Biomechanical comparison of translaminar screw versus pedicle screw supplementation of anterior femoral ring allografts in one-level lumbar spine fusion.
Simultaneous combined anterior and posterior lumbar fusion has become an accepted operative procedure for the treatment of patients with disabling low back pain. Hodgson and Wong were among the first to perform a combined anterior and posterior fusion, and demonstrated that this combined approach achieves more stability than either procedure alone. (1,2)
Currently, combined anterior and posterior lumbar fusion often involves anterior interbody fusion (using either autograft autograft: see transplantation, medical. or allograft allograft: see transplantation, medical. ) and posterior fixation. Instrumentation systems for posterior fixation include pedicle pedicle /ped·i·cle/ (ped´i-k'l) a footlike, stemlike, or narrow basal part or structure.
1. A constricted portion or stalk.
2. screw and translaminar screw constructs. Pedicle screw fixation systems are most useful when correcting degenerative conditions for which the spinous spinous /spi·nous/ (spi´nus) pertaining to or like a spine.
Relating to, shaped like, or having a spine or spines.
pertaining to or like a spine. processes and laminae have been removed for neural decompression. The use of pedicle screw fixation has become popular because it allows for stable attachment to a vertebra vertebra /ver·te·bra/ (ver´te-brah) pl. ver´tebrae [L.] any of the 33 bones of the vertebral (spinal) column, comprising 7 cervical, 12 thoracic, 5 lumbar, 5 sacral, and 4 coccygeal vertebrae . despite resection of the posterior elements. In addition, pedicle screws allow for segmental control of the vertebrae Vertebrae
Bones in the cervical, thoracic, and lumbar regions of the body that make up the vertebral column. Vertebrae have a central foramen (hole), and their superposition makes up the vertebral canal that encloses the spinal cord. , providing an opportunity for distraction or compression along the length of the spinal fusion.
Zdeblick and colleagues (3) showed that the use of pedicle screw instrumentation results in higher fusion rates than bone grafting alone. However, the complication rate is also higher and includes device-related osteoporosis, pain, infection, and nerve root injury. Pedicle screw insertion requires significant muscle dissection and retraction resulting in greater morbidity. Furthermore, the cephalad cephalad /ceph·a·lad/ (sef´ah-lad) toward the head.
Toward the head or anterior section. screws of a pedicle screw plate or rod construct may cause mechanical compromise of the facet joint above the fused level.
Translaminar screw (TLS (1) (Transport Layer Security) A security protocol from the IETF that is based on the Secure Sockets Layer (SSL) 3.0 protocol developed by Netscape. TLS uses digital certificates to authenticate the user as well as authenticate the network (in a wireless ) fixation represents an alternative to pedicle screw constructs. Translaminar screws allow for good stabilization of the segment with minimal soft tissue injury Soft tissue injury is damage of the soft tissue of the body. These types of injuries are a major source of pain and disability. The four fundamental tissues that are affected are the epithelial, muscular, nervous and connective tissues. . (4-11) It is well known that excessive movement at the bone-implant interface will lead to fibrous tissue formation; minimizing movement at the interface theoretically increases the fusion rate. A number of studies have evaluated the biomechanical characteristics of translaminar facet screw fixation in the absence of anterior interbody fusion. (12-15) Subsequently, Volkman and associates (16) demonstrated that the supplementation of anterior lumbar interbody arthrodesis arthrodesis /ar·thro·de·sis/ (-de´sis) the surgical fixation of a joint by a procedure designed to accomplish fusion of the joint surfaces by promoting the proliferation of bone cells; called also artificial ankylosis. with transfacet screw fixation results in an increase in stiffness of the motion segment. However, few studies have directly compared the biomechanical properties of pedicle screws with those of translaminar screws as a means of supplementing anterior interbody fusion.
Therefore, this biomechanical study was designed to compare the stability of one-level anterior interbody lumbar constructs stabilized with either translaminar screw fixation or pedicle screw fixation. Our hypothesis was that there is no difference in initial stability between the two forms of posterior fixation when used as a supplement to an anterior femoral ring allograft construct.
Materials and Methods
Five motion segments (L4-S2) from fresh human cadavers were obtained. Each specimen was radiographed to ensure that no major structural abnormalities were present. Bone density was not performed on these specimens. All specimens were frozen to -20[degrees] C and stored until the day before testing, when they were allowed to thaw slowly to room temperature. Each lumbar motion segment was carefully stripped of muscle, with care taken to preserve all ligaments, joint capsules, discs, and the bone structure. The proximal (L4) and distal (S2) ends of each specimen were then fixed to the centers of aluminum plates (15 x 15 x 0.5 cm), using surgical bone cement (Stryker, Rutherford, NY). Care was taken to ensure that the disc and the facet joints were clear of the cement and easily accessible.
Nondestructive biomechanical testing was performed. During each test, load was applied to the superior plate at a defined center with a ball bearing (Fig. 1). The inferior end plate was clamped to the activator of a mechanical testing machine (MTS (1) See Microsoft Transaction Server.
(2) (Modular TV System) The stereo channel added to the NTSC standard, which includes the SAP audio channel for special use.
1. MTS - Message Transport System.
2. , Canton, MA). After a cyclic compression-conditioning period (500 N [+ or -] 150 N, at 1 Hz, for 1000 cycles), the motion segment was biomechanically tested according to the following loading sequence. At each step, the load was applied three times and a load-deformation curve was obtained each time.
The center of rotation center of rotation,
n a point or line around which all other points in a body move. was established for the intact motion segment in the manner described by Volkman and colleagues. (16) Each specimen was then loaded in pure compression at a displacement rate of 0.25 cm/min. A load of up to 900 N was applied at the center of rotation. Previous studies showed that this maximum load allowed repeated cycles without causing irreversible damage to the intervertebral intervertebral /in·ter·ver·te·bral/ (-ver´te-bral) situated between two contiguous vertebrae; see under disk.
Located between vertebrae. joint. (17,18)
Each specimen was then loaded in flexion flexion /flex·ion/ (flek´shun) the act of bending or the condition of being bent.
1. The act of bending a joint or limb in the body by the action of flexors.
2. , extension, right lateral bending, and left lateral bending. A load of 900 N was applied 2 cm anterior, posterior, right, or left of the center of rotation, respectively, to produce a maximum bending moment of 18 Nm. The specimen was never flexed more than 7[degrees] to prevent permanent deformity. As the last step in the loading sequence, axial torsion was applied. The specimen was first compressed to 900 N and then an axial torque was applied in a clockwise motion, to a maximum of 10 Nm. The angle of displacement was measured using a goniometer goniometer /go·ni·om·e·ter/ (go?ne-om´e-ter)
1. an instrument for measuring angles.
2. a plank that can be tilted at one end to any height, used in testing for labyrinthine disease. .
[FIGURE 1 OMITTED]
The loading sequence was initially performed on each of the intact motion specimens. The loading sequence was then sequentially tested on each of the specimens after placement of the following constructs: anterior femoral ring allograft (FRA Fra: see Angelico, Fra; Bartolommeo di Pagholo del Fattorino, Fra; Fra Filippo Lippi under Lippi. ), anterior FRA with posterior pedicle screw fixation, and anterior FRA with posterior TLS fixation.
For each individual test (except for torsion), a load-deformation curve was obtained. The stiffness of the motion segment was derived as the slope of the curve (from 450 N to 900 N).
An anterior interbody fusion was performed for each specimen. The anterior longitudinal ligament The anterior longitudinal ligament is a ligament that runs down the anterior surface of the spine. It traverses all of the vertebral bodies and intervertebral discs. and nucleus pulposus of L5-S1 were excised. An interbody femoral ring allograft (MTF (1) (Modulation Transfer Function) A measurement of monitor sharpness. MTF compares the contrast ratio between alternating black and green lines that are one pixel thick. , Synthes, Jessup, PA) was inserted via an anterior approach, and was centered within the disc space. A fully threaded screw with a washer was used anteroinferiorly to secure the graft.
Posterior pedicle screw fixation was then performed for each specimen. After proper identification of the entry point, four 6.2 mm self-tapping pedicle screws (Synthes Spine LTD LTD 1 Laron-type dwarfism 2 Leukotriene D 3 Long-term depression, see there 4. Long-term disability , Paoli, PA) were placed according to the manufacturer's protocol. The motion segment was then stabilized with two pre-cut rods. No cross-link was used. Following testing, the screws were removed.
Next, posterior TLS fixation was performed for each specimen. A long 3.2 mm drill was used to create a hole extending from the base of the spinous process transversely across the contralateral contralateral /con·tra·lat·er·al/ (-lat´er-al) pertaining to, situated on, or affecting the opposite side.
adj. lamina to transfix the facet joint. A 4.5 mm fully threaded self-tapping cortical screw (Synthes, Monument, CO) of 48 mm length was then inserted. A contra-lateral screw was inserted after pre-drilling in a similar manner.
A repeated measures analysis of variance (ANOVA anova
see analysis of variance.
ANOVA Analysis of variance, see there ) was conducted to compare the displacement of the intact specimens and the displacement of each of the other constructs. Significance was set at p < 0.05.
Of the specimens, 3/5 (60%) had severe degenerative changes of the L5-S1 segment and the remaining 2/5 (40%) had minimal to mild changes.
In compression, extension, and lateral bending, the intact specimens demonstrated the least amount of displacement. In flexion, the intact specimen demonstrated slightly more displacement than the specimen with FRA alone, but less displacement than the specimens with FRA and pedicle screws or FRA and translaminar screws. There was no statistically significant difference in displacement when the intact specimens were compared with the instrumented constructs.
In torsion-loading, the intact specimen exhibited more displacement than the instrumented constructs. The specimen with anterior interbody femoral ring allograft and pedicle screw fixation demonstrated the least displacement. However, there was no significant difference between any two conditions (p > 0.05).
Supplementation with pedicle screw fixation produced greater stiffness and stability than with translaminar screw fixation in compression, lateral bending, and axial torsion. Conversely, supplementation with translaminar screw fixation provided greater stability in flexion and extension. However, there was no significant difference in displacement between pedicle screw fixation and translaminar screw fixation (p > 0.05) (Fig. 2).
Our study demonstrated a very slight increase in intervertebral displacement when the intact specimens were compared with the femoral ring allograft constructs under all loading conditions except for torsion. However, there were no statistically significant differences in stability under any of the loading conditions. These findings are consistent with those of Rathonyi and coworkers (17) and Lund and colleagues (19) who found a slight increase in the range of motion of the unit after anterior or posterior interbody implantation, respectively. Moreover, Volkman and associates (16) reported a decrease in stiffness in both flexion and extension when stand-alone anterior interbody cages are used. Tencer and coworkers (20) found similar results, although they were not statistically significant. Upon insertion of the anterior femoral ring allograft, the implant rests on the endplate and relies on friction in order to resist sheer; therefore, the increase in displacement may be due to insufficient compressive com·pres·sive
Serving to or able to compress.
com·pressive·ly adv. force or insufficient friction. Under torsion loading, on the other hand, specimens with FRA constructs demonstrated less displacement than the intact specimens, although the differences were not statistically significant. These findings are consistent with those of Brodke and colleageus, (21) who showed that under axial torsion, stiffness increased by 50% with the insertion of a titanium basket into the interbody space. This may be due to the natural orientation of the facets, which provides an intrinsic resistance to torsion, as described by Eskander and associates. (22)
[FIGURE 2 OMITTED]
Previously, Volkman and associates (16) showed that supplementation with transfacet screw fixation increases motion stiffness, especially in extension, compared to anterior interbody reconstruction (using a cage) alone. Rathonyi and coworkers (17) similarly demonstrated that cage fixation alone provides good stability in flexion and lateral bending, but that translaminar fixation improves stabilization, particularly in extension and axial rotation. Lund and colleagues (19) demonstrated similar results for transpedicular fixation. Upon comparing the supplementation of anterior FRA with these two techniques, our study found only minimal differences in intervertebral displacement under all loading conditions except for torsion. Under torsion loading, supplementation with translaminar screw fixation resulted in greater intervertebral displacement and therefore less stability than supplementation with pedicle screws. However, there were no statistically significant differences in stability under any of the loading conditions, which may be due to our small sample size. These results are consistent with those of Eskander and associates, (22) whose findings implied that pedicle screw supplementation of anterior FRA provides greater stiffness than translaminar screw supplementation, although statistical significance was not demonstrated.
This study has several limitations. The active physiological loads on the spine are not fully understood. We applied 900 N (or 10 Nm in the torsion sequence) as this was used and studied by previous investigators. However, greater or lesser loads may exist in vivo. Another limitation is inherent to biomechanical studies using cadaveric motion segments (i.e. the lack of stabilization provided by the surrounding spinal musculature in vivo). Furthermore, three out of five of the motion segments were found to have severe degenerative changes at the L5-S1 segment. Significant anterior degenerative changes may have altered the properties of the intact spine segment, while posterior degenerative changes may have specifically affected intervertebral displacement in sequences such as extension and lateral bending. Additionally, it appeared that our specimens were harvested from rather elderly subjects and were thus osteopenic. This may have possibly caused undetected subsidence of the graft. However, since all specimens acted as their own controls, and had similar loading sequences and conditions, the results are comparable.
Of note, this study addresses only the immediate stability of various implant configurations. The effect of time on stability, fusion rates, and the maintenance of disc height was not evaluated. It is possible, therefore, that the immediate stability shown in our study is a worst-case scenario, and that stability may increase as bony fusion occurs.
Pedicle screw fixation can be useful as a means of augmenting anterior interbody grafting. However, the use of the pedicle screw entails considerably more cost, operative time, and intra-operative risk as compared to translaminar screw fixation. Our results show no statistically significant differences between pedicle screw versus translaminar screw supplementation of an anterior interbody femoral ring allograft in vitro. Therefore, translaminar screw fixation may be an effective alternative in selected cases.
We acknowledge the assistance of Mr. Rudi Hiebert for statistical analysis. The unrestricted grant from Synthes Spine Company LTD is gratefully acknowledged.
None of the authors have a financial or proprietary interest in the subject matter or materials discussed, including, but not limited to, employment, consultancies, stock ownership, honoraria, and paid expert testimony.
(1.) Katz JN, Lipson SJ, Chang LC, et al. Seven- to 10-year outcome of decompressive surgery for degenerative lumbar spinal stenosis. Spine. 1996;21(1):92-8.
(2.) Hodgson AR, Wong SK. A description of a technique and evaluation of results in anterior spinal fusion for deranged de·range
tr.v. de·ranged, de·rang·ing, de·rang·es
1. To disturb the order or arrangement of.
2. To upset the normal condition or functioning of.
3. To disturb mentally; make insane. intervertebral disk and spondylolisthesis spondylolisthesis /spon·dy·lo·lis·the·sis/ (-lis´the-sis) forward displacement of a vertebra over a lower segment, usually of the fourth or fifth lumbar vertebra due to a developmental defect in the pars interarticularis. . Clin Orthop Relat Res. 1968;56:133-62.
(3.) Zdeblick TA. A prospective, randomized study of lumbar fusion. Preliminary results. Spine. 1993;18(8):983-91.
(4.) King D. Internal fixation for lumbosacral fusion. J Bone Joint Surg Am. 1948;30(3):560-5.
(5.) Bosworth DM. Surgery of the spine. Instr Course Lect. 1957;14:39-55.
(6.) Boucher HH. A method of spinal fusion. J Bone Joint Surg Br. 1959;41(2):248-59.
(7.) Magerl FP. Stabilization of the lower thoracic and lumbar spine with external skeletal fixation. Clin Orthop Relat Res. 1984;(189):125-41.
(8.) Greenough CG, Peterson MD, Hadlow S, Fraser RD. Instrumented posterolateral lumbar fusion. Results and comparison with anterior interbody fusion. Spine. 1998;23(4):479-86.
(9.) Humke T, Grob D, Dvorak J, Messikommer A. Translaminar screw fixation of the lumbar and lumbosacral spine. A 5-year follow-up. Spine. 1998;23(10):1180-4.
(10.) Reich SM, Kuflik P, Neuwirth M. Translaminar facet screw fixation in lumbar spine fusion. Spine. 1993;18(4):444-9.
(11.) Liljenqvist U, O'Brien JP, Renton P. Simultaneous combined anterior and posterior lumbar fusion with femoral femoral /fem·o·ral/ (fem´or-al) pertaining to the femur or to the thigh.
Of or relating to the femur or thigh. cortical allograft. Eur Spine J. 1998;7(2):125-31.
(12.) Guyer DW, Yuan HA, Werner FW, et al. Biomechanical comparison of seven internal fixation devices for the lumbosacral junction. Spine. 1987;12(6):569-73.
(13.) Heggeness MH, Esses SI. Translaminar facet joint screw fixation for lumbar and lumbosacral fusion. A clinical and biomechanical study. Spine. 1991;16(6 Suppl):S266-9.
(14.) Panjabi M, Yamamoto I, Oxland T, et al. Biomechanical stability of five pedicle screw fixation systems in a human lumbar spine instability model. Clin Biomech. 1991;6(4):197-205.
(15.) Deguchi M, Cheng BC, Sato K, Matsuyama Y, Zdeblick TA. Biomechanical evaluation of translaminar facet joint fixation. A comparative study of poly-L-lactide pins, screws, and pedicle fixation. Spine. 1998;23(12):1307-12; discussion 1313.
(16.) Volkman T, Horton WC, Hutton WC. Transfacet screws with lumbar interbody reconstruction: biomechanical study of motion segment stiffness. J Spinal Disord. 1996;9(5):425-32.
(17.) Rathonyi GC, Oxland TR, Gerich U, et al. The role of supplemental translaminar screws in anterior lumbar interbody fixation: a biomechanical study. Eur Spine J. 1998;7(5):400-7.
(18.) Murakami H, Horton WC, Kawahara N, Tomita K, Hutton WC. Anterior lumbar interbody fusion using two standard cylindrical threaded cages, a single mega-cage, or dual nested cages: a biomechanical comparison. J Orthop Sci. 2001;6(4):343-8.
(19.) Lund T, Oxland TR, Jost B, et al. Interbody cage stabilisation in the lumbar spine: biomechanical evaluation of cage design, posterior instrumentation and bone density. J Bone Joint Surg Br. 1998;80(2):351-9.
(20.) Tencer AF, Hampton D, Eddy S. Biomechanical properties of threaded inserts for lumbar interbody spinal fusion. Spine. 1995;20(22):2408-14.
(21.) Brodke DS, Dick JC, Kunz DN, et al. Posterior lumbar inter body fusion. A biomechanical comparison, including a new threaded cage. Spine. 1997;22(1):26-31.
(22.) Eskander M, Brooks D, Ordway N, et al. Analysis of pedicle and translaminar facet fixation in a multisegment interbody fusion model. Spine. 2007;32(7):230-5.
Afshin E. Razi, M.D., Jeffrey M. Spivak, M.D., Frederick J. Kummer, Ph.D., and Jeffrey A. Goldstein, M.D., are in the Department of Orthopaedic Surgery, NYU NYU New York University
NYU New York Undercover (TV show) Hospital for Joint Diseases, 301 East 17th Street, New York, New York. David S. Hersh, M.D., is a resident in the Department of Neurosurgery, University of Maryland University of Maryland can refer to:
Correspondence: Afshin E. Razi, M.D., Department of Orthopaedic Surgery, NYU Hospital for Joint Diseases, 145 East 32nd Street, 4th Floor, New York, New York, 10016; email@example.com.