Finite element analysis of occlusal splint therapy in patients with bruxism
Seifollah Gholampour, Hanie Gholampour, and Hamed Khanmohammadi
Abstract
Background
Bruxism is among the habits considered generally as contributory factors for temporomandibular joint (TMJ) disorders and its etiology is still controversial.
Methods
Three-dimensional models of maxilla and mandible and teeth of 37 patients and 36 control subjects were created using in-vivo image data. The maximum values of stress and deformation were calculated in 21 patients six months after using a splint and compared with those in the initial conditions.
Results
The maximum stresses in the jaw bone and head of mandible were respectively 4.4 and 4.1 times higher in patients than in control subjects. Similar values for deformation were 5.8 and 4.9, respectively. The maximum stress in the jaw bone and head of mandible decreased six months after splint application by up to 71.0 and 72.8%, respectively. Similar values for the maximum deformation were 80.7 and 78.7%, respectively. Following the occlusal splint therapy, the approximation of maximum deformation to the relevant values in control subjects was about 2.6 times the approximation of maximum stress to the relevant values in control subjects. The maximum stress and maximum deformation occurred in all cases in the head of the mandible and the splint had the highest effectiveness in jaw bone adjacent to the molar teeth.
Conclusions
Splint acts as a stress relaxer and dissipates the extra stresses generated as well as the TMJ deformation and deviations due to bruxism. The splint also makes the bilateral and simultaneous loading possible and helps with the treatment of this disorder through regulation of bruxism by creating a biomechanical equilibrium between the physiological loading and the generated stress.
Keywords: Occlusal splint therapy, Bruxism, Stress, Deformation, Temporomandibular joint (TMJ), Finite element method (FEM)
Background
In adults, the prevalence of temporomandibular disorders is 25-50% and, in particular, the prevalence of bruxism is 8-31.4% [1, 2]. In general, habits such as bruxism are contributory factors for temporomandibular joint (TMJ) disorders. From a biomechanical point of view, TMJ is the most complex joint in the human body. More than 2000 neuromuscular control signals are registered daily for normal performance of this joint [3]. The consequences of bruxism are revealed mostly in form of wear and damage and are more prevalent in men than women [4]. Bruxism not only leads to wear, grinding, crushing, fracture and ultimately serious damages to teeth but also may cause hearing loss, maxillofacial problems and even facial deformation [5]. If bruxism is not treated, the teeth, bones and gum may be worn or fractured due to wear pressure [6]. Since bruxism is the most important risk factor for TMJ [7], the study of suitable strategies for treating this disorder is of great importance.
Previous studies related to the subject of this research can be divided into two main groups. The first group of studies has examined merely the changes in the biomechanical parameters in TMJ and mandible. Tanaka et al. examined the effect of age on the manner of changes in the parameters affecting the TMJ disc displacement [8]. Hirose et al. investigated the destructive effects of prolonged jaw and teeth pressing on TMJ disc using finite element method (FEM) [9]. Donzelli et al. examined the kinematic and geometric changes in TMJ discs using FE analysis [10]. Koolstra et al. showed with the help of FEM that the articular disk has the ability to distribute loads in a wide area [11]. In a biomechanical study, Naeije et al. investigated the loads exerted on TMJ during chewing and chopping [12]. Del Palomar et al. examined with the help of FEM the effective biomechanical parameters in lateral excursions of the mandible during chewing [13]. Commisso et al. examined the effect of pterygoid muscles on movement of the jaw during mastication using FE analysis [14]. Nishigawa et al. measured the maximum bite force in patients with sleep associated bruxism experimentally, however, they did not deal with the change of bite force during or after treatment [15]. Some studies focused solely on biomechanical parameters affecting implant insertion and filling teeth and dental pain [16–19].
The second group of studies has focused on the assessment of treatments of TMJ disorders. Ferreira et al. showed how the occlusal splint distributes stress in TMJ disc [20]. Salmi et al. found a new digital process to produce occlusal splints in a study using a laser scanner and evaluated the effectiveness of this new production method [21]. Kobayashi et al. examined the association between masticatory performance and bite force in children with bruxism [22].
The results of previous studies have shown that occlusal splint therapy can be an option for treatment of patients suffering from bruxism [22–24]. These studies showed that biomechanical factors such as stress are associated with bruxism, however the exact contribution of these parameters is still unknown [22]. Therefore, it was tried in this research to perform a study with the aim of quantitative assessment of the effectiveness of occlusal splint for treating bruxism using in vivo image data of patients and control subjects. The manner of changes in biomechanical parameters affecting this disease, such as stress and deformation, after occlusal splint therapy was also examined in the present study in order to gain more insight into the detail performance mechanism of this therapy.
Methods
A total number of 37 volunteers were selected from the 420 patients who had been referred to the North Tehran Dental Hospital during 23 months. The patients included 19 women and 18 men aged between 21-49 years old and with a body mass index between 18. 2-21.9 kg.m− 2. 5.5% of male and 10.5% of female patients had in up to 3 teeth a history of tooth caries and tooth fracture which did not result from jaw or mouth injury and were treated previously and did not pose a particular problem during the study. Further, 55.5% of male and 52.6% of female patients had a history of dental filling in up to 2 teeth. All patients were evaluated first using a questionnaire in order to identify the main complaint, pain history and bruxism [25, 26]. It should be noted that this research was approved by the Ethics Committee of the North Tehran Branch of the Islamic Azad University (No. 18245/86–2) in accordance with the 1964 Helsinki declaration. In this study, all participants provided informed consent according to the ethical standard. An equally standardized diagnostic protocol was applied by a professional dentist for all patients before and after the occlusal splint therapy. This diagnostic protocol included an interview and a systematic evaluation of dental, cranial, facial, cervical and other oral structures [25, 26]. No craniofacial surgery, no use of any medication and no reported systemic disease were the initial inclusion criteria. Selection of patients with sleep bruxism was done based on the criteria of American Academy of Sleep Medicine as follows [27]:
A. Occurrence of tooth grinding at least 3 nights per weeks for 6 months, as confirmed by a sleep partner; B. clinical presence of tooth wear; C. hypertrophy of masseter muscle; and D. occurrence of fatigue or tenderness of jaw muscle in the morning.
From the Subjects referred to the North Tehran Dental Hospital, 36 volunteers included 18 women and 18 men aged between 26-52 years old and with a body mass index of 19. 6-22.3 kg.m− 2, who had no history of disease or symptoms associated with bruxism or TMJ disorders, were selected as control subjects. They were completely healthy with regard to bruxism or TMJ disorders, but had toothache from a cracked or attritioned tooth (22.2% of males and 16.6% of females), tooth fracture and tooth caries in up to 4 teeth (27.8% males and 38.8% female). 66.7% of males and 77.8% of females from the control subjects needed a dental implant for up to 4 teeth. During the diagnosis and treatment process, CT scans were done based on the specialist’s diagnosis. Also 61.1% of males and 55.5% of females from the control subjects had a history of dental filling in up to 3 teeth. It should be noted that the control subjects underwent all stages of diagnosing process and informing about this study the same as the patients, and provided informed consent as well.
Cone-beam CT (CBCT) scanning was used for preparing images due to its low costs, unique accessibility and low effective radiation dose. A Newtom VG system (QR, Verona Italy) was used for CBTC scan setting. The scan setting included: 3.6 mAs and 90 KV with radiation time of 15 s and field of view of 20 × 19 in.. Furthermore, the subjects were in standing position during scanning and their head was in natural head position. Patients were asked not to swallow or breathe during imaging. The voxel size and slice thickness were 0.3 × 0.3 × 0.3 mm. and 0.3 mm, respectively. It should be noted that for all patients and control subjects, the jaw was in the maximum intercuspation position during imaging.
The CT scan images of the subjects’ jaw and teeth of were used and the DICOM files of these images were imported into Mimics software version 13.1 (Materialise, Leuven, Belgium) for producing the point clouds of the maxilla, mandible and teeth of each subject as separate parts (Fig. 1a). In Mimics, the bony parts of the maxilla, mandible and teeth in image file were kept. After modifying the areas containing soft tissue in all image slices and repeating these modifications layer by layer, the spaces between layers were finally modified and differentiated and the point clouds of the teeth and jaw bone were extracted as the software output. Subsequently, the point clouds were transferred to the CATIA software version 5R21 (Dassault Systemes, Waltham, Mass., USA), and a three-dimensional model of the maxilla, mandible and teeth was built (Fig. (Fig.11b).
Fig. 1
The point clouds of the maxilla, mandible and teeth. b 3D model. c Meshed model
Three-dimensional models of the maxilla, mandible and teeth of all 37 patients and 36 control subjects were assembled in conditions of no contact pressure with respect to each other. Six months after insertion of the occlusal splint, the process of CT scanning, creating the point cloud, and building the three-dimensional models of jaws, teeth and splint were repeated for patients with the splint in their mouth. At this stage, the 3D models of patients’ splints were constructed from their CT scan images and the 3D splint models were inserted between the patients’ upper and lower teeth. It should be noted that all patients were treated using occlusal splint therapy based on the diagnosis of an experienced dentist. However, sleep hygiene measures combined with relaxation techniques were advised and prescribed for all patients. The material of splints was a hard colorless acrylic resin polymerized using the conventional heat-curing method. It is worth noting that due to personal limitations of the patients, it was only possible to create the 3D model of jaw, teeth and splint of 10 women and 11 men after 6 months of using splint. Since the analyses based on FEM are among the most familiar methods for biological simulation [28–41], the assembled models were transferred finally to ABAQUS software version 6.14 (Dassault Systemes) for FE analysis. Furthermore, for comparing the results of computer simulations in patients and control subjects and also for comparing the results in patients before and after the occlusal splint therapy, three specific anatomical points of the skull of samples were used as set points to synchronize the procedures and to standardize the samples’ head position. The 3D models of the samples were standardized in terms of defining the x, y, and z axis with respect to the same reference in order to ensure the correct loading distribution for comparing the biomechanical parameters of the models with each other.
Table 1 shows the material properties considered for jaw bones, teeth, and splints [20, 42]. One of the most important points in FE analysis is how different parts of the model interact with each other. In this study, these interactions and constraints were defined based on the actual anatomical function of these components in human body. The constraint considered for the contact between the inserted teeth on the upper and lower jaws with splint was a surface-to-surface constraint with a friction coefficient of 0.5 [20]. The degree of freedom of the upper surface of maxilla was considered to be zero at all three directions of x, y and z, i. e., the surface was considered to be fixed. Other degrees of freedom were considered in accordance with the real performance of TMJ, so that the necessary degrees of freedom for opening and closing movements of jaw (rotational degree of freedom) as well as the translation and lateral displacement of jaws over each other (translational degree of freedom) were considered (Fig. 2a). According to a previous study, a first order Ogden hyperelastic model was used for defining the periodontal ligament with a Poisson’s ratio of 0.45 and the material parameter μ = 0.0025 MPa [43]. The average force exerted by the medial pterigoid muscle and masseter muscle for both of the left and right muscles was assumed to be 50 N [20, 42]. It should be noted that, according to previous studies, the force of these muscles should be applied under a particular angle to the model, as shown in Fig. Fig.2a.2a. One of the most important issues in numerical computer simulations is to ensure the mesh convergence of responses [44–48]. The tetrahedral element was used for meshing the models (Fig. (Fig.1c).1c). The results showed that the maximum difference between the stress values in the medium and fine meshes in all three groups of patients, control subjects and patients after using the occlusal splint for 6 months was less than 1.8%. Therefore, the convergence of responses from the grid and time step was ensured (Fig. (Fig.22b).
Table 1
Degree of freedom, interactions and constraints between the parts. b Diagram of the maximum stress in the head of mandible – the number of elements for grid independence study
Fig 2.
Degree of freedom, interactions and constraints between the parts. b Diagram of the maximum stress in the head of mandible – the number of elements for grid independence study
Statistical analyses
The mean value, standard deviation (SD) and coefficient of variation (CV) for maximum stress and maximum deformity were calculated using SPSS version 22 (IBM Corp., Armonk, New York, USA) in all three groups of patients, control subjects and patients after using the occlusal splint for 6 months.
Results
Data validation is one of the most important concerns in computer simulations. Therefore, it is necessary to verify the correctness of the simulation results in order to assure the accuracy of the assumptions and modeling and analysis processes. For data validation, the maximum bite force was measured experimentally in control subjects and patients (before using the splint) and was compared with the similar results calculated in the simulation process. For this goal, a miniature strain-gauge transducer (LM-50- KAM186, Kyowa Electronic Instruments Co., Tokyo, Japan) was mounted on the first molar regions right and left in all subjects and the average value of maximum bite forces was registered after 30 records for each subject and was compared with the similar parameter calculated by FEM simulation. Figure 3 shows that the maximum difference between the computer simulation and experimental results of the maximum bite forces in all patients and control subjects was less than 3.9%. Therefore, the validity of the simulation process is confirmed. Then, the correctness of the statistical analysis of the main results of this study, i.e. the maximum stress and maximum deformation, should be assured for each of the three groups of patients, control subjects and patients after using the splint for 6 months. The results of the statistical analysis showed that the highest amount of CV in all three groups of subjects was less than 3.1% for both maximum stress and maximum deformation (Table 2). The results in Table Table22 showed that SD and CV values were acceptable for all parameters in all three groups of subjects. It should be noted that the reported values for maximum stress and maximum deformation in the rest of the paper are the average values of these parameters for each of the three groups of patients, control subjects and patients after using the splint for 6 months.
Fig. 3
The maximum difference between the computer simulation and the experimental results of the maximum bite forces in control subjects a and patients b
Table 2
Stress and deformation values in jaw bone and head of mandible. SD: standard deviation; CV: coefficient of variation
According to Fig. 4 a and Table Table2,2, the maximum stress in the jaw bone of control subjects and patients was 4.82 and 21.10 MPa, respectively. Results of analysis of patients 6 months after using the splint showed that the maximum stress was 6.12 MPa. The maximum stress produced in the head of mandible of control subjects and patients was 6.91 and 28.26 MPa, respectively. The respective value of this parameter in patients 6 months after using the splint was 7.68 MPa.
Fig. 4
Stress distribution of the jaw bone in a control subject b the manner of changes in deformation values in the upper and lower jaws. c Deformation distribution of the jaw bone in a control subject. d The location of maximum stres
Figure 4, b shows the manner of changes in deformation values. The results showed that the maximum deformation in the jaw bone of control subjects and patients was 63.91× 10-4 and 368.10× 10-4 mm (Fig. (Fig.44 c and Table Table2).2). Similarly, the result for patients six months after using the splint was 71.10× 10-4 mm. The maximum deformation in the head of mandible of control subjects and patients was 9.40× 10-4 mm and 437.20× 10-4 mm, respectively. This value decreased in patients 6 months after using the splint to 93.11× 10-4 mm (Table (Table22).
Discussion
The main objectives of this study were the numerical examination of the manner of changes in effective parameters in occlusal splint therapy during bruxism treatment as well as the assessment of the effectiveness of using occlusal splint for treating this disease. Stress and deformation are the most important biomechanical indices for assessing TMJ disorders and are usually used for quantitative examination of these disorders [14, 49]. However, the bite force, as mentioned earlier, was used for data validation in the present study due to the fact that the experimental measurement of stress and deformation is very difficult [14] and the experimental measurement of the distribution of these parameters in the jaw bone is impossible. Therefore, the bite force parameter, which can be obtained both experimentally and using FEM simulation, was used in this study for data validation. The values of the von Mises stress and deformation in the jaw bone were also calculated using FE method in patients, control subjects and patients 6 months after using the splint in order to assess the disease. The results showed that the maximum stress in the jaw bone of patients was 4.4 times the maximum stress in control subjects. After using the splint, the maximum stress decreased by 71.0% (Table (Table2).2). However, based on the results, the maximum stress in patients after using the splint did not return exactly to the range of maximum stress in control subjects and there was a difference of 26.9% between the values of maximum stress in control subjects and patients after splint treatment. The contact surfaces opposite to the jaw bone are not exactly parallel to it and there are various geometric complexities in this area. Also, with regard to the jaw anatomy, the muscular forces exerted to it are not exactly perpendicular to the surface and are exerted in a particular orientation. Therefore, the von Mises stress calculated by computer simulation presented shear stress, in addition to compressive stress. Consequently, all areas undergoing deformation are not in the same direction and this can also lead to local shear stress. Hence, the lateral walls of the splint can play an effective role in confrontation with these shear stresses and this is an important issue in designing the splint. Regarding the large difference between the elastic modules of the splint material and the jaw bone and the teeth materials (Table (Table1),1), a large contribution to load absorbing and damping can be attributed to the splint due to the softness and flexibility of its material. Therefore, the splint acts as an absorber and dissipater of the generated stress and can help reduce and somehow relax the stress. If this additional loading due to the bruxism is not damped by the splint, a reaction force and consequently an additional reaction stress will be generated in TMJ, which will damage the joints, muscles and ligaments associated with TMJ. Therefore, splint creates a biomechanical equilibrium between the physiological loading and the generated stress through stress relaxation. The imbalance between the input physiological loading and the generated stress can be one of the biomechanical causes of bruxism and the splint can contribute to the neuromuscular reflex and to reduce the stresses on the ligaments and joints associated with the TMJ by helping achieve this balance. As shown in Fig. Fig.44 d, the maximum stress in the total jaw bone is generated in the TMJ and, in particular, in the head of mandible. Its biomechanical cause can be the stress concentration, since the head of mandible, considering the jaw bone anatomy, has the most complex and limited cross sections in the entire mandible. The maximum stress in the head of the mandible in patients was 4.1 times that in control subjects but reduced by 72.8% after using the splint. The difference between this stress and the similar parameter in control subjects was 11.1%. The important point is that 6 months after using the splint, the difference between the maximum stress in the head of the mandible and the other parts of the jaw bone was closer to the similar values in control subjects. This means that the effectiveness of the occlusal splint in patients suffering from bruxism in reducing the stress in the head of mandible is higher than other locations of mandible. It should be noted that the location of generation of the maximum stress after using the splint did not change and the maximum stress always occurred in the head of mandible. The results showed that the highest deformation, like the maximum stress, occurred in the head of the mandible. According to Table Table2,2, the maximum deformation in the jaw bone and head of mandible of patients was, respectively, 5.8 and 4.9 times that in control subjects and decreased by 80.7 and 78.7% six months after using splint. The difference between the maximum deformation in the jaw bone and head of mandible of patients who used splint for six months and control subjects was 11.3 and 4.1%, respectively. The results in Table 3 show that the maximum stress and deformation in all subjects were greater in the lower jaw than in the upper jaw. Similar to the reported results for patient No. 1, the greatest effectiveness of the splint in the jaw bone was related to the areas adjacent to the first, second and third molar teeth in all patients (Table (Table3).3). The results also showed that the stresses in the left and right mandible of patients are not necessarily balanced and uniform. However, due to the flexibility of the splint material, the bilateral and simultaneous loading becomes possible, which can also be useful in the treatment of bruxism.
Table 3
Stress and deformation values in upper and lower teeth of patient No. 1 and patient No. 1 after using splint
It should be noted that the minimal effectiveness of the splint in damping the stress and deformation was related to the canine teeth. The results showed that the occlusal splint therapy was effective in reducing stress and deformation, especially in the head of mandible. It should be noted that following the occlusal splint therapy, the maximum deformation approached almost 2.6 times the maximum stress to the respective value in control subjects. Thus, the effectiveness of splint was higher in reducing deformation than stress. In fact, the design of the occlusal splint therapy is not based on the prevention of bruxism, but the results of this study show that the occlusal splint can help treat this disease by reducing stress and correcting deformations and deviations, especially in the head of mandible, and eventually reducing the additional support reaction due to bruxism in TMJ. It is suggested that the future studies record and compare the stimulation of TMJ-related muscles affecting bruxism before and after using splint by patients, so that the effect of splint on muscle stimulation and bruxism frequency is also examined as the main focus of the present study was on intensity not frequency.
Conclusion
The results showed that the occlusal splint creates a biomechanical equilibrium between the physiological loading and the generated stress through stress relaxation. The splint also provides the possibility for making the asymmetric and non-uniform loading due to bruxism bilateral and simultaneous. Thus, the occlusal splint can lead to regulation of bruxism by reducing stresses, and in particular, by reducing deformations and deviations in TMJ and consequently can help treat this disease. The results of this study can be useful in quantitative evaluation of the changes in stress and deformation before and after treatment of bruxism as well as in development of a biomechanical approach for assessing the effectiveness of occlusal splint therapy.
Acknowledgements
Not applicable.
Abbreviations
CV
coefficient of variation
FEM
finite element method
SD
standard deviation;
TMJ
temporomandibular joint
Authors’ contributions
SG designed the study, collected and analyzed the data. HG and HK wrote the manuscript. SG, HG and HK interpreted of data and provided critical input and revisions. All authors read and approved the final version of the manuscript.
Funding
Not applicable.
Availability of data and materials
All relevant data are within the present paper; however, the ethics committee strictly forbids sharing the CBCT files of patients and control subjects that they contain some identifying information, according to its regulations on the data access. Therefore, CBCT data of the samples will not be shared.
Ethics approval and consent to participate
All procedures performed in studies involving human participants were in accordance with the ethical standards of the North Tehran Branch of the Islamic Azad University, Tehran, Iran, (Ethics committee of biomedical research center, No. 18245/86–2) and with the 1964 Helsinki declaration and its later amendments or comparable ethical standards. Furthermore, this article does not contain any studies performed by any of the authors on animals. It is noteworthy that according to the ethical standards, all patients and control subjects provided verbal informed consent.
Consent for publication
Not Applicable.
Competing interests
The authors declare that they have no competing interests.
Footnotes
Publisher’s Note
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Article information
BMC Oral Health. 2019; 19: 205.
Published online 2019 Sep 4. doi: 10.1186/s12903-019-0897-z
PMCID: PMC6727492
PMID: 31484524
1Department of Biomedical Engineering, North Tehran Branch, Islamic Azad University, Tehran, Iran
2Department of Electrical and Computer Engineering, Science and Research Branch, Islamic Azad University, Tehran, Iran
Seifollah Gholampour, Phone: (+98-21) 77317998, Email: ri.ca.bnt-uai@ruopmalohg.s.
Corresponding author.
Received 2019 May 25; Accepted 2019 Aug 21.
Copyright © The Author(s). 2019
Open AccessThis article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.
Articles from BMC Oral Health are provided here courtesy of BioMed Central
References
1. Manfredini D, Winocur E, Guarda-Nardini L, Paesani D, Lobbezoo F. Epidemiology of bruxism in adults: a systematic review of the literature. J Orofac Pain. 2013;27(2):99–110. doi: 10.11607/jop.921. [PubMed] [CrossRef] [Google Scholar]
2. Kuttila M, Niemi PM, Kuttila S, Alanen P, Le Bell Y. TMD treatment need in relation to age, gender, stress, and diagnostic subgroup. J Orofac Pain. 1998;1(1):12. [PubMed] [Google Scholar]
3. Pizolato RA, Gavião MB, Berretin-Felix G, Sampaio AC, Trindade Junior AS. Maximal bite force in young adults with temporomandibular disorders and bruxism. Braz Oral Res. 2007;21(3):278–283. doi: 10.1590/S1806-83242007000300015. [PubMed] [CrossRef] [Google Scholar]
4. Alkhiary YM, Nassef TM, Yassine IA, Tayel SB, Ezzat AE. A new numerical model to analyze stress distribution of TMJ disc from 2-D MRI scans. Advances Computing. 2012;2(05):66–77. doi: 10.5923/j.ac.20120205.01. [CrossRef] [Google Scholar]
5. Kitsoulis P, Marini A, Iliou K, Galani V, Zimpis A, Kanavaros P, Paraskevas G. Signs and symptoms of temporomandibular joint disorders related to the degree of mouth opening and hearing loss. BMC Ear, Nose and Throat Disorders. 2011;11(1):5. doi: 10.1186/1472-6815-11-5. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
6. Reichardt G, Miyakawa Y, Otsuka T, Sato S. The mandibular response to occlusal relief using a flat guidance splint. Int J Stomatol Occlusion Med. 2013;6(4):134–139. doi: 10.1007/s12548-013-0093-8. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
7. Pereira LJ, Costa RC, França JP, Pereira SM, Castelo PM. Risk indicators for signs and symptoms of temporomandibular dysfunction in children. J Clin Pediatr Dent. 2009;34(1):81–86. doi: 10.17796/jcpd.34.1.l1773mh5pw2745g6. [PubMed] [CrossRef] [Google Scholar]
8. Tanaka E, Hirose M, Yamano E, Dalla-Bona DA, Fujita R, Tanaka M, Van Eijden T, Tanne K. Age-associated changes in viscoelastic properties of the bovine temporomandibular joint disc. Eur J Oral Sci. 2006;114(1):70–73. doi: 10.1111/j.1600-0722.2006.00265.x. [PubMed] [CrossRef] [Google Scholar]
9. Hirose M, Tanaka E, Tanaka M, Fujita R, Kuroda Y, Yamano E, Van Eijden TM, Tanne K. Three-dimensional finite-element model of the human temporomandibular joint disc during prolonged clenching. Eur J Oral Sci. 2006;114(5):441–448. doi: 10.1111/j.1600-0722.2006.00389.x. [PubMed] [CrossRef] [Google Scholar]
10. Donzelli PS, Gallo LM, Spilker RL, Palla S. Biphasic finite element simulation of the TMJ disc from in vivo kinematic and geometric measurements. J Biomech. 2004;37(11):1787–1791. doi: 10.1016/j.jbiomech.2004.01.029. [PubMed] [CrossRef] [Google Scholar]
11. Koolstra JH, Van Eijden TM. Combined finite-element and rigid-body analysis of human jaw joint dynamics. J Biomech. 2005;38(12):2431–2439. doi: 10.1016/j.jbiomech.2004.10.014. [PubMed] [CrossRef] [Google Scholar]
12. Naeije M, Hofman N. Biomechanics of the human temporomandibular joint during chewing. J Dent Res. 2003;82(7):528–531. doi: 10.1177/154405910308200708. [PubMed] [CrossRef] [Google Scholar]
13. Del Palomar AP, Doblaré M. Finite element analysis of the temporomandibular joint during lateral excursions of the mandible. J Biomech. 2006;39(12):2153–2163. doi: 10.1016/j.jbiomech.2005.06.020. [PubMed] [CrossRef] [Google Scholar]
14. Commisso MS, Martínez-Reina J, Ojeda J, Mayo J. Finite element analysis of the human mastication cycle. J Mech Behav Biomed Mater. 2015;41:23–35. doi: 10.1016/j.jmbbm.2014.09.022. [PubMed] [CrossRef] [Google Scholar]
15. Nishigawa K, Bando E, Nakano M. Quantitative study of bite force during sleep associated bruxism. J Oral Rehabil. 2001;28(5):485–491. doi: 10.1046/j.1365-2842.2001.00692.x. [PubMed] [CrossRef] [Google Scholar]
16. Rubo JH, Capello Souza EA. Finite-element analysis of stress on dental implant prosthesis. Clin Implant Dent Relat Res. 2010;12(2):105–113. doi: 10.1111/j.1708-8208.2008.00142.x. [PubMed] [CrossRef] [Google Scholar]
17. Svensson P, Jadidi F, Arima T, BAAD-HANSEN L, Sessle BJ. Relationships between craniofacial pain and bruxism. J Oral Rehabil. 2008;35(7):524–547. doi: 10.1111/j.1365-2842.2008.01852.x. [PubMed] [CrossRef] [Google Scholar]
18. Gholampour S, Jalali A. Thermal analysis of the dentine tubule under hot and cold stimuli using fluid–structure interaction simulation. Biomech Model Mechanobiol. 2018;17(6):1599–1610. doi: 10.1007/s10237-018-1046-3. [PubMed] [CrossRef] [Google Scholar]
19. Gholampour S, Zoorazma G, Shakouri E. Evaluating the effect of dental filling material and filling depth on the strength and deformation of filled teeth. Journal of Dental Materials and Techniques. 2016;5(4):172–180. [Google Scholar]
20. Ferreira FM, Cézar Simamoto-Júnior P, Soares CJ, Ramos AM, Fernandes-Neto AJ. Effect of occlusal splints on the stress distribution on the temporomandibular joint disc. Braz Dent J. 2017;28(3):324–329. doi: 10.1590/0103-6440201601459. [PubMed] [CrossRef] [Google Scholar]
21. Salmi M, Paloheimo KS, Tuomi J, Ingman T, Mäkitie A. A digital process for additive manufacturing of occlusal splints: a clinical pilot study. J R Soc Interface. 2013;10(84):20130203. doi: 10.1098/rsif.2013.0203. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
22. Kobayashi FY, Furlan NF, Barbosa TS, Castelo PM, Gaviao MB. Evaluation of masticatory performance and bite force in children with sleep bruxism. J Oral Rehabil. 2012;39(10):776–784. doi: 10.1111/j.1365-2842.2012.02331.x. [PubMed] [CrossRef] [Google Scholar]
23. Lee HS, Baek HS, Song DS, Kim HC, Kim HG, Kim BJ, Kim MS, Shin SH, Jung SH, Kim CH. Effect of simultaneous therapy of arthrocentesis and occlusal splints on temporomandibular disorders: anterior disc displacement without reduction. J Korean Assoc Oral Maxillofac Surg. 2013;39(1):14–20. doi: 10.5125/jkaoms.2013.39.1.14. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
24. Nitzan DW. Intraarticular pressure in the functioning human temporomandibular joint and its alteration by uniform elevation of the occlusal plane. J Oral Maxillofac Surg. 1994;52(7):671–679. doi: 10.1016/0278-2391(94)90476-6. [PubMed] [CrossRef] [Google Scholar]
25. Winocur E, Uziel N, Lisha T, Goldsmith C, Eli I. Self-reported bruxism-associations with perceived stress, motivation for control, dental anxiety and gagging. J Oral Rehabil. 2011;38(1):3–11. doi: 10.1111/j.1365-2842.2010.02118.x. [PubMed] [CrossRef] [Google Scholar]
26. Lobbezoo F, Ahlberg J, Glaros AG, Kato T, Koyano K, Lavigne GJ, De Leeuw R, Manfredini D, Svensson P, Winocur E. Bruxism defined and graded: an international consensus. J Oral Rehabil. 2013;40(1):2–4. doi: 10.1111/joor.12011. [PubMed] [CrossRef] [Google Scholar]
27. American Academy of Sleep Medicine . International classification of sleep disorders: diagnostic and coding classification of sleep disorders 697 manual. 2. Westchester: American Academy of Sleep Medicine; 2005. [Google Scholar]
28. Gholampour S, Soleimani N, Zalii AR, Seddighi A. Numerical simulation of the cervical spine in a normal subject and a patient with intervertebral cage under various loadings and in various positions. International Clinical Neuroscience Journal. 2016;3(2):92–98. [Google Scholar]
29. Gholampour - S, Hajirayat K, Erfanian A, Zali AR, Shakouri E. Investigating the role of helmet layers in reducing the stress applied during head injury using FEM. International Clinical Neuroscience Journal. 2017;4(1):4–11.
30. Gholampour S, Soleimani N, Karizi FZ, Zalii AR, Masoudian N, Seddighi AS. Biomechanical assessment of cervical spine with artificial disc during axial rotation, flexion and extension. International Clinical Neuroscience Journal. 2016;3(2):113–119. [Google Scholar]
31. Gholampour S, Fatouraee N, Seddighi AS, Yazdani SO. A Hydrodynamical study to propose a numerical index for evaluating the CSF conditions in cerebralventricular system. International Clinical Neuroscience Journal. 2014;1(1):1–9. [Google Scholar]
32. Shakouri E, Haghighi Hassanalideh H, Gholampour S. Experimental investigation of temperature rise in bone drilling with cooling: a comparison between modes of without cooling, internal gas cooling, and external liquid cooling. Proc Inst Mech Eng H J Eng Med. 2018;232(1):45–53. doi: 10.1177/0954411917742944. [PubMed] [CrossRef] [Google Scholar]
33. Hajirayat K, Gholampour S, Seddighi AS, Fatouraee N. Evaluation of blood hemodynamics in patients with cerebral aneurysm. International Clinical Neuroscience Journal. 2016;3(1):44–50. [Google Scholar]
34. Gholampour S, Seddighi A, Fatouraee N. Relationship between spinal fluid and cerebrospinal fluid as an index for assessment of non-communicating hydrocephalus. Modares Mechanical Engineering. 2015;11:14(13). [Google Scholar]
35. Khademi M, Mohammadi Y, Gholampour S, Fatouraee N. The nucleus pulpous of intervertebral disc effect on finite element modeling of spine. International Clinical Neuroscience Journal. 2016;3(3):150–157. [Google Scholar]
36. Gholampour S, Shakouri E, Deh HH. Effect of drilling direction and depth on thermal necrosis during tibia drilling: an in vitro study. Technol Health Care. 2018;26(4):687–697. doi: 10.3233/THC-181246. [PubMed] [CrossRef] [Google Scholar]
37. Vahdat I, TabatabaiGhomsheh F, Gholampour S, Rostami M, Khorramymehr S. Biomechanical evaluation of passive resistive torque structure of elbow joint and its application in rehabilitation and practical equipment. Journal of Modern Rehabilitation. 2015;9(4):16–24. [Google Scholar]
38. Gholampour S, Bahmani M, Shariati A. Comparing the efficiency of two treatment methods of hydrocephalus: shunt implantation and endoscopic third ventriculostomy. Basic and Clinical Neuroscience. 2019;10(3):185–198. [PMC free article] [PubMed] [Google Scholar]
39. Gholampour S, Fatouraee N. The impact of the model boundary conditions on computer simulation of hydrocephalus patients. PLoS One. 2018; [in press].
40. Gholampour S, Hajirayat K. Minimizing thermal damage to vascular nerves while drilling of calcified plaque. BMC research notes. 2019;12(1):338. doi: 10.1186/s13104-019-4381-2. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
41. Gholampour S, Deh HH. The effect of spatial distances between holes and time delays between bone drillings based on examination of heat accumulation and risk of bone thermal necrosis. Biomed Eng Online. 2019;18(1):65. doi: 10.1186/s12938-019-0686-6. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
42. dos Santos MV, Lehmann RB, de Assis Claro CA, Amaral M, Vitti RP, Neves AC, da Silva Concilio LR. Three-dimensional finite element analysis of occlusal splint and implant connection on stress distribution in implant–supported fixed dental prosthesis and peri-implantal bone. Mater Sci Eng C. 2017;80:141–148. doi: 10.1016/j.msec.2017.05.071. [PubMed] [CrossRef] [Google Scholar]
43. Martinez S, Lenz J, Schweizerhof K, Schindler HJ. A Variable Finite Element Model of the Overall Human Masticatory System for Evaluation of Stress Distributions during Biting and Bruxism. In10th European LS-DYNA Conference, Würzburg, Germany 2015.
44. Gholampour S. FSI simulation of CSF hydrodynamic changes in a large population of non-communicating hydrocephalus patients during treatment process with regard to their clinical symptoms. PLoS One. 2018;13(4):e0196216. doi: 10.1371/journal.pone.0196216. [PMC free article] [PubMed] [CrossRef] [Google Scholar]
45. Gholampour S, Taher M. Relationship of morphologic changes in the brain and spinal cord and disease symptoms with cerebrospinal fluid hydrodynamic changes in patients with Chiari malformation type I. World neurosurgery. 2018;12(5):8. [PubMed] [Google Scholar]
46. Hajirayat K, Gholampour S, Sharifi I, Bizari D. Biomechanical simulation to compare the blood hemodynamics and cerebral aneurysm rupture risk in patients with different aneurysm necks. J Appl Mech Tech Phys. 2017;58(6):968–974. doi: 10.1134/S0021894417060025. [CrossRef] [Google Scholar]
47. Gholampour S, Fatouraee N, Seddighi AS, Seddighi A. Numerical simulation of cerebrospinal fluid hydrodynamics in the healing process of hydrocephalus patients. J Appl Mech Tech Phys. 2017;58(3):386–391. doi: 10.1134/S0021894417030026. [CrossRef] [Google Scholar]
48. Gholampour S, Fatouraee N, Seddighi AS, Seddighi A. Evaluating the effect of hydrocephalus cause on the manner of changes in the effective parameters and clinical symptoms of the disease. J Clin Neurosci. 2017;35:50–55. doi: 10.1016/j.jocn.2016.09.012. [PubMed] [CrossRef] [Google Scholar]
49. Chen-Tin L, Chou YR, Chao-Chia W, Chia-Yu W, Keng-Liang O, Han-Yi C. Research of Oral remodeling on mandible with Ameloblast. J Biomed Sci. 2015;1:4(1). [Google Scholar]
Citation
Comentarios