Effect of different surgical strategies on screw forces after correction of scoliosis with a VDS implant
Authors
- First Online:
- Received:
- Revised:
- Accepted:
DOI: 10.1007/s00586-005-0923-5
- Cite this article as:
- Rohlmann, A., Richter, M., Zander, T. et al. Eur Spine J (2006) 15: 457. doi:10.1007/s00586-005-0923-5
- 12 Citations
- 176 Views
Abstract
Pullout of the cranial end-vertebra screw following the correction of a scoliosis with the VDS implant is a common complication. Very little is known about the forces acting on the screws during ventral derotation spondylodesis (VDS) in ventral scoliosis surgery. These forces determine the risk of screw-loosening. The purpose of this study was to identify implant properties and to determine surgical correction strategies that reduce the risk of cranial end-vertebra screw pullout. For this aim, a three-dimensional nonlinear finite element model of a scoliotic thoracic spine was created with a Cobb angle of 61° and 32° rotation. The VDS implant was inserted between T5 and T9. The longitudinal rod diameter, the implant material and seven surgical correction strategies were examined to determine their influence on the Cobb angle as well as on derotation and on axial and transverse forces in the screws. A stiffer implant achieves a better correction but causes higher axial and transverse screw forces. Axial tensile forces act on the screws fixed to the cranial end vertebra and the middle vertebra, while axial compressive forces act on the other screws. A strong correction at the cranial segment leads to high axial and transverse screw forces in the farthest cranial screw and thus to a high risk of screw pullout. The resultant transverse force is often much higher than the axial force component. Simulation of local trunk muscle forces has only a minor effect on the results. The axial tensile forces and thus the risk of screw pullout are highest at the cranial end vertebra. A strategy in which surgical correction is strong in the middle segments and moderate in the outer ones leads to a good reduction of the Cobb angle, a wide derotation angle, and relatively low axial tensile forces at the cranial end vertebra screw.
Keywords
ScoliosisVentral derotation spondylodesis (VDS)Finite element analysisSurgical strategyScrew forceIntroduction
Surgical correction may be indicated for scoliotic thoracic spines with a Cobb angle of more than 40° [4]. Ventral derotation spondylodesis (VDS) is still regarded as one of the most important procedures in ventral scoliosis surgery. It corrects by compression and derotation and achieves excellent surgical results with a short fusion length [3]. The VDS implant (Ulrich Co., Ulm, Germany) is a flexible single-rod system for ventral surgical treatment of scoliosis that was introduced by Zielke et al. [15]. During surgery via an anterior approach, screws are inserted laterally on the convex side of the vertebral bodies. A flexible threaded longitudinal rod is fixed to the screw heads by special nuts whose cylindrical part fits into them. Tightening the two nuts on either side of the screw head ensures that the rod direction in the head is perpendicular to the screw axis. Correction of scoliosis is achieved by reducing the distances between the screw heads. This means that the nuts on the rod are tightened in the direction of the apical vertebra. The spine is compressed on the convex side and decompressed on the concave side. Segmental derotation requires resection of the intervertebral discs in the bridged region. They can be replaced by bone from the bone mill or bone grafts from the ribs or iliac crest or by cages. The application of bone material or cages depends on the sagittal profile. The outer nut of a screw carries the force component perpendicular to the screw axis, while the nut closer to the apical vertebra mainly serves to secure the rod in the screw head. Little is known about the loads acting in the screws during correction of scoliosis.
On the outermost screws of the VDS implant, a unilateral force acts in the direction of the longitudinal rod, while the other screws are subject to two forces acting in opposite directions, thus reducing the resultant transverse force on the screw. Straightening the spine increases the axial and transverse forces on the screw head. The transverse force may weaken the bone around the thread and lower the pullout resistance against the axial force. Due to the unilateral transverse force acting on the screws, the reduction of pullout strength is most pronounced at the end vertebrae. The width of vertebrae in the frontal plane decreases from caudal to cranial. Thus the cranial end vertebra probably has the lowest pullout strength. This is also the vertebra where most screw pullouts have been observed during VDS, especially in patients with rigid scoliosis [5, 6]. Pullout of the screw does not necessarily occur during corrective surgery. Applying high corrective forces may reduce the fixation strength intraoperatively to the extent that the screw is already on the verge of being pulled out. The screw may be loosened during slight movements without the patient’s controlling force, as when shifting the still intubated patient. This complication may require extension of the fusion length or it reduces the outcome of the correction surgery. Moreover, screw dislocation may also cause injury to thoracic or abdominal organs or vessels.
The axial pullout strength of vertebral screws has been measured in vitro [1]. However, it is reduced in surgical correction of scoliosis, since the screws are additionally loaded perpendicular to their axis. Ogon et al. [8] compared fixation strength of single VDS screws and triangulated double screws. They performed pull-out tests and applied a load perpendicular to the screw axis. The triangulated, double-screw fixation led to a 73% increase in resistance against load perpendicular to the screw axis compared with resistance produced using VDS single-screw instrumentation. The pullout force during surgical correction of scoliosis cannot be measured. However, the finite element method enables an analytical estimation of axial forces on the screw head. It also allows the simulation of different strategies for reducing the axial screw force in the cranial end vertebra.
The aims of this paper were to calculate the loads on the screws as well as the changes in Cobb angle and derotation for (i) different implant properties and (ii) several strategies for scoliosis correction.
Methods
Finite element model
Material properties
Material | Elastic modulus (N/mm^{2}) | Poisson’s ratio (−) |
---|---|---|
Cortical bone | 12,000 | 0.3 |
Cancellous bone | 500 | 0.3 |
Annulus fibrosus | 4.2 | 0.45 |
Nucleus pulposus | 1.1 | 0.499 |
Implant steel | 210,000 | 0.3 |
Titanium alloy | 110,000 | 0.3 |
Stiffness coefficients (N/mm for forces and Nm/deg for moments) of a functional spinal unit. The upper part indicates the values used in the current study and the lower part the extreme values calculated from the experimental data of Panjabi et al. [9]
Region | Forces | Moments | Remark | |||||
---|---|---|---|---|---|---|---|---|
Tension | Compression | Shear | Flexion | Extension | Lat.Bending | Axial Rot. | ||
T1/2-T4/5 | 770 | 1,250 | 110 | 2.22 | 2.80 | 2.80 | 2.53 | Average values from [9] |
T5/6-T8/9 | 770 | 1,550 | 235 | 2.00 | 2.00 | 2.18 | 3.07 | |
T9/10-T11/12 | 770 | 1,250 | 110 | 2.22 | 2.80 | 2.80 | 2.53 | Average values from [9] |
T1/2-T11/12 | 423 | 579 | 41 | 1.05 | 1.67 | 1.73 | 1.30 | Minimum values calculated from [9] |
T1/2-T11/12 | 3,667 | 11,000 | 375 | 3.33 | 13.3 | 6.33 | 5.57 | Maximum values calculated from [9] |
Screws were securely inserted on the convex side of the five vertebrae T5–T9, and a longitudinal rod was connected to the screw heads. The farthest cranial screw is designated as screw 1 and the farthest caudal one as screw 5. The screw positions on the circumference of the vertebral body were chosen according to the axial rotation of the spine. This caused a derotation during the correction procedure. The derotator of the VDS implant was not included in our computer model, since it is not used by many surgeons nowadays. Beam elements were used to represent the screws and rod. In the bridged region, contact was defined as allowing the transmission of compressive force between adjacent vertebrae.
The finite element program ABAQUS and the pre- and post-processor MSC/PATRAN were used. The highly nonlinear model can reproduce large deformities and nonlinear material properties, and contact behavior can be simulated.
Correction of scoliosis
Correction of scoliosis was simulated in two steps. (1) The initially straight longitudinal rod was connected to the screw heads of the scoliotic spine. The rod elasticity exerted different forces on the screw heads and led to a slight correction of the scoliosis. (2) The distance between the end screw heads was reduced by 16 units. The standard case showed a 4-unit reduction in each of the four segments. One unit is equivalent to 1.2 mm.
Implant properties
The VDS implant is available with rod diameters of 3, 4 and 5 mm. If not explicitly stated otherwise, a 3 mm rod was assumed in the model. The VDS implant is normally made of implant steel, but titanium alloy implants are also available. In a parameter study, the rod diameter and elastic material properties were varied accordingly.
Simulated surgical correction strategies
Distance reduction between adjacent screws for different surgical correction strategies
Strategy Code | Reduction at T5/T6 (mm) | Reduction at T6/T7 (mm) | Reduction at T7/T8 (mm) | Reduction at T8/T9 (mm) |
---|---|---|---|---|
1555 | 1.2 | 6.0 | 6.0 | 6.0 |
2266 | 2.4 | 2.4 | 7.2 | 7.2 |
2662 | 2.4 | 7.2 | 7.2 | 2.4 |
4444 | 4.8 | 4.8 | 4.8 | 4.8 |
6226 | 7.2 | 2.4 | 2.4 | 7.2 |
5551 | 6.0 | 6.0 | 6.0 | 1.2 |
6622 | 7.2 | 7.2 | 2.4 | 2.4 |
Only a slight distance reduction was achieved at the farthest cranial scoliotic segment by strategies 1555 and 2266 and at the farthest caudal segment by strategies 6622 and 5551 (Table 3). The screw distance reduction was low for both outer segments in strategy 2662 and for the inner segments in strategy 6226. In strategy 4444 the reduction was equal at all segments. Strategy 4444 (with a 3 mm steel rod) is the ‘reference case‘ if not explicitly stated otherwise.
Boundary conditions
The nodal points of the caudal T12 vertebral endplate were rigidly fixed. The patient is anesthetized during surgery and thus exerted no active muscle forces. In a lying position, local muscles stabilize the position of the vertebrae relative to each other when the patient is not anesthetized. These local muscles can be simulated by applying a follower load [10, 11], which is a compressive load whose direction follows the curvature of the spine. In the finite element model the follower load was simulated by forces acting in the centers of the vertebral bodies and directed to the centers of adjacent vertebrae, except for the most cranial vertebra where only a force in the caudal direction was applied. A follower load of 280 N was applied to simulate the situation directly after surgery when the conscious patient is in a lying position.
Evaluation
The following parameters were determined: the Cobb angle, derotation, the axial force at each of the five screw heads, and the resultant force perpendicular to the screw axis acting at the five screw heads.
Results
Effect of implant properties
The Cobb angle is reduced from 61° to 35° by correction with the 3 mm VDS implant and using strategy 4444. With a titanium implant, this angle increases by less than 1°. A 4 mm (5 mm) longitudinal rod reduces the Cobb angle to 31° (25°), thus improving the correction. Derotation is 5.8° for the standard implant and 5.5° for the titanium one. It is increased to 6.9° by a 4 mm rod and to 8.2° by a 5 mm one.
Effect of surgical correction strategies
Discussion
A finite element model of the thoracic spine was used to simulate different implant properties and surgical strategies for correction of scoliosis with a VDS implant. This study has a number of limitations. The investigation covered only one type of scoliosis with a Cobb angle of 61° and a rotation of 32°, although each type is different. Only the situations during the surgical procedure and immediately postoperatively were studied since they represent the situations where most screw pullouts occur. Like all finite element studies dealing with the spine, this one also required several assumptions and simplifications. A simplified geometry was applied in representing the vertebrae as cylindrical bodies. Several spring elements in the intervertebral space were used to simulate the posterior parts of the vertebra, the rib-cage and the ligaments. The springs were adapted to intervertebral stiffness values reported in the literature. The material properties of the different spinal structures were also taken from the literature. They were determined in normal specimens and may thus differ from those of a scoliotic spine. Bone grafts or cages were not included in the model since, if at all, they are normally placed anteriorly to avoid an unphysiological spinal curve in the sagittal plane. In addition, they are mostly inserted during the last phase of the correction procedure. However, a stiff bone graft or a cage may alter the center of rotation of a vertebra and thus affect the screw forces. In a pilot study, we could show that bone meal in the intervertebral space has only a minor effect on the results.
The local muscles were represented by a follower load, but it has not yet been proven that this delivers realistic results in the case of a scoliotic spine. Only one value was used for the follower load in this study. Since we were mainly interested in the axial screw forces, the computer model was loaded by the implant and a follower load, while all other forces were disregarded. All these simplifications suggest that the results are qualitative and should be seen as trends rather than exact values.
Finite element models of complex structures like the spine should generally be validated by experimental data. Only very few measured data are available on scoliotic spines since it is extremely difficult to obtain such specimens. To our knowledge, there are no experimental data on implant screw forces during the correction of scoliosis. The scoliotic thoracic spine is curved in the sagittal and frontal planes and rotated in the transverse plane. It is not easy to predict the forces acting on the screws. Therefore a pilot study was done using a model curved only in the frontal plane. After insertion of the implant, the axial screw forces showed the expected pattern, i.e. tensile axial forces in the outer and compressive ones in the inner screws. The load components in the longitudinal rod segments and the loads on the screw part inside the vertebral body were also studied to check the model.
Clinical decisions should not be made solely on the base of finite element calculations since the computer models represent mostly an ideal situation and many factors and possible situations are neglected. This is especially true when the computer model cannot be validated with experimental data. Our results quantitatively justify the intuitive approach of many spine surgeons. Since each scoliosis is different, only trends can be expected from a finite element study.
A stiffer implant (thicker rod) leads to a lower Cobb angle and higher derotation, since the predetermined reduction of screw distances on the threaded rod causes a smaller deformation of the implant itself. Correction mainly in the outer segments (strategy 6226) slightly improves the Cobb angle and the derotation. The best correction of the Cobb angle is achieved with a thick longitudinal rod and a small correction at the cranial segment. The greatest derotation is achieved by a thick implant rod and a small correction at the caudal segment. Our model did not assume the application of the derotator. Instead, the screws were placed according to the rotation of the spine. During surgery, the distances between screw heads are not reduced in one step but in intervals to allow relaxation of the soft tissues. Our computer model did not account for the viscoelastic behavior of the spine.
During correction, bone contact is established between adjacent vertebrae by their gradual convergence. The point of contact then becomes the center of rotation for further correction. There is also a strong increase in the stiffness and screw forces. This explains the high screw forces associated with certain strategies (Figs. 7 and 8). When stiff bone grafts or cages are inserted in the intervertebral space prior to correction they may become the center of rotation, which may affect the screw forces and the correction angle. The results will then depend on the level of the stiff bone graft or cage and the position within the intervertebral space.
An axial tensile force is found in the screw of the cranial end vertebra and in screw 3. The axial force in the latter is normally much smaller than in screw 1. The axial compressive force in the other screws does not cause screw pullout. In the screw of the cranial end vertebra, the axial tensile force is highest for a stiff longitudinal rod. A strong correction at the farthest cranial segment also increases the axial tensile force in screw 1. Low axial tensile forces in screw 1 are achieved by a 3 mm titanium rod and small corrections at the farthest cranial segment.
The resultant force perpendicular to the screw axis is highest at the screws of the end vertebrae (screws 1 and 5) in cases with a uniform correction at all segments (Fig. 3). In the other screws, the caudally directed transverse correction force partly compensates the cranially directed one. The relatively high transverse force at screw 3 is partly due to the force causing the derotation. Rotation is greatest at the apical vertebra. A high transverse force reduces the pullout strength of a screw and may even cause the screw to cut through the cancellous bone of the vertebral body. Screw 1 has a low transverse force if the correction at the farthest cranial segment is small.
A high transverse force widens the screw hole due to the viscoelastic behavior of bone. Combined with a high axial screw force, this leads to a high risk of screw pullout. Strategy 2662 results in a marked reduction of the Cobb angle, a wide derotation angle, a relatively low axial tensile force in screw 1 and moderate transverse forces in the other screws. Thus our calculations predict that this strategy achieves good scoliosis correction with a low risk of screw pullout. It must be noted, however, that the sum of segment corrections is not constant during surgery. Thus combinations other than the one studied may lead to slightly better results.
Conclusions
The axial tensile forces and thus the risk of screw pullout are highest at the cranial end vertebra. A stiffer implant achieves a better correction but causes higher axial and transverse screw forces. A strategy in which surgical correction is strong in the middle segments and moderate in the outer ones leads to a good reduction of the Cobb angle, a wide derotation angle, and relatively low axial tensile forces at the cranial end vertebra screw.
Acknowledgements
Finite element analyses were performed at the Norddeutscher Verbund für Hoch- und Höchstleistungsrechnen (HLRN) and the Zentraleinrichtung Rechenzentrum Berlin (ZRZ). The authors thank Dr. J.Weirowski for editorial assistance.