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Research on Biomedical Engineering

Print version ISSN 2446-4732On-line version ISSN 2446-4740

Res. Biomed. Eng. vol.31 no.4 Rio de Janeiro Oct./Dec. 2015  Epub Nov 27, 2015

http://dx.doi.org/10.1590/2446-4740.0637 

Original Articles

A bilinear elastic constitutive model applied for midpalatal suture behavior during rapid maxillary expansion

Larissa Carvalho Trojan Serpe1  * 

Estevam Barbosa de Las Casas1 

Ana Cláudia Moreira Melo Toyofuku1 

Libardo Andrés González-Torres1 

1Grupo de Engenharia Biomecânica, Escola de Engenharia, Universidade Federal de Minas Gerais – UFMG, Av. Antônio Carlos, 6627, Sala 4502, CEP 31270-901, Belo Horizonte, MG, Brasil.

ABSTRACT

Introduction : This study aims to evaluate the influence of the biomechanical behavior of the midpalatal suture (MPS) during the rapid maxillary expansion (RME) when modeled by the Finite Element Method.

Methods

Four simulation alternatives are discussed and, for each analysis, the suture is considered as a functional unit with a different mechanical behavior: (i) without MPS elements, (ii) MPS with Young's modulus (E) equal to 1 MPa, (ii) MPS with E equal to 0.01 MPa and (iv) MPS with bilinear elastic behavior.

Results

The stress analysis showed that, when MPS is not considered in the model, stress peaks are reduced in magnitude and their distribution is restricted to a smaller area when compared to the model with the inclusion of MPS (E=1 MPa). The increased suture stiffness also has a direct influence on MPS displacements after 30 expander activations.

Conclusion

The consideration of the MPS in RME computer models influences greatly the calculated displacements between the suture bone ends, even as the stress levels in maxillary structures. Furthermore, as proposed for the described model, the elastic bilinear behavior assigned to MPS allows coherent prediction of stresses and displacements results, being a good representation for this suture overall behavior.

Keywords:  Midpalatal suture; Biomechanics; Finite element analysis; Rapid maxillary expansion

Introduction

Biomechanical studies using the Finite Element Method (FEM) are common in Orthodontics (Holberg and Rudzki-Janson, 2006; Provatidis et al., 2008; Serpe et al., 2014; Wang et al., 2012). Recent computational studies have evaluated stresses and displacements generated in the craniofacial complex due to rapid maxillary expansion (RME). This therapeutic technique basically consists of separating the bone ends of the suture (MPS) using a palatal expander – a device attached to the posterior teeth and supported or not on palatal mucosa.

According to clinical data, a total displacement of 7 mm applied by an expansion screw in 8 to 14 years old patient results in a 2.54 mm increase in the distance between the central incisor crowns, 36% of the expansion screw opening (Ballanti et al., 2010). In another study with patients of the same age span (Weissheimer et al., 2011), the authors noted a “V” shaped suture expansion after RME, with the anterior maxillary wide basis, representing around 50% (32.7-54.7%) of the applied displacement by the expansion device (8 mm) in the anterior region and 36% (27.2-39.2%) in the posterior region. The percentage of the total applied displacement that effectively is transferred to the MPS is one parameter used to access the effectiveness of the proposed procedure.

Biomechanical studies (Gautam et al., 2007; Iseri et al., 1998; Jafari et al., 2003; Lee et al., 2009; Provatidis et al., 2008) attempted to improve the understanding of this phenomenon and to evaluate how this orthodontic therapy affects other regions of the skull. But most of them considered only linear elastic constitutive model for the analysis, which potentially can result in a model that provides an improved representation of the expansion process. Iseri et al. (1998) used a tridimensional (3D) model of the skull with thick shell elements and considered all materials as linear elastic. Simulating RME, an expansion of 5 mm was applied on each half of the expander (overall 10 mm) and, as a result, a greater displacement in dentoalveolar area was obtained, which gradually diminished in upper structures as nasal cavity. High von Mises stress levels were observed in the jaw bone regions near the canines and molars (184.62 and 56.11 MPa, respectively), in the lateral wall of the inferior nasal cavity, in the nasal and the zygomatic bone. The highest stress peak was in the pterygoid plates of the sphenoid bone, near the skull basis (723 MPa). Using the same material properties and 10 mm of expansion, Jafari et al. (2003) observed the following results: 5.31 mm of maximum lateral displacement in the region of central incisors; 1.08 mm of maximum displacement for anterior bone region, located in the anterior edge of the nasal septum. The nasal bone, nasomaxillary suture, nasofrontal suture and anterior border of the frontal process of the zygomatic bone experienced von Mises stresses up to 321 MPa. In the frontal, parietal, temporal and occipital bones the stress levels were between 0 to 40 MPa.

Gautam et al. (2007) also evaluated the stress distribution along the facial sutures with finite element analysis using tetrahedral solid elements with the aim to improve accuracy when compared with shell elements. Maximum von Mises stress were found along the frontomaxillary, nasomaxillary, and frontonasal sutures, followed by zygomaticotemporal and zygomaticosphenoid sutures. Tensile and compressive strains were observed along the same suture, as is the case for zygomaticotemporal, zygomaticofrontal and zygomaticomaxillary sutures.

Isaacson and Ingram (1964) observed in a clinical study a phenomenon of stress relaxation that occurs in the craniofacial complex between successive activations of the expander screw, as seen in Figure 1. Also considering this phenomenon, and based on data obtained from a Finite Element (FE) study that compared displacement and stress distribution for different models, Provatidis et al. (2007), showed that the most accurate model for the study of RME treatment must contain all skull, complete maxillary dentition, including MPS and consider the phenomenon of stress relaxation that occurs between two successive screw activations.

Figure 1 Results of force measurement for each expander activation according to Isaacson and Ingram (1964)

In a subsequent study, Provatidis et al. (2008) compared the effects of different ossification degrees of the MPS on the craniofacial complex. The model closer to the clinical reality considered all the circummaxillary sutures completely ossified (with Young’s modulus equal to the bone) and the palatine and transverse sutures unossified (E = 1 MPa, as proposed by Verrue et al. (2001)). It was found that the lacrimomaxillary, frontomaxillary nasomaxillary, transverse palatal sutures, as well as the suture between the maxilla and the pterygoid process of the sphenoid bone do not influence the result at the RME, while zygomaticomaxillary suture has an influence on its response. Furthermore, the maximum displacement was observed in the region below the hard palate from the central incisors to second premolar, which was dissipated in the frontal and parietal bone. In the occipital bone the displacement was zero.

According to a literature review study by Romanyk et al. (2013), the most common ways to represent the MPS in computer models were either to assume it as an empty space or as a material with the same elastic properties as the cortical bone (E = 13700 MPa) or to use elastic properties similar to those of soft tissues (E = 1 MPa). All studies in this review accepted linear elastic properties for MPS. Lee et al. (2009), comparing three FE models (maxilla without a midpalatal suture, maxilla with suture elements and maxilla without suture elements), suggested that different states of MPS may partly explain the differences in clinical studies of RME.

Considering the findings of previous works and aiming to reach more reliable results than linear elastic models, the present study intends to describe the stress distribution and displacements generated in maxillary complex by tooth-supported palatal expander considering the bilinear elastic behavior of the MPS using FE analysis. It also evaluates the influence of the constitutive model used to model the suture for computational models of the RME technique.

Methods

For computational simulations, a three-dimensional model (Figure 2) consisting of the maxillary bones and the bones closely related to them was developed. The model was based on Cone Beam Computed Tomography (CT) images of a 12 years old patient and this study has been approved by the Research Ethics Committee of UFMG, Brazil (nº 171.147). The images generated by the CT in DICOM format were imported into the computer aided design software (CAD), Simpleware®. For three-dimensional reconstruction, 218 cross sections, 285 sagittal and 231 coronal sections were used, with 0.45 mm spacing between them. Segmentation was done according to the tissues contrast, initially divided into bone, tooth and dental pulp elements. The bone was not separated between trabecular and cortical bone. After processing these sections, the generated 3D model was exported in STL format to Rapidform® XOR3, software used for solid faces parameterization. The model was then exported in IGES format for SolidWorks® 12, another CAD software, to refine the geometry. Considering the model symmetric, it was half-sectioned to reduce the complexity and the number of nodes of the FE model.

Figure 2 Complete 3D model with palatal expander fixed to posterior teeth (in light gray: bone; dark gray: palatal expander/steel; beige: teeth; brown: functional unit of midpalatal suture). 

The structures that compose the model were considered as isotropic linear elastic, given the limitations in representing the bone biomechanical behavior, and as an initial study of the skull stresses. The real mechanical behavior of the tissues is time dependent, and this characteristic should be further studied to develop a more realistic material model where stress relaxation effects can be considered. The considered mechanical properties, Young's modulus (E) and Poisson's ratio, were as follows: Bone, 10000 MPa and 0.3 (Serpe et al., 2014); Teeth, 20000 MPa and 0.3 (Tanne et al., 1989); Periodontal Ligament, 0.69 MPa and 0.49 (Yoshida et al., 2001); Expander/Steel 200000 MPa and 0.33 (Hibbeler, 2002), respectively. The Young's modulus assigned to the bone (10000 MPa) was estimated in terms of the proportion of cortical bone (13700 MPa) and trabecular bone (1370 MPa) present in the cranium (Serpe et al., 2014), since the model used was composed of a single type of bone tissue aiming to reduce the number of mesh nodes. The consideration of the bone as a homogeneous material is based on an homogenization with the purpose to reduce the computational cost of the analysis, considering that the main focus of the model was to examine the effect of different assumptions for the MPS. For each analysis, the functional unit representing the suture was considered with different mechanical behaviors to evaluate how it influences the results of the simulations. Model (i) represented the maxilla without MPS (MPS unit was removed) while for the remaining models the MPS had different constitutive properties. In models (ii) and (iii), MPS was considered linear elastic, with E equal to 1 MPa and 0.01 MPa, respectively, and Poisson's ratio of 0.49. In addition to these hypotheses, the suture unit was considered to have a bilinear elastic behavior for Model (iv), (E initial = 1 MPa, threshold stress (transition) at 0.1 MPa and E final = 0.01 MPa).

The bilinear model was used to provide a more realistic representation. This model represents the difference in suture stiffness before and after its breakup/separation. The initial elastic modulus (1 MPa) represented the organized connective tissue behavior, which is its main suture component (Provatidis et al., 2007). After its partial failure, the MPS has lower expansion restriction. Preliminary FE analyses were done switching the threshold stress value between 0.5, 0.1 and 0.05 MPa. Based on preliminary FE displacement results and analyzing the parameters to adjust the bilinear model simulations to clinical results (Ballanti et al., 2010; Weissheimer et al., 2011), a stress value of 0.1 MPa was assigned as the threshold for changing the elastic modulus. This represents the stress level at which the disorganization of the MPS functional unit occurs. After reaching this limiting value, the elastic modulus is reduced (E final = 0.01 MPa) to represent an unorganized connective tissue. All these assumptions were made to represent the MPS opening as observed in clinical studies found in the literature (Ballanti et al., 2010; Weissheimer et al., 2011).

The mesh was generated using ANSYS® 14.5 and resulted in a model with 462,916 tetrahedral elements and 749,935 nodes. The boundary conditions were applied in the same region where the symmetry was used to restrict lateral movement (Figure 3). In the posterior region of temporal bone, total or partial movement restrictions were applied, to represent the constraints imposed by the skull base. This assumption was done considering that skull bones have displacements limited by the anterior cranial base structures. As in the present work the model is not represented by the full skull, some areas were restrained based in the displacement results obtained by clinical studies (Ballanti et al., 2010; Weissheimer et al., 2011). A partial displacement restriction (yellow areas in Figure 3, marked as “B”, “C” and “E”) was applied to only Y-axis. All the constraints were imposed only in the posterior region of the model (“D” area in Figure 3), as far as possible from the face, in order not to influence the stress distribution/results in the anterior region of the skull (face).

Figure 3 Finite element model with mesh (left) and the boundary conditions applied in the model (right). The areas were divided in A: region where the displacement related to the rapid maxillary expansion was applied; B, C and E: regions with partial restriction of movement; D: total motion restriction. 

The medial face of the expander unit was chosen to apply the displacement on the horizontal axis (X axis), as performed by the expander screw (“A” area in Figure 3), and also to restrict the displacement in the vertical and anteroposterior axes, as required by the whole appliance structure. The offsets applied in the simulations were 0.125 mm to one side (overall 0.25 mm – an activation of the unit) and 3.75 mm, simulating the average total displacement in RME (overall 7.5 mm – 30 activations).

The simulations were performed on the left half of the model considering its symmetry and the results mirrored for visualization.

Results

For all results of tensile and compressive stresses occurring at the bone, the detected maximum (peak) values, shown in the color charts on the following figures, are located in regions where the boundary conditions were applied (posterior region of the model, Figure 3). As it is not a region of interest for this study, these points were not indicated on the following images.

To evaluate the influence of MPS on stress distribution in the initial stages of RME, models (i) and (ii) were simulated with only one palatal expander activation (0.125 mm). As these first models considered the assumption of linear elastic behavior for the MPS, common in the literature (Romanyk et al., 2013), which is a great simplification considering the relaxation present in connective tissues, this analysis aimed to reduce the simulation error, especially for large applied displacements. The results showed that, when MPS was removed from the model (i), the peak of maximum principal stresses was in the range of 1 MPa, close to the orbit and the lingual surface of the alveolar bone, near the first molar (Figure 4). When MPS was considered (Model (ii)), a region of maximum stresses in alveolar bone was observed at buccal and lingual sides close to the teeth used as support, at the beginning of the zygomatic process of the maxilla, nasal floor and internal walls of the nasal cavity, resulting in peaks from 1.5 to 2 MPa.

Figure 4 Distribution of maximum and minimum principal stresses for Model (i) (without suture) and (ii) (with midpalatal suture, E = 1 Mpa). 

Regarding minimum principal stresses, there was also difference between models with and without MPS. With the presence of the suture, stress peaks were located in the medial wall of the orbit increased, ranging from 1.5 to 2 MPa (Figure 4).

Dental elements used as support were also evaluated mechanically. For a single screw activation of the tooth-supported expander, results showed tensile stress peak of 10 MPa in the middle third of the first molar palatal root and –11 MPa compressive stress peak near the fulcrum region between the first molar roots (Figure 5). The reaction force found when applied one activation on expansor’ medial surface was 25 N.

Figure 5 Maximum and minimum principal stresses distribution in the dental elements when applied one activation on tooth-supported expander (Model (ii)). 

To assess the stresses generated by the entire displacement applied by the expander (3.75 mm on each side, overall 30 activations), when the MPS has a lower expansion restriction after its partial failure, a bilinear elastic model was adopted (Model (iv)). The results showed that the maximum principal stress is distributed throughout the orbit (in the anterior and inferior border), canine fossa of malar surface, buccal face of alveolar bone (close to first molar and first premolar), palatal side of the alveolar bone, lateral wall of the nasal cavity, nasal bone and extended along the superior medial orbital wall with peaks of 50.5 MPa. The nasal floor experienced tensile stresses along its length with peaks up to 22.5 MPa. For minimum principal stress, also shown in Figure 6, peaks up to –56.5 MPa were observed in the lower region of the medial orbital wall. In the canine fossa region of the maxillary bone and extending to the zygomatic arch, peak stresses reached –26 MPa. At the nasal floor and the palatal area, results showed compressive stresses in median regions with values ​​between –8.5 and –11 MPa.

Figure 6 Maximum and minimum principal stresses distribution when total displacement is applied by tooth-supported expander appliance (Bilinear model for midpalatal suture - Model (iv)). 

When the bilinear behavior for MPS was considered, there was a significant increase in processing time. An Intel (R) X5670 computer, with 2 GHz processor and RAM of 24 GB required approximately 144 hours to complete the simulation, a high operational cost when compared to the linear model, which required an average of 5 minutes of processing time.

The expander showed a large dental effect due to RME. This can be observed in Table 1, which compares the displacement predicted in MPS (desirable skeletal effect of RME) with the one predicted for the tooth occlusal surface. The ratio between the MPS opening and displacement of dental crown is close to 1:3, at premolar and molar regions.

Table 1 Displacement results predicted for midpalatal suture (MPS) and dental crown areas with bilinear model for MPS. 

MPS region Displacement
(% of the total applied)
Anterior 26.3
Premolar 18.7
Molar 18.1
Posterior 14.3
Tooth displacement
Anterior/incisive 29.2
Premolar 50.9
Molar 49.8

Models (i) and (iii), without and with (E = 0.01MPa) MPS elements respectively, were also simulated when subjected to the total displacement. The simulation resulted in displacement between bone ends of MPS and it was compared to the bilinear model in Table 2.

Table 2 Predicted displacement results to midpalatal suture (MPS) for different mechanical behavior (% of the total displacement applied by the expander). 

MPS region Bilinear MPS 0.01 MPa MPS MPS absent
Anterior 26.3 40.8 45.3
Premolar 18.7 28.4 31.5
Molar 18.1 26.1 27.1
Posterior 14.3 18.9 21.9

The higher rigidity of the suture, in the initial region of the bilinear model, reduces the total amount of the suture opening, when compared to cases where only the elastic modulus suggesting disorganized tissue was considered (E = 0.01 MPa). This was also the case when comparing the results with the ones obtained from the model without MPS elements. It was observed that the presence and stiffness of the sutures quantitatively influence the removal of the MPS bone ends, as well as the considered mechanical behavior.

Discussion

The influence of MPS in the FE model was assessed by comparing the stress distribution results, in the presence or absence of MPS elements and also in relation to the mechanical behavior assigned to it. The results obtained from this computational study show that an adequate MPS constitutive model is necessary to analyze RME by FEM, which is in accordance with other studies that suggested a significant influence of MPS on the stresses and strains of adjacent structures (Provatidis et al., 2008; Romanyk et al., 2013).

When the MPS elements were suppressed – simulating surgically sectioned suture –, the stress values were considerably lower (Figure 4). But only when the goal is to simulate the RME assisted surgically, a model without the MPS elements can realistically represent the clinical situation. For the remaining situations it would be required, ideally, carrying out mechanical tests for the determination of a reliable constitutive model. However, in the absence of this ideal constitutive model that should consider the viscoelastoplastic behavior for MPS and damage, a bilinear behavior was proposed in this study.

The bilinear behavior is represented in a constitutive model that has a threshold stress value after which the elastic modulus changes. In this case, when this value is achieved, the elastic modulus for the MPS decreases radically, representing the stress level on MPS before partial rupture. The threshold stress value was estimated by a fitting obtained after repeated FE simulations. For this preliminary tests, it was assigned between 0.5, 0.1 and 0.05 MPa to threshold and the value of 0.1 MPa was chosen as it led to the predicted displacements results for the MPS bone ends (Table 2) found in clinical studies (Ballanti et al., 2010; Weissheimer et al., 2011).

According to some clinical studies, the suture opening depends on the skeletal maturation and usually occurs in a “V” shape, with the fulcrum in the posterior region (Bishara and Staley, 1987; Weissheimer et al., 2011). The displacements variations found in clinical studies were in the range of 32% to 45% in the palatal anterior region and 12 to 32% in the palatal posterior region (Ballanti et al., 2010; Weissheimer et al., 2011) and this displacement was used as a parameter to validate the computational models.

The removal of the suture, related to the total displacement applied, varied according to the behavior assumed for MPS (bilinear, linear and absent). The large variation in the displacements observed when changing tissue behavior from linear to bilinear agrees with the statement that different mechanical behaviors of the suture are related to the differences in clinical RME outcomes, as suggested by Lee et al. (2009). This assumption could be extrapolated to clinical results and propose that different ossification stages and imbrications levels of the MPS, that affects the stiffness of the suture, may partly explain the variability of the measures for palatal opening in clinical RME studies.

All models in the present study predicted the “V” shaped opening of MPS (Table 2) but the bilinear model showed smaller displacement than the other cases, probably because this model considers the change in stiffness that occurs in MPS after its rupture. The difference observed on results enlightens the effect of the simplification considered when linear elastic properties were applied for MPS. This fact was sustained also by the stress predicted for the FE models, as biomechanical studies (Gautam et al., 2007; Jafari et al., 2003) that point out to high stresses in various skull bones.

The peak of von Mises stresses up to 321 MPa were observed for nasal bone, nasomaxillary suture, nasofrontal suture, anterior border of frontal process of the zygomatic bone (Jafari et al., 2003). Gautam et al. (2007) obtained von Mises stresses up to 459 MPa in frontomaxillary, nasomaxillary, and frontonasal sutures. However, these results do not represent quantitative reliability due to model simplifications, such as the use of shell element discrete model requiring a simplified geometry (Jafari et al., 2003) and absence of periodontal ligament and linear elastic properties for sutures and bone. As previously mentioned, the bone partially relaxes between expander activations, which makes it difficult to compare the values generated by the sum of displacements directly applied in a model with linear elastic material behavior.

Despite of displacements, the bilinear model showed considerable lower stress peaks on skull bone. To simulate the complete expansion promoted by RME, the bilinear model could generates more acceptable results for predicted MPS removal bone ends and the maximum principal stresses predicted was close to 50 MPa distributed throughout the orbit, canine fossa, alveolar bone (close to, nasal cavity and nasal bone (Figure 5). This model also kept a distribution pattern similar to other studies in the literature (Jafari et al., 2003; Provatidis et al., 2008), reasserting that forces applied by the expander devices are not only restricted to the intermaxillary suture.

The maxillary complex behavior during RME was describe by Isaacson and Ingram (1964) when a gauge was adapt in the palatal expander and showed that forces produced by the expander are not cumulative, it reduced significantly between activations and remain throughout treatment within the range of 9 N and 45 N (Figure 1). This result suggests that the maxillofacial complex absorbs the displacement imposed by palatal expander between activations and the linear model could not be a good option for FEM. Aiming to obtain stress values consistent with the limitations of the linear model, only the efforts of first expander activation was predicted when this constitutive behavior have been applied (Model (ii)). However the linear model showed a distribution pattern of maximum stresses similar to other studies in the literature (Jafari et al., 2003; Provatidis et al., 2008), such as nasal bone, zygomatic arch and nasomaxillary suture, but did not exceed 6 MPa for these regions (Figure 4) when only one activation was applied. This value could be more reliable considering the non-accumulative stress by MPS.

Assuming the force range assessed on palatal expander (Isaacson and Ingram, 1964) and as one more FEM validation, the reaction force of bilinear model (Model (iv)) was requested. The value predicted on the expander appliance for one activation was 25 N, it belongs to clinical range of force evaluated in the palatal expander. Finally, a good representation of the cases studied was obtained, even though the used model did not contain a complete representation of the skull.

Considering the limitation from FE analysis, the obtained results proved that the simplification of complex behavior of some materials has an important influence on stress analysis. In addition, some final remarks can be made:

    1. The presence and stiffness of the sutures influence the displacement between the MPS bone ends and the stress provided computationally in maxillary structures;

    2. The high level of stresses promoted over deeper craniofacial skeleton structures demonstrates that expander devices effects are not only restricted to the intermaxillary suture, but also distributed in other sutures of the nasomaxillary complex, and showed the role of the entire circummaxillary complex in the RME;

    3. For this FEM, the elastic bilinear behavior assigned to MPS allows coherent predicted stress and displacement results similar to available clinical data.

Considering the predicted results for MPS with bilinear properties were more consisted than linear model and it has less computational time than viscoelastic model, the bilinear model should be a good option to represent the MPS on FEM for rapid maxillary expansion.

Acknowledgements

The authors acknowledge the support of the Brazilian research funding agencies CAPES and FAPEMIG and also the Renato Archer Information Technology Center (CTI) in Campinas, Brazil, for assisting in the model generation.

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Received: August 10, 2014; Accepted: October 19, 2015

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