Research Article Volume 2 Issue 2
^{1}Department of spinal cord and spine pathology, Romodanov Neurosurgery Institute of National Academy of Medical Sciences of Ukraine, Ukraine
^{1}Department of spinal cord and spine pathology, Romodanov Neurosurgery Institute of National Academy of Medical Sciences of Ukraine, Ukraine
Correspondence: Alexey S Nekhlopochin, Department of spinal cord and spine pathology, Romodanov Neurosurgery Institute of National Academy of Medical Sciences of Ukraine, Ukraine
Received: December 04, 2018  Published: April 19, 2018
citation: Slynko II, Nekhlopochin AS. The clinically and biomechanically based optimization of sagittal contour surgical correction of the injured segment with the anterior subaxial fusion. MOJ App Bio Biomech. 2018;2(2):150–155. DOI: 10.15406/mojabb.2018.02.00058
The anterior decompressionfusion surgery is currently the most effective treatment method for number of pathological conditions and traumatic injuries of the cervical spine. The study is devoted to the surgery and implant optimization, to achieve the optimal state of sagittal kyphosis in patients after anterior subaxial cervical fusion. The retrospective analysis of 151 clinical cases was held; the nonlinear dependence of the final results of treatment on the degree of correction was revealed using regression analysis, the finite element analysis of the cervical spine models with different parameters of segmental kyphosis of the operated segment was carried out. As a result, the optimal parameters of sagittal contour correction of the operated cervical spine were determined.
Keywords: subaxial level, implanted systems, surgical, technical issues, clinical efficiency, bodyreplacing
Decompressionfusion surgery is the most common method of correction of the subaxial cervical spine traumatic injury, accompanied by compression of neural structures.^{1,2} Vertical cylindrical cancellous implant (mesh cage or mesh) has been widely used as a bodyreplacing structure for the last few decades. The literature analysis demonstrates a high clinical efficiency of combined application of mesh and anterior rigid plate.^{3} At the same time a number of authors report rather high frequency of unsatisfactory results such as dislocation, migration, fragmentation of the implanted systems, loss of intraoperative correction and the neural disorder increasing.^{4–7} Despite the rather contradictory assessment, the combined use of mesh and anterior rigid plate de facto is the standard for decompressionfusion surgery at the subaxial level of the cervical spine.^{5} At the same time, technical issues of surgical correction are described quite poorly. Currently, there is no consensus about optimal correction of the operated vertebral segment height and the formation of a certain segmental kyphosis of the cervical spine in the surgical intervention area.^{8} Subjective approach often leads to unsatisfactory results and loss of achieved correction in the longterm postoperative period.^{9}
To improve the state of sagittal kyphosis of the operated segment in the delayed patients' postoperative period, who underwent anterior subaxial fusion using the combination of mesh and rigid plate.
Retrospective estimation and analysis of the spondylometry sagittal kyphosis state of the operated spine segment just after fusion and 1 year later;
We performed retrospective analysis of the surgery results of patients with traumatic cervical spine injury that had been hospitalized in the spinal cord and spine pathology department of Romodanov Neurosurgery Institute of National Academy of Medical Sciences of Ukraine in the period from 2006 to 2016. The inclusion items were the following:
151 medical cases were chosen satisfying the above mentioned parameters.
Spondylometry technique
The state of the operated spine segment was evaluated as segmental kyphosis (SK). The measurement was performed with two methods:
Statistical analysis
We determined the dependence of the final values of SK on the values of SK achieved during decompressionfusion surgery. Based on the analysis of roentgenogram SKfin=f(SKint) was calculated. Taking into account the specifics of the distribution of the analyzed values, a nonlinear regression analysis with least squares principle was used to identify the mathematical dependence. Levenberg – Marquardt algorithm was used as an optimization method. Evaluation of the suitability of the model was carried out by calculating the determination coefficient R2. The correlation matrix was analyzed to exclude unnecessary parameters of the model. The statistical significance of the calculated coefficients of the model was estimated using the criterion χ2. The residual analysis was executed by evaluating the distribution normality using KolmogorovSmirnov criterion and analyzing normal and seminormal graphs. Cluster analysis was executed by the Kmeans method. Statistical confidence was estimated by analyzing the sum of squares of deviations between the cluster centers and the sums of squares of deviations of objects from the cluster center. The calculations are carried out with the use of statistical and analytical package Statistica ^{10}.
Estimation of the stressstrain state
The finite element analysis of the designed models of the human cervical spine in the area from the C3 vertebra to the C7 vertebra was executed. The C5 vertebra was replaced with a vertical cylindrical mesh implant, the stabilization was supplemented with anterior rigid plate with fixed screws. The models had different values of SK spine segment in zone of “operation”. The stressstrain state of the models was studied in the following loading options: compression, bending forward, bending backward and rotational effects. The model had rigid fixing at the bottom plane of the vertebral body C7 and joint masses. The load intensity on the models was 100 H. Compression loading was carried out by the distributed loading 36 N on the top surface of a body of a vertebra of C3 and 32 N on the top plane of its arc joints. Forward bending was simulated by a load of 100 N on the anterior edge of the vertebral body C3, backward bending – by a load of 50 N on its arcs. The rotational load was carried out by force of 100 N on the upper surface of the vertebral body C3. Von Mises tension was used to estimate the stress strain state of the models.^{11}
The spondylometry data is shown in Figure 1. Following the above mentioned method, the average values were analyzed. When using different methods for the SK determination, the maximum difference was 1,20, the average of the module difference for all clinical cases 0,2840±0,0460, that indicates a high results comparability (correlation r=0,97). A visual analysis of the distribution allows to suggest that the optimal function with the least number of coefficients is a parabola $\left(y=a{x}^{2}+bx+c\right)$ . During the relevant calculations, the assumption is confirmed by a sufficiently high value of the coefficient of determination (R2=0,8914). Model characteristics is defined in the third iteration. As a result, the function is revealed which describes the nature of the dependence of the analyzed indicators the most effectively: $S{K}_{fin}=0,182626*S{K}_{int}{}^{2}+1,85793*S{K}_{int}+2,92143$ The analysis of the correlation matrix demonstrates quite convincingly the absence of unnecessary components of the reduced formula (Table 1). Attention is paid to the sufficiently high value of correlation $S{K}_{fin}=0,182626*S{K}_{int}{}^{2}+1,85793*S{K}_{int}+2,92143$ and $b$ coefficients of the model, which is naturally explained by a fairly narrow range of initial values (Table 2). The residual analysis results (Figure 2) are also testified in favor of adequacy of the received model. Thus, the evaluation demonstrates a sufficiently high representativeness and predictive efficiency of the obtained dependence. The next stage of the analysis was to assess the nature of the deviation of real indicators from the predicted values. The visual evaluation of the graph of distribution (Figure 1) allows to mark out 3 ranges $S{K}_{int}$ t which $S{K}_{fin}$ shows the specificity of dispersion relative to$S{K}_{fin}=f\left(S{K}_{int}\right)$. The following tendency revealed:
With the purpose of objectifying boundaries of these groups, which are differ in their correlation of SKfin и SKint we used the cluster analysis with Kmeans method. The obtained results are shown in Figure 3. The statistical reliability of the analysis is presented in Table 3. Taking into consideration that the cluster analysis findings are characterized by a high level of the statistical significance, we determined the boundaries of the clusters at the $S{K}_{int}$ , which were as follows: 1st cluster:$S{K}_{int}>3,{10}^{0}$ ; 2nd cluster:$6,{15}^{0}<\text{}S{K}_{int}3,{10}^{0}$ ;3d cluster:$S{K}_{int}<\text{}6,{15}^{0}$ . Consequently, the obtained data allows considering the intraoperative range $SK\approx {6}^{0}\mathrm{..}{3}^{0}$ as the optimal for saving the indicators of correction in the late postoperative period (Figure 4). Subsequently, the biomechanical verification of the results was executed. It was analyzed 3 finite element models of the cervical spine. The SK of spine segment with fusion system were corresponded to the centers of the obtained clusters and arranged 1,80; 4,60 and 7,80. Models marked as “$SK1,{8}^{0}$ “, “$SK4,{6}^{0}$ and “$SK7,{8}^{0}$ “.The maximum values of equivalent von Mises stresses were estimated in the following model elements: the upper laminar plate of C6 vertebra body, the lower laminar plate of C4 vertebra body; arcs roots and articular masses of C4 and C6 vertebrae, screws fixing the anterior plate that are located in the bodies of C4 and C6 vertebrae. The peak values of the equivalent stresses were registered in the analyzed model elements and are shown in Figure 5.
The load distribution analysis in the contact zone of the vertebral plates with the implanted bodyreplacing system reveals the following regularitie
Compression action on the operated cervical spine causes the maximum loading of the lower locking plate of the C4 vertebral body during the formation of $SK7,{8}^{0}$ . Thus, the value of the equivalent tension is 8,4MPa, that is 2,3MPa more than the SK4,60 model and 1,9MPa more than the $SK1,{8}^{0}$ . Loading of the upper laminar plate of the body C6 during compression demonstrates some other results. Consequently the values for$SK4,{6}^{0}$ and $SK7,{8}^{0}$ models are almost identical and arrange respectively 7,2MPa and 7,.3MPa, while the minimum values of segmental kyphosis provide tension of 6,3MPa. The extension load provokes the following redistribution of von Mises equivalent tension on the analyzed models. The lower laminar plate of C4 vertebra shows the highest values with SK equal to 7,80, that is manifested by the peak value of the tension of 8,6MPa. The minimum tension is fixed with $SK1,{8}^{0}$ and it is arranged 7,5MPa. In the model $SK4,{6}^{0}$ the corresponding value is registered at the level of 7,7MPa. The maximum value of the stress on the upper surface of the body C6 was recorded at $SK4,{6}^{0}$ and is 7,5MPa, while for the models $SK1,{8}^{0}$ and $SK7,{8}^{0}$ this figure is less, respectively, 0,4MPa and 0,2MPa. In a series of the load tests, the flexion emulation impact demonstrates the highest von Mises stress. So, on the lower laminar plate of C4 the analyzed value was calculated for models$SK1,{8}^{0}$ , $SK4,{6}^{0}$ and respectively 9,7MPa, 8,1MPa and 11,2MPa. A similar pattern was observed in the analysis of stress on the upper surface of the body C6. The minimum value is registered when loading$SK4,{6}^{0}$ model and made 6,5MPa. The maximum was observed in $SK7,{8}^{0}8,9$ MPa, while the value of 7,9MPa was observed with$SK1,{8}^{0}$ . The modelling of the rotational load demonstrates the expected low values of the equivalent stress of the anterior support complex in the area of the operated vertebral segment. So, on the lower surface of the body of C4 models$SK1,{8}^{0}$ , $SK4,{6}^{0}$ and $SK7,{8}^{0}$ peak values arranged, respectively, 3,5MPa, 3,3MPa and 4,1MPa. A similar pattern is recorded in the analysis of the equivalent stress in the contact zone of the implanted system and the upper surface of the body C6. The maximum value of 3,4MPa is marked at $SK7,{8}^{0}$ , the minimum one is registered at $SK4,{6}^{0}$ and is 2,6MPa.
The tension distribution on the C4 and C6 vertebrae arcs roots with the different loading options of the analyzed models is the followin
The C4 vertebra is the least loaded in a case of compression effect with the$SK7,{8}^{0}$ , the equivalent tension is 5,9MPa. The highest load value of the analyzed zone was noted in the model and amounted to 6,8MPa. In contrast, the roots of C6 vertebral arc of all analyzed models demonstrate significantly higher values of the analyzed parameter. Thus, the maximum amount is observed in the model $SK7,{8}^{0}$ and arranged 18,2MPa, the lowest value of 16,9MPa was in the kyphosis formation 1,80. The extension loading causes peak values at the roots of arcs in all analyzed models. For the C4 vertebra the equivalent stress was 9,2MPa, 10,0MPa and 12,4MPa for models$SK1,{8}^{0}$ , $SK4,{6}^{0}$ and$SK7,{8}^{0}$ respectively. The C6 vertebra is loaded more significantly. Thus, for the model $SK7,{8}^{0}$ the value of the arc root von Mises equivalent tension was 25,3MPa, which is the maximum of all values obtained in the experiment. Model $SK1,{8}^{0}$ demonstrates lower data – 22,4MPa. The most biomechanically favorable is the formation of sagittal kyphosis 4,60, which provides the load of the analyzed zone no more than 20,2MPa.The flexion of the cervical spine almost completely unloads the elements of the rear support complex. At the same time, for C4 vertebrae, the equivalent stress on the roots of arcs of all analyzed models is practically the same and is 0,8MPa, 0,9MPa and 1,1MPa, respectively,$SK1,{8}^{0}$ , $SK4,{6}^{0}$ and$SK7,{8}^{0}$ . Almost identical pattern was observed in the analysis of the C6 arc root: 0,9MPa, 1,1MPa and 1,2MPa. The changes of the SK operated segment practically does not affect the arc root load of the C4 vertebra under the rotational action. Thus, the values of the equivalent tension were 5,8MPa, 6,0MPa and 6,2MPa for models$SK1,{8}^{0}$ , $SK4,{6}^{0}$ и$SK7,{8}^{0}$ . A lightly different pattern was observed when loading of the root of the vertebral arch, located below the resected one. Thus, the maximum tension value is calculated in the model $SK1,{8}^{0}$ and was 8,2MPa, while for SK equals to 4,60 the analyzed parameter is 6,0MPa.
The loading of the articular masses of the vertebrae which are adjacented to the resected one is similar to the nature of the load distribution on the arcs roots, but in some cases has its own characteristics
The articular masses of C4 vertebrae of the analyzed models demonstrate the highest values of equivalent stresses under compression and extension. Thus, the compressive load causes the analyzed parameter to 3,2MPa, 2,8MPa and 2,4MPa, respectively, for$SK1,{8}^{0}$ , $SK4,{6}^{0}$ и$SK7,{8}^{0}$ . In the modeling extension, the maximum value was noted in the $SK7,{8}^{0}$ model and was 5,5MPa, while for$SK1,{8}^{0}$ , $SK4,{6}^{0}$ the values were 4,5MPa and 3,8MPa, respectively. At a flexion load, the values of the equivalent tension are corresponding to the range of 0,30,6MPa while the highest value is noted in the model$SK1,{8}^{0}$ . Similar to the arc root C4, the change of SC practically does not affect the level of loading of the articular masses of the C4 vertebra during rotation, the equivalent stress values correspond to the range of 0,91,1MPa. A similar pattern was observed with analysis of C6 vertebra. Under the compression, the highest indices were registered in the model $SK7,{8}^{0}$ and amounted to 3,2MPa, the lowest 2,6MPa in$SK1,{8}^{0}$ . The extensional loading demonstrates the clear advantage of$SK4,{6}^{0}$ , which is manifested by the value of the analyzed indicator 3,5MPa in comparison with 6,5MPa and 6,8MPa for $SK1,{8}^{0}$ and $SK7,{8}^{0}$ respectively. The cervical spine flexion naturally demonstrates the minimal stress values of the articular masses of the vertebrae, the range of values corresponds to 0,10,2MPa. With the rotation, the analyzed zone of model $SK4,{6}^{0}$ is less loaded –2,2MPa, while for $SK1,{8}^{0}$ and $SK7,{8}^{0}$ this index is 2,9MPa and 3,2MPa, respectively.
The analysis of the equivalent tension on fixing screws allows to reveal the following features
Under compression loading, the upper pair of screws shows the highest values of equivalent stress in the model$SK1,{8}^{0}$ , that was 9,2MPa. The load in $SK7,{8}^{0}$ is 0,1MPa less. The most biomechanically favorable for the analyzed value was $SK4,{6}^{0}$ , the load made 8,2MPa. A similar pattern was observed in the analysis of the lower screw pair: 3,2MPa, 2,8MPa and 2,7MPa for$SK1,{8}^{0}$ , $SK4,{6}^{0}$ and $SK7,{8}^{0}$ respectively.The еxtension in all cases is accompanied with decrease of tension in the screw pairs, that is caused with the load transfer to the rear support complex. Thus, for $SK1,{8}^{0}$ and $SK4,{6}^{0}$ , the values of von Mises equivalent tension on the top pair of screws were decreased in comparison with the compression load by 1,5MPa and 0,4MPa and amounted to 7,7MPa and 7,8MPa, respectively. In the model $SK7,{8}^{0}$ no changes are observed and the tension is 9.1MPa.The lower screw pair is also characterized by the load reduction. The highest indices, however, were registered in $SK1,{8}^{0}$ model and arranged up to 2.8MPa, while for $SK4,{6}^{0}$ and $SK7,{8}^{0}$ the equivalent stresses were determined as 1,1MPa and 1,5MPa, respectively. The flexion load causes a significant increase in the stress on the fixing elements of the anterior plate. Thus, the highest rates were registered when modeling 7,80 SC and amounted to 11,2MPa on the upper screw pair. For$SK1,{8}^{0}$ , $SK4,{6}^{0}$ , these values are corresponded to 10,2MPa and 9,5MPa, respectively. The lower pair of screws in the modelling front bending remains less loaded. The values of equivalent tension for model $SK1,{8}^{0}$ , $SK4,{6}^{0}$ and $SK7,{8}^{0}$ correspond to 4,5MPa, 3,2MPa and 4,8MPa.The rotation modeling for the upper screw pair shows the maximum load at kyphosis 7,80 (10,0MPa), while the lower screw pair is significantly overloaded with a minimum value of SK. So for $SK1,{8}^{0}$ the equivalent stress was 7,2MPa, while for models $SK4,{6}^{0}$ and $SK7,{8}^{0}$ only 4,2MPa and 4,3MPa.
Consequently, summarizing the finite element analysis data, it is possible to identify the following patterns:
Figure 1 N=57; Epidemiological distribution of the pathological fractures, traumatic fractures, and nonunion.
Figure 1 Dependence of sagittal kyphosis values of the operated segment in the delayed postoperative period on the value of intraoperative correction and prognostic SKfin=f(SKint).
Figure 4The pattern of the finiteelement model “SK 4,60” with the different loading options: (A) compression, (B) extension, (C) inflexion, (D) rotation.

A 
B 
C 
A 
1,000000 
0,974551 
0,819138 
B 
0,974551 
1,000000 
0,913061 
C 
0,819138 
0,913061 
1,000000 
Table 1 The correlation matrix of the calculated coefficients of the model

Аverage value 
Standard 
t (df = 148) 
p 
Confidence interval (alpha=0.05) 


low 
top 

a 
0,182626 
0,008965 
20,37046 
0,00 
0,164909 
0,200342 
b 
1,857933 
0,090267 
20,58268 
0,00 
1,679555 
2,036311 
c 
2,921429 
0,195262 
14,96161 
0,00 
2,535568 
3,307289 
Table 2 The reliability estimation of the calculated coefficients of the model

Sum of squares of the deviations between the cluster centers 
df 
Sum of squares of the deviations of objects from cluster center 
df 
F 
Importance, p 
SKint 
838,5718 
2 
101,9286 
148 
608,8019 
<0,000001 
SKfin 
140,4024 
2 
80,4737 
148 
129,1077 
<0,000001 
Table 3 Results of the dispersive estimation based on cluster analysis
Since the first successful anterior decompressionfusion cervical surgery and up to the present time, the technical aspects of performing surgical correction remain very discounted. The corporotomy with subsequent stabilization at subaxial level despite the relatively high risks in some cases remains the only effective method of decompression spinal cord in traumatic injuries and neoplastic and inflammatory processes in vertebral bodies, degenerative changes of the cervical spine, which are provoking the compression of the ventral spinal cord and it is accompanied by the myelopathy. For a quite long period, the use of tricortical auto graft was the gold standard of the spinal surgery. Further researches, however, showed a fairly high rate of adverse results, that were manifested by lysis of the implanted bone fragment, its fracture, migration, loss of achieved intraoperative correction and, in some cases, aggravation of neurological disorders. The combination of auto graft with a anterior plate partially solved these problems. The next significant milestone in the development of spine surgery is the use as the body replacing system as hollow vertical cylindrical mesh implants. The first clinical experience with the use of meshsystems without additional fixing wasn’t met with significant success because of the extremely high frequency of prolapse of the system in the body of the vertebrae adjacent to the resected ones. The combination of mesh and rigid ventral plate has demonstrated rather high clinical efficiency.
The literature data allows to reveal a significant number of works devoted to the evaluation of the effectiveness of this combination. The authors consider both biomechanical, clinical and radiological aspects. At the same time, the results are extremely variable. A number of researchers demonstrate 100% efficiency and safety of the stabilization method, others  indicate the frequency of unsatisfactory results up to 30%.
Such results dissociation appears to be due to a number of factors
Firstly, until now, there have not been developed sufficiently clear criteria that would allow to evaluate the effectiveness of the surgical intervention. It is known that clinical symptoms often do not correspond to the xray picture. Thus, progressive kyphotic deformation in the postoperative period may not be accompanied by neurological disorders for a long time. At the same time, the effective fusion with preservation of the sagittal contour and optimized distribution of the load on the cervical spine in case of severe trauma may not lead to an obvious regression of neurological disorders. Considering the SK state of the operated segment as a criterion of efficiency of the fusion, which is emphasized in this research, it should be mentioned that the different authors’ interpretation of the results is very ambiguous. Thus, K. Narotam and coauthors, based on a 4year retrospective study, estimate the correction loss up to 4^{0} as an excellent and 5^{0}9^{0} as a good one.^{12} At the same time, a number of authors allow the increase of kyphotic deformation up to 10^{0} in comparison with intraoperative parameters.^{13} In other publications can be found a quite reasonable statements about such loss of correction in traumatic lesions of the cervical spine, it is quite significant local CSF flow and vascular disorders, in addition to the violation of the congruence of the facet joints in combination with the defeat of the ligamentous apparatus of the rear support complex can lead to one or bilateral dislocation, causing enough risk of the vascular lesions compression of neural structures at the level of the operated segment. Secondly, the vast majority of publications devoted to the combined use of mesh and ventral plate evaluate the result of the performed surgery, but not the result of the treatment of a certain pathology. For example, some clinical studies include the patients with traumatic spinal cord injury and patients with compression myelopathy due to degenerative changes of the spine. This approach, obviously, does not allow to carry out the comparative biomechanical analysis of the produced fusion in full objectively. It is known that decompressivefusion surgery performed in patients with isolated traumatic injury of the anterior support cervical spine complex biomechanically has no equivalent to similar surgical manipulation performed in the treatment of cervical myelopathy.
For example, the absence of traumatic injury of ligamentous apparatus of the posterior supporting complex verified with MRA or CT doesn’t give a total assurance of the absence of this pathology and it does not exclude, however, the distension of the ligamentouscapsular apparatus of the concerned spine segment. Results of search in the National Center for Biotechnology Information database using keywords “cervical mesh cage” for the period of last 5 years shows that the vast majority of publications is devoted to the application of the analysed combination in treatment of cervical myelopathy. As for the traumatic injuries treatment, the majority of authors prefer the 360^{0}fixation. Along with this, however, there is some tendency to minimize surgical exposure. Thus, a number of works convincingly demonstrate the effectiveness of isolated anterior fusion even with significant damage to the front and rear support structures of the subaxial section of the cervical spine. This data is fully correlated with our research results. The retrospective analysis demonstrates rather convincingly high clinical efficiency of the described method of surgical treatment under condition of technical adequacy of execution with the subsequent clinically and biomechanically reasoned stages of rehabilitation. This approach, undoubtedly, can reduce both the economic loading and the surgical trauma, reducing the postoperative complications risk and negative iatrogenic effects.
Thirdly, the most important factor is the lack of a unified approach to the surgical operation technique. In fact, considering the use of mesh, there are two different approaches that have an impact on the final results.^{12} A number of surgeons, during the system installation, prefer to use the partial resection of the endplates of the vertebral bodies, which significantly increases the coherence with the implantable structure. However, due to the cortical layer removal, this approach requires the use of endcaps, in order to increase the bearing surface of the implant and prevent the system prolapse into the vertebral body. Another approach is to maximize the preservation of the cortical layer of the endplates, that eliminates the use of additional structural elements. In our research we applied this surgical modification that for a number of reasons was considered as more expedient. Thus, the structure teeth impression in the cortical layer of the endplate and a kind of adaptation in the implantbone system. It creates additional stabilization and prevents dislocation of the structure. The use of endplates inevitably reduces the contact area of the filler of mesh with bone tissue and in some way prevents the bone block formation. Thus, the meshsystem, which is actually a cage for a filler and is designed to consolidate with the bodies of the vertebrae, is that case loses its main advantage and turns into simple spacer. Taking into consideration the fact of true fusion formation, i.e. bone fusion, is the most optimal and most stable outcome of surgery, and the use of end caps is impractical. Besides, a certain role in forming the biomechanical pattern of anterior fusion plays the type of screws for cervical plate fixation. Our retrospective data consists of cases with fixed screws, so the model has the appropriate type of fusion system. Using nonfixed or variable type screws obviously impacts the stability of fixation and can be studied further. Presented data demonstrates the reasons of wide range the final results of the similar surgical interventions, that are given in the literature. The obtained in our study data is partly consistent with some of them. At the same time, it should be mentioned that the concept of the maximum possible preservation of the physiological curvature of the cervical spine formed the basis of this research. It which is unconditionally proved, even when the deviation from the desired SK values do not have visible negative clinical consequences within the analysed observation period.
The data analysis clearly demonstrates the connection between the values of SK achieved during the operation and the values in delayed postoperative period. The intraoperative correction with SK formation in the range of 6,150..3,100 is optimal for preserving the physiological curvature of the operated segment in the longterm postoperative period. The obtained data have both clinical and experimental biomechanical confirmation.
None.
Authors declare that there is no conflict of interest.
©2018 Slynko, et al . This is an open access article distributed under the terms of the Creative Commons Attribution License , which permits unrestricted use, distribution, and build upon your work noncommercially.