 2 mm, and the cross-sectional area was 12.6 mm2. The horizontal connecting rod was 35 mm long, 7 mm wide, and 5 mm high. In order to shorten the FE analysis time, the screw thread part and the vertical connecting rod middle connection part of the structure were neglected. After the solid models of the implants were created, they were imported into HyperWorks to generate the FE meshes. The four-vertebral pedicle screw plus transverse connecting rod FE mesh model is shown in Fig. 4a, and the six-vertebral pedicle screw model is shown in Fig. 4b.
Four fixation models
The internal fixators were placed in the thoracolumbar models as described by Park et al. . Four fixation models were used for comparison in this study: S-L, S-I, S-L-C, S-I-C. FE models of these four fixation types are shown in Fig. 5.
Material parameter settings
The material parameters (Young’s moduli and the Poisson’s ratios of cortical bone, cancellous bone, posterior bone element, endplate, and intervertebral disc) of the thoracolumbar models were set based on the work of Qiu et al. . The models were assumed to be homogeneous, isotropic, and linearly elastic. Material parameters are summarized in Table 1.
Loading and boundary conditions, and friction coefficient settings
The loading and boundary conditions of the FE analysis were based on the work of Qiu et al. . Flexion, extension, lateral bending, and axial rotation were applied to the rigid plane above the T11 vertebra, respectively, and the load was applied as a set in a progressive manner (2.5 Nm, 5.0 Nm, 7.5 Nm of bending moment), respectively, and all degrees of freedom on the bottom nodes of L1 were constrained. To simulate a real contact setting, the friction coefficient of the contact surface of the facet joint was set to 0.1. This study simulated bone fusion following surgery, therefore, the interfaces between the screw and vertebrae were set to be perfectly bonded.
By evaluating the range of motion (ROM) of T11-L1, the maximum von Mises stress on the pedicle screw root, and stress distribution of the pedicle screws and rods of the four fixation FE models under flexion, extension, left/right lateral bending, and left/right axial rotation, the biomechanical differences between the four fixation models could be compared.
Validation of the intact T11-L1 FE model
After establishment of the normal T11-L1 FE model, moments of 7.5 Nm in six directions were obtained. The ROM of the T11-T12 segment were: flexion (3.0°), extension (3.1°), left bending (3.3°), right bending (3.8°), left rotation (2.2°), and right rotation (2.0°). The ROM of the T12-L1 segment were: flexion (3.3°), extension (3.7°), left bending (4.0°), right bending (3.6°), left rotation (1.3°), and right rotation (1.4°) (Table 2). The ROM results were similar to those reported by Panjabi et al. .
ROM of the four FE fixation models
The moments of 7.5 Nm in six directions were applied to the four fixation models. The ROM of the T11-L1 segment were: S-L group: flexion (1.03°), extension (1.05°), left bending (2.92°), right bending (2.80°), left rotation (2.60°), right rotation (2.60°); S-I group: flexion (0.95°), extension (0.98°), left bending (2.67°), right bending (2.54°), left rotation (2.32°), right rotation (2.32°); S-L-C group: flexion (0.98°), extension (1.00°), left bending (2.75°), right bending (2.61°), left rotation (2.46°), right rotation (2.46°); S-I-C group: flexion (0.87°), extension (0.92°), left bending (2.57°), right bending (2.51°), left rotation (2.23°), right rotation (2.23°) (Table 3).
Comparisons between the four fixation models and the intact model
The percentage of ROM of the four fixation models with respect to the intact model was compared in terms of the degree of ROM in each direction of movement. The percentage of ROM of the S-I-C group was lowest in all directions of motion (flexion: 13.2%; extension: 13.5%; left bending: 35.0%; right bending: 33.9%; left rotation: 64.6%; right rotation: 65.6%), indicating the stability was the best. The percentage ROM of the S-L group was the highest in all directions of motion (flexion: 15.6%; extension: 15.4%; left bending: 39.7%; right bending: 37.8%; left rotation: 75.3%; right rotation: 76.5%), indicating the worst stability. The S-I group ranked second, and the S-L-C group ranked third with respect to stability (Fig. 6).
Stress distribution of the pedicle instrumentation system
von Mises stress distribution analysis showed that high stresses were mainly concentrated on the screws during flexion and extension. High stress in lateral bending was mainly concentrated on the longitudinal connecting rod. High stress was also concentrated at the junction of the transverse connecting rod and the longitudinal connecting rod under a rotation load (Fig. 7).
Maximum von Mises stress on the root of the pedicle screw
von Mises stresses of the pedicle screw neck of the S-L group were 30.9 MPa in flexion, 31.7 MPa in extension, 200.7 MPa in left lateral bending, 202.3 MPa in right lateral bending, 261.9 MPa in left rotation, and 265.3 MPa in right rotation. Stresses in the S-I group were 24.7 MPa in flexion, 25.7 MPa in extension, 141.8 MPa in left lateral bending, 144.3 MPa in right bending, 192.9 MPa in left rotation, and 191.2 MPa in right rotation. Stresses in the S-L-C group were 25.9 MPa in flexion, 26.1 MPa in extension, 156.5 MPa in left lateral bending, 258.4 MPa in right lateral bending, 200.4 MPa in left rotation, and 201.6 in right rotation. Stresses in the S-I-C group were 23.5 MPa in flexion, 24.6 MPa in extension, 128.6 MPa in left lateral bending, 130.2 MPa in right lateral bending, 162.3 MPa in left rotation, and 162.3 MPa in right rotation (Table 4).
Surgical management of a thoracolumbar burst fracture varies according to many factors. Fracture morphology, neurologic status, and surgeon preference all play major roles in deciding the surgical approach. An anterior approach to the fracture site can directly decompress the neural elements, and the reconstruction ca be performed by simultaneous iliac bone graft and plating. Hitchon et al.  and Sasso et al.  reported that the anterior approach was superior to the posterior approach in its ability to maintain the kyphotic correction at final follow-up, but both approaches achieved similar in clinical results. A major disadvantage of anterior surgery is potential donor site morbidity from harvesting iliac tri-cortical bone graft. In addition, the cost of the anterior approach is generally greater than that of the posterior approach. We usually use a posterior approach for the repair of thoracolumbar burst fractures, which is one of the reasons that led to the current study.
Traditional one-above and one-below short-segment posterior instrumentation has the potential for early implant failure and re-kyphosis due to lack of anterior support of the defect inside the injured vertebra. Several techniques, such as reinforcement with additional screws at the fractured level, or augmentation with any kind of bone cement to fill the defect of the fractured vertebra, have been proposed to improve the stability of the posterior instrumentation construct, and thus prevent implant failure and enhance fracture union [17,18,19,20]. However, no studies examined reinforcement of a fractured vertebra with a combination of bone cement with two additional fracture-level screws. Several biomechanical studies have suggested that reinforcement with fracture-level screws could improve the biomechanical stability of the construct [21,22,23]. Clinical studies have also suggested that reinforcement with additional screws at the fractured level can provide better kyphotic correction, more effectively restore fractured vertebra height, and allow earlier ambulation for patients with thoracolumbar burst fractures [24, 25]. On the contrary, authors have also claimed that a fractured vertebra augmented by absorbable bone cement followed by a posterior short-segment construct can provide satisfactory clinical results, with a low implant failure rate of 0% to 5% [19, 20]. Xu et al.  designed a FE model of a thoracolumbar burst fracture, and demonstrated that vertebroplasty inside the fractured vertebra can significantly reduce the stresses of the pedicle instrumentations and spine to prevent kyphotic correction loss and implant failure. In a clinical study, Liao et al.  showed that two screws placed inside the fractured vertebra with short-segment instrumentation was associated with shorter surgical time and less implant failure as compared to augmentation with injectable calcium sulphate/phosphate cement following posterior short-segment instrumentation.
In the current study, the four fixation models all demonstrated decreased ROM in all directions as compared with the intact spine model. ROM in flexion, extension, axial rotation, and lateral bending was the smallest in the S-I-C fixation model, followed by the S-I and S-L-C fixation models; the greatest ROM was seen in the S-L fixation model. The S-I-C and the S-I fixation model both contained six screws in the construct; the S-L-C and the S-L fixation only had four screws in the construct. Reinforcement with two additional screws at the fractured level can enhance biomechanical stability; and these results were similar to a previous FE study by Li et al. . Two additional screws inside the fractured vertebra was also stronger than when bone cement was used inside the fractured level (S-I fixation model versus S-L-C fixation model). This result was similar to the clinical results demonstrated by Liao et al. .
The pedicle screw is considered to be the weakest point of the posterior fixation, and implant failure is usually caused by screw loosening or screw root breakage . It has also been shown that the pedicle screws still continue to bear most of the load after fusion [30, 31]. To prevent early screw breakage, and to prolong the life of the screw, it is necessary to prevent the load on the screw from reaching the fatigue load. For this reason, we evaluated the maximum von Mises stress on the root of the pedicle screws in the four fixation models. A lower stress distribution around the root of the pedicle screw means the less chance of pedicle screw breakage. The maximum von Mises stress of the pedicle screws in the S-L group was higher than that in the other three fixation groups. In the S-I-C group, the maximum von Mises stress of the pedicle screw in all directions was the lowest. These results indicate that using two additional screws inside the fractured vertebra can reduce the stress on the pedicle screw root. Further augmentation with bone cement at the fractured level can further reduce the stress around the pedicle screw root, and further decrease the probability of screw failure. In addition, we found the pedicle screw root under lateral bending and axial rotation load sustained higher von Mises stresses, as finding similar to that of Xu et al. .
Injectable bone substitutes such as calcium sulfate, calcium phosphate cement, and hydroxyapatite cement are widely used for filling bone defects. These bone substitutes not only have osteoconductive ability to promote bone union, but also provide initial mechanical support. Evaniew et al.  used calcium sulfate/phosphate cement to manage patients with bone defects after curettage of primary tumor. Orsini et al.  demonstrated that calcium sulfate cement could promote new bone formation in a rabbit model of bone defects. Furthermore, Xu et al.  used a FE model to show that cement augmentation of a fractured vertebra could decrease the von Mises stress on the rods by 50% and on the screws by 40%. In the current study, however, the initial stability provided by bone cement inside the fractured vertebra did not achieve the stability provided by two additional screws. Nevertheless, an advantage of bone cements is that they can stimulate bone healing inside the vertebra, which screws cannot provide. Therefore, a combination of bone cement and two additional screws inside the fractured vertebra along with short-segment instrumentation may be an ideal surgical method for thoracolumbar burst fractures because provides greater initial stability, and also stimulates bone growth.
There are limitations of this study that should be considered. First, the FE spine models were reconstructed from data of a single patient, and thus is not representative of various ages or different sexes. Second, most cases of thoracolumbar burst fractures are associated with injury to the upper endplate and/or adjacent intervertebral disc. This was not addressed in the current models. Removal of the upper end-plate of the vertebrae in the FE model may better reflect the real injury pattern of a burst fracture. However, the main purpose of this study was to compare different fixation techniques, not different injuries. Third, because the current FE study only provided comparison data for the stability of different fixation methods, and the material representations of the biological structures were assumed to be linearly elastic, biomechanical studies of cadavers are necessary to validate the results for clinical practice. If the results are validated in cadaver studies, clinical cohort studies would be warranted.
Additional bilateral pedicle screws combined with cement augmentation vertebroplasty at the level of the fractured vertebra results in a stiffer construct and lower von Mises stress on the pedicle screws as compared with other types of posterior short-segment fixations. Four-screws plus a link resulted in the highest stress on the screws, suggesting this method would be associated with a higher incidence of implant failure and re-kyphosis. The S-I-C fixation was the strongest posterior short-segment fixation method for thoracolumbar burst fractures.
Range of motion
Benson DR, Burkus JK, Montesano PX, Sutherland TB, McLain RF. Unstable thoracolumbar and lumbar burst fractures treated with the AO fixateur interne. J Spinal Disord. 1992;5:335–43.
Crawford NR, Dickman CA. Construction of local vertebral coordinate systems using a digitizing probe. Tech Note Spine. 1997;22:559–63.
Limb D, Shaw DL, Dickson RA. Neurological injury in thoracolumbar burst fractures. J Bone Joint Surg Br. 1995;77:774–7.
Kaneda K, Taneichi H, Abumi K, Hashimoto T, Satoh S, Fujiya M. Anterior decompression and stabilization with the Kaneda device for thoracolumbar burst fractures associated with neurological deficits. J Bone Joint Surg Am. 1997;79:69–83.
Steffee AD, Biscup RS, Sitkowski DJ. Segmental spine plates with pedicle screw fixation. A new internal fixation device for disorders of the lumbar and thoracolumbar spine. Clin Orthop Relat Res. 1986;203:45–53.
Müller U, Berlemann U, Sledge J, Schwarzenbach O. Treatment of thoracolumbar burst fractures without neurologic deficit by indirect reduction and posterior instrumentation: bisegmental stabilization with monosegmental fusion. Eur Spine J. 1999;8:284–9.
Liao JC, Fan KF, Keorochana G, Chen WJ, Chen LH. Transpedicular grafting after short-segment pedicle instrumentation for thoracolumbar burst fracture: calcium sulfate cement versus autogenous iliac bone graft. Spine. 2010;35:1482–8.
Korovessis P, Hadjipavlou A, Repantis T. Minimal invasive short posterior instrumentation plus balloon kyphoplasty with calcium phosphate for burst and severe compression lumbar fractures. Spine. 2008;33:658–67.
Norton RP, Milne EL, Kaimrajh DN, Eismont FJ, Latta LL, Williams SK. Biomechanical analysis of four- versus six-screw constructs for short-segment pedicle screw and rod instrumentation of unstable thoracolumbar fractures. Spine J. 2014;14:1734–9. See comment in PubMed Commons below
Chosa E, Goto K, Totoribe K, Tajima N. Analysis of the effect of lumbar spine fusion on the superior adjacent intervertebral disk in the presence of disk degeneration, using the three-dimensional finite element method. J Spinal Disord Tech. 2004;17:134–9.
Park WM, Park YS, Kim K, Kim YH. Biomechanical comparison of instrumentation techniques in treatment of thoracolumbar burst fractures: a finite element analysis. J Orthop Sci. 2009;14:443–9.
Qiu TX, Tan KW, Lee VS, Teo EC. Investigation of thoracolumbar T12-L1 burst fracture mechanism using finite element method. Med Eng Phys. 2006;28:656–64.
Qiu TX, Teo EC, Zhang QH. Effect of bilateral facetectomy of thoracolumbar spine T11-L1 on spinal stability. Med Biol Eng Comput. 2006;44:363–70.
Panjabi MM, Oxland TR, Lin RM, McGowen TW. Thoracolumbar burst fracture. A biomechanical investigation of its multidirectional flexibility. Spine. 1994;19:578–85.
Hitchon PW, Torner J, Eichholz KM, Beeler SN. Comparison of anterolateral and posterior approaches in the management of thoracolumbar burst fractures. J Neurosurg Spine. 2006;5:117–25.
Sasso RC, Renkens K, Hanson D, Reilly T, McGuire RA Jr, Best NM. Unstable thoracolumbar burst fractures: anterior-only versus short-segment posterior fixation. J Spinal Disord Tech. 2006;19:242–8.
Guven O, Kocaoglu B, Bezer M, Aydin N, Nalbantoglu U. The use of screw at the fracture level in the treatment of thoracolumbar burst fractures. J Spinal Disord Tech. 2009;22:417–21.
Farrokhi MR, Razmkon A, Maghami Z, Nikoo Z. Inclusion of the fracture level in short segment fixation of thoracolumbar fractures. Eur Spine J. 2010;19:1651–6.
Marco RA, Meyer BC, Kushwaha VP. Thoracolumbar burst fractures treated with posterior decompression and pedicle screw instrumentation supplemented with balloon-assisted vertebroplasty and calcium phosphate reconstruction. Surgical technique. J Bone Joint Surg Am. 2010;92(Suppl 1 Pt 1):67–76.
Shen YX, Zhang P, Zhao JG, Xu W, Fan ZH, Lu ZF, et al. Pedicle screw instrumentation plus augmentation vertebroplasty using calcium sulfate for thoracolumbar burst fractures without neurologic deficits. Orthop Surg. 2011;3:1–6.
Anekstein Y, Brosh T, Mirovsky Y. Intermediate screws in short segment pedicular fixation for thoracic and lumbar fractures: a biomechanical study. J Spinal Disord Tech. 2007;20:72-77.
Baaj AA, Reyes PM, Yaqoobi AS, Uribe JS, Vale FL, Theodore N, et al. Biomechanical advantage of the index-level pedicle screw in unstable thoracolumbar junction fractures. J Neurosurg Spine. 2011;14:192–7.
Wang H, Li C, Liu T, Zhao WD, Zhou Y. Biomechanical efficacy of monoaxial or polyaxial pedicle screw and additional screw insertion at the level of fracture, in lumbar burst fracture: an experimental study. Indian J Orthop. 2012;46:395–401.
Mahar A, Kim C, Wedemeyer M, Mitsunaga L, Odell T, Johnson B, et al. Short-segment fixation of lumbar burst fractures using pedicle fixation at the level of the fracture. Spine. 2007;32:1503–7.
Tian JW, Wang L, Xia T, Liu CY, Zhao QH, Dong SH. Posterior short-segmental fixation combined with intermediate screws vs conventional intersegmental fixation for monosegmental thoracolumbar fractures. Orthopedics. 2011;34:e389–96.
Xu G, Fu X, Du C, Ma J, Li Z, Ma X. Biomechanical effects of vertebroplasty on thoracolumbar burst fracture with transpedicular fixation: a finite element model analysis. Orthop Traumatol Surg Res. 2014;100:379–83.
Liao JC, Fan KF. Posterior short-segment fixation in thoracolumbar unstable burst fractures - Transpedicular grafting or six-screw construct? Clin Neurol Neurosurg. 2016;153:56–63.
Li C, Zhou Y, Wang H, Liu J, Xiang L. Treatment of unstable thoracolumbar fractures through short segment pedicle screw fixation techniques using pedicle fixation at the level of the fracture: a finite element analysis. PLoS One. 2014;9:e99156.
Moran JM, Berg WS, Berry JL, Geiger JM, Steffee AD. Transpedicular screw fixation. J Orthop Res. 1989;7:107–14.
Chen CS, Cheng CK, Liu CL. A biomechanical comparison of posterolateral fusion and posterior fusion in the lumbar spine. J Spinal Disord Tech. 2002;15:53–63.
Suda K, Ito M, Abumi K, Haba H, Taneichi H, Kaneda K. Radiological risk factors of pseudoarthrosis and/or instrument breakage after PLF with the pedicle screw system in isthmic spondylolisthesis. J Spinal Disord Tech. 2006;19:541–6.
Xu G, Fu X, Du C, Ma J, Li Z, Tian P, et al. Biomechanical comparison of mono-segment transpedicular fixation with short-segment fixation for treatment of thoracolumbar fractures: a finite element analysis. Proc Inst Mech Eng H. 2014;228:1005–13.
Evaniew N, Tan V, Parasu N, Jurriaans E, Finlay K, Deheshi B, et al. Use of a calcium sulfate-calcium phosphate synthetic bone graft composite in the surgical management of primary bone tumors. Orthopedics. 2013;36:e216–22.
Orsini G, Ricci J, Scarano A, Pecora G, Petrone G, Iezzi G, et al. Bone-defect healing with calcium-sulfate particles and cement: an experimental study in rabbit. J Biomed Mater Res B Appl Biomater. 2004;68:199–208. See comment in PubMed Commons below
This study was funded by the Chang Gung Memorial Hospital Research Fund. The grant number is CRRPG3E0151.
Availability of data and materials
The raw data belongs to our institution archive. All the necessary information is contained in the manuscript. We will be glad to share our data upon a reasonable request.
JCL provided the concept of the study and wrote the manuscript. WPC designed the study and took responsibility for revising the manuscript. HW designed the study and performed the anaalyses. All authors read and approved the final manuscript.
The authors declare that they have no competing interests.
Consent for publication
Ethics approval and consent to participate
This study was performed after obtaining ethics approval from Institute Review Board (IRB) of Chang Gung Memorial Hospital (IRB number: 105-6778C1). However, participant’s consent was not needed because this study did not involve any living person or animal body. Also, the license agreement to use images of Visible Human Data set for scientific research was granted by the Project officer at National Library of Medicine, U.S.A. on Nov. 17, 2015.
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
About this article
Cite this article
Liao, J., Chen, W. & Wang, H. Treatment of thoracolumbar burst fractures by short-segment pedicle screw fixation using a combination of two additional pedicle screws and vertebroplasty at the level of the fracture: a finite element analysis. BMC Musculoskelet Disord 18, 262 (2017). https://doi.org/10.1186/s12891-017-1623-0
- Thoracolumbar burst fracture
- Posterior instrumentation
- Finite element analysis