Content uploaded by João Paulo Mendes Tribst
Author content
All content in this area was uploaded by João Paulo Mendes Tribst on Jan 02, 2021
Content may be subject to copyright.
© International Academy of Periodontology
Journal of the International Academy of Periodontology 2021 23/1: 65–71
Correspondence to: João Paulo Mendes Tribst, Department of
Dental Materials and Prosthodontics, São Paulo State University
(Unesp), Institute of Science and Technology, Av. Eng. Francisco
José Longo, n° 777, Jardim São Dimas, 12245-000 São José dos
Campos, SP, Brazil. Email: joao.tribst@gmail.com
Introduction
The primary function of the human dentition is food
preparation and processing through a biomechanical
masticatory process. This process is involves transferring
masticatory forces to the periodontium and this is medi-
ated through the teeth (Versluis and Versluis-Tantbirojn,
2011). The periodontal apparatus (cementum, periodontal
ligament and alveolar bone) plays an important role in sta-
bilizing teeth. The forces produced during mastication are
distributed and absorbed by the alveolar process through
the alveolar bone. In health, the tooth-periodontium
complex, maintains tissue homeostasis when subjected
to physiological forces (Cattaneo et al., 2009).
Reduced Periodontal Support for Lower
Central Incisor – A 3D Finite Element
Analysis of Compressive Stress in the
Periodontium
Milena Cerqueira da Rocha,1 Daniel Maranha da Rocha,1
João Paulo Mendes Tribst,2 Alexandre Luiz Souto Borges2 and
Fabiano Alvim-Pereira1
Abstract
Background: The aim of this study was to assess the stress concentration in simulated
periodontal alveolar bone containing healthy teeth with and without attachment loss.
Methods: Six 3-D models of a lower central incisor were created simulating the teeth struc-
ture, cancellous and cortical bone and periodontal ligament. Each model presented a 1mm
increasing distance between cement-enamel junction (CEJ) and alveolar bone crest (ABC) (1
to 6mm). A 100N, 45-degree load was applied to the buccal face of the lower central incisor.
The effects of Minimum Principal Stress (MPS) on lamina dura (LD) and ABC were analyzed.
Results: The results showed an increase of MPS in the surrounding bone (ABC and LD)
due to periodontal attachment loss. The 6mm attachment loss model showed the highest
(p<0.001) magnitude in MPS. Each millimeter increase in CEJ-ABC distance generated a
12% pattern of attachment loss and an increase at least of 65.7% for ABC and 33.6% for LD.
Conclusion: Under simulated conditions, attachment loss increases stress concentration
in the surrounding bone suggesting a partly explanation regarding bone resorption risk
for teeth with periodontal attachment loss.
Keywords: Periodontium, nite element analysis, bone, incisor
1Departament of Dentistry, Universidade Federal de Sergipe,
SE, Brazil; 2Department of Dental Materials and Prosthodontics,
São Paulo State University (Unesp), Institute of Science and
Technology, Brazil.
Chronic periodontal disease is a major public
health condition that affects more than one third of
the population, 10-15% in its most severe form (Eke
et al., 2012). Chronic periodontitis is the primary cause
of tooth loss in people over age 35 (Deng et al., 2010).
Diminished periodontal support results from the sur-
rounding chronic inammation arising in respons to the
presence of a periodontal pathogenic biolm (Cattaneo
et al., 2009). Even after effective chronic periodontal
disease treatment, a subsequent optimal maintenance
phase, and the advances in bone regeneration therapies,
vertical bone regeneration around tooth is an unsolved
challenge for clinicians (Van Dyke et al., 2015).
Evidence in the literature indicates that previous at-
tachment loss is classied as a risk indicator for recurrent
disease (Takeuchi et al., 2010; Martin et al., 2010; Hirata et
al., 2019). This risk may be explained by the diminished
periodontal support removing the capability of teeth to
withstand physiological chewing forces (Takeuchi et al.,
2010; Martin et al., 2010).
66 Journal of the International Academy of Periodontology (2021) 23/1
Among the methods for stress analysis of complex
structures, nite element method (FEM) is a widely ap-
plied tool for bioengineering studies in dentistry (Dal
Piva et al., 2019; Tribst et al., 2020). Different mechanical
stimuli can impact the balance of bone homeostasis
(Mercuri et al., 2016). The relationship between bone and
mechanical stimuli has been evaluated by FEM analysis
and PET/CT scanning (in vivo) with good correlation
between these two methods (Suenaga et al., 2015).
Three-dimensional nite element analysis has been
used in periodontology to estimate the potential effects
of mechanical stimuli and stress on the periodontal
apparatus (Poiate et al., 2008; Ona and Wakabayashi,
2006; Kondo and Wakabayashi, 2009; Tajima et al., 2009;
Papadopoulou et al., 2013; Wakabayashi et al., 2008).
Therefore, the aim of this study was to use nite ele-
ment analysis to measure and map the stress distribution
of simulated normal and reduced periodontal support.
Materials and Methods
A computational-laboratorial study was conducted using
a three-dimensional human lower central incisor model,
constructed into the BioCAD protocol that consists of
creating virtual geometric models of biological struc-
tures based on anatomical references (Papadopoulou
et al., 2013). A three-dimensional scanned image of a
lower central incisor with 19 mm length (9 mm crown;
10 mm root) was used as the reference for modeling the
structures (Poiate et al., 2009). The complete model was
constituted of cancellous bone, 1.0 mm cortical bone,
0.2 mm periodontal ligament (Wakabayashi et al., 2010)
space and tooth (enamel, dentin and pulp) (Figure 1).
Computer-aided design (CAD) software Rhinoceros
4.0 (McNeel North America) was used to achieve the
3-D model. Six different geometries of periodontal at-
tachment were performed, in order to simulate different
levels of periodontal attachment loss. In each situation
different distances (1 mm; 2 mm; 3 mm; 4 mm; 5 mm
and 6 mm) between the enamel-cement junction (CEJ)
and alveolar bone crest (ABC) were simulated.
The geometric data were imported into Ansys soft-
ware (version 16.0; Ansys, Canonsburg, PA) for static
structural analysis. The mechanical properties of the
tissues mechanical considered were: elastic, homoge-
neous, linear and isotropic. Biomechanical proprieties
of the tissues was based on previously published data
(Table 1) for bone (Moroi et al., 1993), enamel, dentin
and periodontal ligament (Monteiro et al., 2018) and
pulp (Toparli et al., 1999).
Figure 1. Geometric modeling of structures
Material/tissue Young’s Moduli
(GPa) Poisson Ratio
Enamel 84,1 0,30
Dentin 14,7 0,31
Pulp 0,000003 0,45
Periodontal ligament 0,0118 0,45
Cortical bone
(Moroi, 1993) 14,7 0,30
Cancellous bone
(Moroi, 1993) 0,49 0,30
Table 1. Mechanical properties of materials/tissues
simulated
Mesh generation used tetrahedral elements. The
overall mean number of units was 197,908 elements
and 347,271 nodes. The elements had 0.2 mm mean size
and mesh surface convergence applied was 5%. It was
ensured that all contacts were considered fully bonded,
which means that the model was considered solid, with
no gaps between structures.
A simulated 100N and 45-degree angled load applied
at the buccal incisal edge of the lower central incisor.
Nodal restriction was applied at the cortical bone base in
all directions. The Consistency of the results was veried
by total displacement analysis and von Mises criteria.
The stress concentration was analyzed using the
Minimum Principal Stress (MPS) criteria, where positive
values were related to tensile stresses and negative values
to compressive stresses. Data processing performed
was arranged in stress color maps and numeric values.
Mechanical stress was analyzed in the cortical bone
and focused in two critical structures: alveolar bone crest
and lamina dura. Stress variations are presented as a scale
color map, where different colors mean different stress
da Rocha et al.: Periodontal support nite element analysis 67
concentrations. Qualitatively the proximity colors with
red in the scale, indicates higher stress concentration. For
quantitative analyses the numerical values of minimum
principal stress distributed in each structure (alveolar bone
crest and lamina dura) were assessed. The colorimetric
scales were adjustable for a visual comparison between
the groups.
Results
The qualitative analysis (Figure 2) shows a color map
illustrating the MPS distribution among the models.
In the analyses of alveolar bone crest, an increase of
compressive zones could be veried when the cement-
enamel junction (CEJ) to the alveolar crest (ABC) dis-
tances were increased. In the 1 mm model compressive
stress concentration peaks were observed on the lingual
bone crest. With an increase in the CEJ-ABC distance,
an increase in the minimum principal stress was located
mainly on lingual face and in the 5 to 6 mm models some
peaks were noted on the buccal face. For the lamina
dura color map, an increasing CEJ-ABC distance lead
to wider compressive stress concentration areas. In the
1 to 3 mm models, compressive areas were primarily
located to proximal regions (near to fulcrum area). For
4 mm, the location peaks of compressive stress started
to spread to buccal and lingual areas. It is noteworthy
that in all models, the 6 mm situation presented the
broadest areas of compressive stress.
Quantitative analyses were also performed and re-
vealed the same pattern of qualitative data, augmented
values of MPS showed an increased distance for CEJ-
ABC. For each millimeter increase in CEJ-ABC distance,
about 11% of the linear attachment was lost up to a 12%
total attachment area loss (Table 2).
Minimum principal stress distributions, as assessed
by scatter plots for 2D distribution, showed statistical
signicant differences (SSD) among groups for changes
in alveolar bone crest and lamina dura. The compres-
sive stress values were also compared in pairs (1 vs. 2,
2 vs. 3, 3 vs. 4, 4 vs. 5 e 5 vs. 6). Statistical signicant
differences were found for both the alveolar bone crest
and lamina dura (Figure 3). Moreover, it was noted that
with a decrease in periodontal support the intra model
variance of MPS display amplication (Figure 3).
Pearson’s correlation coefcient analyses between
attachment loss and peak of MPS were performed for
ABC and LD. Statistical signicant difference and high
Figure 2 - Color mapping of compression stress in the alveolar bone (a) ABC view, (b) LD occlusal view, (c) LD
proximal view
68 Journal of the International Academy of Periodontology (2021) 23/1
positive correlation (p=0.020; r=0.882) were found for
LD. SSD had a very high positive correlation (p=0.001;
r=0.975) for ABC.
The MPS peak increase in the no attachment loss
model, showed that the peak of compression stress
increased by 65.7% (ABC) and 33.6% (LD) with 11%
of attachment loss (2 mm model), and up to 252.6%
(ABC), 464.6% (LD) and 55.6% of attachment loss (6
mm model) (Figure 4).
Discussion
Horizontal attachment loss is a consequence of peri-
odontitis that remains even with the reestablishment of
periodontal health. Reduced periodontal support does
not seem to limit bite force (Kleinfelder and Ludwigt
2002). Subjects with attachment loss can exert up to
three times higher forces on the teeth. These func-
tions may related to affected sensory function of the
periodontal ligament (Johansson et al., 2006). Different
mechanical stimuli can modulate bone-remodeling
processes (Burger et al., 1999), and alter molecular path-
ways in bone metabolism (Rubin et al., 2006). Excessive
mechanical stress during hyper-occlusion may lead to
alveolar bone destruction during occlusal traumatism
(Tsutsumi et al., 2013). An important gap in knowledge
still remains unanswered whether the masticatory loads
in severe attachment loss can exceed bone adaptive load
bearing capability leading to periodontal tissue damage.
In the present study an overall increase in the mini-
mum principal stress (mainly compressive stress) was
Distance of
CEJ-ACB
Alveolar Crestal Bone Lamina Dura
Number of
nodes
% of linear
attachment lost
Minimum
Principal Stress
(MPa) Number of
nodes
% of
attachment
area lost
Minimum
Principal Stress
(MPa)
Peak Peak
1 mm 178 0,0% -14,76 6176 0,0% -21,64
2 mm 183 11,1% -24,46 5463 12,4% -28,91
3 mm 181 22,2% -25,37 4290 24,7% -33,07
4 mm 175 33,3% -33,86 3601 36,9% -45,99
5 mm 170 44,4% -48,96 3080 48,4% -60,51
6 mm 160 55,6% -52,04 2333 59,3% -122,18
CEJ - Cementum Enamel Junction
ABC - Alveolar Bone Crest
MPS - Minimum Principal Stress
Table 2. Descriptive statistics of compressive stress in ABC and LD in each simulated CEJ-ABC distance
Figure 3. Chart of distribution of Minimal Principal Stress values among groups
da Rocha et al.: Periodontal support nite element analysis 69
demonstrated in the target bone structures (alveolar bone
crest and lamina dura). This result shows that even with
the same force (that simulated bite forces), the tooth
surrounding bone structures were subjected to higher
compressive stress. Cyclic stress may generate cumulative
damage to the bone (Hambli et al., 2016). Therefore, if
a tooth has reduced periodontal support, the cyclic oc-
clusal forces can intensify bone damage. In periodontal
maintenance therapy, reinforcement of oral hygiene and
biolm removal is indicated (Armitage et al., 2016). Also
in this phase, occlusal adjustment has been reported to
improve periodontal health in terms of bacterial prole
and clinical appearance (Meynardi et al., 2016).
The distribution of stress values presented a non-
parametric distribution in the investigated bone struc-
tures, this is expected due to anatomic characteristics of
the designed structures, the vector force incidence, and
the axis of tooth rotation. Other studies have shown
a similar distribution conguration (Ona and Waka-
bayashi, 2006; Geramy et al., 2004).
Stress values exceeding the critical threshold of
between 50 and 60 MPa have been reported to cause
detrimental effects on human cortical bone (Sugiura et
al., 2000). In our study, peaks of MPS were reached in
the 5 and 6 mm model in lamina dura. These ndings
are not in agreement with a previous study that found
the height bone reduction potentially did not cause
mechanical damage (Ona and Wakabayashi, 2006). It is
noteworthy that literal interpretation of the stress values
is not a straightforward matter and characteristics such
as position of the teeth (Gerami et al., 2016), oclusal
dynamic and cyclic loading conditions should all be
taken into account (Benazzi et al., 2013). Caution also
is necessary since the effects of forces are dependent
on the accuracy of the elastic properties that are being
fed into the program and the accurate biomechanical
proprieties of tissues (McGuinness et al., 1991). Alveolar
bone was chosen for analysis because it is one of the
rst tissues affected by the inammatory response to
bacterial stimuli (Nakamura et al., 2010). Biochemical
mediators regulate inammation and bone resorption
and some in vitro studies have shown that these sites can
also be be modulated by mechanical stimuli (Hienz et
al., 2015). The lamina dura area was chosen for analysis
because it has an intimate anatomical relationship with
the root surface and during injury, adaptive remodeling
occurs during the repair phase aiming to better cope
with excessive loads (Gerami et al., 2016).
An increase in the intensity of the MPS peak was
clearly seen in the LD when 40% of the attachment
area was lost, this increase also showed a peak increase
in the ABC, but without any change in pattern. The
correlation coefficient between the MPS peak and
percentage of attachment loss reveled the high degree
dependence between these parameters. When the force
of occlusion was constant, and the attachment area of
the tooth became smaller, the compressive/area stress
tended to increase.
Even considering the inherent limitations of
finite element analysis, and the restrictions in the
created computational mathematical model, such as
simplification of structures mechanical properties
(Cook and Mongeau 2007), the specic dental element
designed and its anatomical morphology are reasonable
Figure 4. Chart of Minimal Principal Stress peak increase in relation to no attachment loss model
70 Journal of the International Academy of Periodontology (2021) 23/1
if their impact on the conclusions is carefully taken
into account. It has been shown, for example, that the
assumption properties for periodontal ligament could
interfere with the stress values, but this did not change
the biomechanical behavior of tooth-periodontal
structure (Wood et al., 2011). Moreover, force application
is a difcult task to mimic because of the nature of
masticatory function and natural loading scenario.
However, the patterns of compressive stress distribution
values found in the simulated models, clearly indicated
a trend towards increase stress concentration when
periodontal attachment was reduced.
The results of this study provide some knowledge to
understanding the relationahip between occlusal trauma
in teeth with reduced attachment apparatus and normal
periodontal ligament space. Clinically, this suggests that
in vivo, similar clinical situations, submitted to chewing
forces can generate stresses that exceed physiological
limits and cause periodontal bone damage. Questions
about the threshold capability should be explored. These
ndings may potentially assist in the development of
treatment strategies and prevention to avoid alveolar
bone injury during periodontal treatment maintenance
phase. Thus, teeth with attachment loss and normal peri-
odontal ligament space, should receive special attention
in relation to occlusal relations and masticatory loads.
Limitations of this study are that the present models
do not represent all the oral variations such as changes
in pH, temperature, sliding occlusal loading, pres-
ence of bacteria, different antagonistic materials, and
parafunctional habit. The simulated condition used for
this study were considered isotropic and homogeneous
with a simplied behavior.
Conclusion
The results of this study demonstrate that attachment
loss around teeth increases stress concentration in the
surrounding bone. Despite inherent limitations of the
model used the results dene a biomechanical chang-
ing in stress pattern, which help to partly explain bone
resorption risk for teeth with periodontal attachment
loss and normal ligament space.
Acknowledgment
CAPES/FAPITEC/SE supported this research.
References
Armitage GC, Xenoudi P. Post-treatment supportive
care for the natural dentition and dental implants.
Periodontology 2000 2016; 71:164-184.
Benazzi S, Nguyen HN, Schulz D, Grosse IR, Gruppioni
G, Hublin J, Kullmer O. The evolutionary paradox of
tooth wear: simply destruction or inevitable adapta-
tion? PlOS one 2013; 8:e62263.
Burger EH, Klein-Nulend J. Mechanotransduction in
bone—role of the lacuno-canalicular network. The
FASEB Journal 1999; 13:101-112.
Cattaneo PM, Dalstra M, Melsen B. Strains in periodon-
tal ligament and alveolar bone associated with orth-
odontic tooth movement analyzed by nite element.
Orthodontics & Craniofacial Research 2009; 12:120-128.
Cook DD, Mongeau L. Sensitivity of a continuum vocal
fold model to geometric parameters, constraints, and
boundary conditions. Journal of the Acoustic Society of
America 2007; 121:2247-2253.
Dal Piva AMO, Tribst JPM, Saavedra GSFA, Souza RO,
Melo RM, Borges ALS, Ozcan M. Short communica-
tion: Inuence of retainer conguration and loading
direction on the stress distribution of lithium disili-
cate resin-bonded xed dental prostheses: 3D nite
element analysis. Journal of the Mechanical Behavior of
Biomedical Materials 2019; 100:103389.
Deng F, Zhang H, Zhang H, Shao H, He Q, Zhang
P. A comparison of clinical outcomes for implants
placed in fresh extraction sockets versus healed sites
in periodontally compromised patients: a 1-year
follow-up report. The International Journal of Oral &
Maxillofacial Implants 2010; 25:1036-1040.
Eke PI, Page RC, Wei L, Thornton-Evans G, Genco RJ.
Update of the case denitions for population-based
surveillance of periodontitis. Journal of Periodontology
2012; 83:1449-1454.
Gerami A, Dadgar S, Rakhshan V, Jannati P, Sobouti
F. Displacement and force distribution of splinted
and tilted mandibular anterior teeth under occlusal
loads: an in silico 3D nite element analysis. Progress
in Orthodontics 2016; 17:16.
Geramy A, Faghihi S. Secondary trauma from occlusion:
three-dimensional analysis using the nite element
method. Quintessence International 2004; 35:835-843.
Hambli R, Frikha S, Toumi H, Tavares JM. Finite ele-
ment prediction of fatigue damage growth in can-
cellous bone. Computer Methods in Biomechanics and
Biomedical Engineering 2016; 19:563-570.
Hienz SA, Paliwal S, Ivanovski S. Mechanisms of Bone
Resorption in Periodontitis. Journal of Immunology
Research 2015; 2015:615486.
Hirata T, Fuchida S, Yamamoto T, Kudo C, Minabe M.
Predictive factors for tooth loss during supportive
periodontal therapy in patients with severe periodon-
titis: a Japanese multicenter study. BMC Oral Health
2019; 15:19.
Johansson AS, Svensson KG, Trulsson M. Impaired masti-
catory behavior in subjects with reduced periodontal tis-
sue support. Journal of Periodontology 2006; 77:1491-1497.
Kleinfelder JW, Ludwigt K. Maximal bite force in pa-
tients with reduced periodontal tissue support with
and without splinting. Journal of Periodontology 2002;
73:1184-1187.
da Rocha et al.: Periodontal support nite element analysis 71
Kondo T, Wakabayashi N. Inuence of molar support
loss on stress and strain in premolar periodontium: a
patient-specic FEM study. Journal of Dentistry 2009;
37:541-548.
Martin JA, Page RC, Loeb CF, Levi PA, Jr. Tooth loss in
776 treated periodontal patients. Journal of Periodontol-
ogy 2010; 81:244-250.
McGuinness NJ, Wilson AN, Jones ML, Middleton J.
A stress analysis of the periodontal ligament under
various orthodontic loadings. The European Journal of
Orthodontics 1991; 13:231-242.
Mercuri EG, Daniel AL, Hecke MB, Carvalho L. Inu-
ence of different mechanical stimuli in a multi-scale
mechanobiological isotropic model for bone remod-
elling. Medical Engineering & Physics 2016; 38:904-910.
Mercuri EG, Daniel AL, Hecke MB, Carvalho L. Inu-
ence of different mechanical stimuli in a multi-scale
mechanobiological isotropic model for bone remod-
elling. Medical Engineering & Physics 2016; 38:904-910.
Meynardi F, Pasqualini ME, Rossi F, Dal Carlo L, Biancotti
P, Carinci F. Correlation between dysfunctional occlu-
sion and periodontal bacterial prole. Journal of Biologi-
cal Regulators and Homeostatic Agents 2016; 30:115-121.
Moroi HH, Okimoto K, Moroi R, Tereda Y. Numeric
approach to the biomechanical analysis of thermal
effects in coated implants. International Journal of
Prosthodontics 1993; 6:564-572.
Monteiro JB, Dal Piva AMDO, Tribst JPM, Borges ALS,
Tango RN. The effect of resection angle on stress
distribution after root-end surgery. Iranian Endodontic
Journal 2018; 13:180-188.
Nakamura A, Osonoi T, Terauchi Y. Relationship between
urinary sodium excretion and pioglitazone-induced
edema. Journal of Diabetes Investigation 2010; 1:208-211.
Ona M, Wakabayashi N. Inuence of alveolar support
on stress in periodontal structures. Journal of Dental
Research 2006; 85:1087-1091.
Papadopoulou K, Hasan I, Keilig L, Reimann S, Eliades
T, Jager A, Deschner J, Bourauel C. Biomechanical
time dependency of the periodontal ligament: a
combined experimental and numerical approach.
European Journal of Orthodontics 2013; 35:811-818.
Poiate IA, Vasconcellos AB, Andueza A, Pola IR, Poiate
E, Jr. Three dimensional nite element analyses of
oral structures by computerized tomography. Journal
of Bioscience and Bioengineering 2008; 106:606-609.
Poiate IA, de Vasconcellos AB, de Santana RB, Poiate E.
Three-dimensional stress distribution in the human
periodontal ligament in masticatory, parafunctional,
and trauma loads: nite element analysis. Journal of
Periodontology 2009; 80:1859-1867.
Rubin J, Rubin C, Jacobs CR. Molecular pathways mediat-
ing mechanical signaling in bone. Gene 2006; 367:1-16.
Suenaga H, Chen J, Yamaguchi K, Li W, Sasaki K, Swain
M, Li Q. Mechanobiological bone reaction quantied
by positron emission tomography. Journal of Dental
Research 2015; 94:738-744.
Sugiura T, Horiuchi K, Sugimura M, Tsutsumi S. Evalu-
ation of threshold stress for bone resorption around
screws based on in vivo strain measurement of mini-
plate. Journal of Musculoskeletal & Neuronal Interactions
2000; 1:165-170.
Tajima K, Chen KK, Takahashi N, Noda N, Nagamatsu
Y, Kakigawa H. Three-dimensional nite element
modeling from CT images of tooth and its validation.
Dental Materials Journal 2009; 28:219-226.
Takeuchi N, Ekuni D, Yamamoto T, Morita M. Relation-
ship between the prognosis of periodontitis and oc-
clusal force during the maintenance phase--a cohort
study. Journal of Periodontal Research 2010; 45:612-617.
Toparli M, Gökay N, Aksoy T. Analysis of a restored
maxillary second premolar tooth by using three-
dimensional nite element method. Journal of Oral
Rehabilitation 1999; 26:157-164.
Tribst JPM, Dal Piva AMO, Borges ALS, Bottino MA. In-
uence of Socket-shield technique on the biomechani-
cal response of dental implant: three-dimensional
nite element analysis. Computer Methods in Biomechanics
and Biomedical Engineering 2020; 23:224-231.
Tsutsumi T, Kajiya H, Goto KT, Takahashi Y, Okabe
K. Hyperocclusion up-regulates CCL3 expression
in CCL2- and CCR2-decient mice. Journal of Dental
Research 2013; 92:65-70.
Van Dyke TE, Hasturk H, Kantarci A, Freire MO,
Nguyen D, Dalli J, Serhan CN. Proresolving nano-
medicines activate bone regeneration in periodontitis.
Journal of Dental Research 2015; 94:148-56.
Versluis A, Versluis-Tantbirojn D. Filling cavities or
restoring teeth? The Journal of the Tennessee Dental
Association 2011; 91:36-42.
Wakabayashi N, Ona M, Suzuki T, Igarashi Y. Nonlinear
nite element analyses: advances and challenges in
dental applications. Journal of Dentistry 2008; 36:463-471.
Wakabayashi N, Kondo T, Yahagi R, Suzuki T. A patient-
based model study of xed splinting of premolars
with reduced periodontal support. International Journal
of Computerized Dentistry 2010; 13:317-330.
Wood SA, Strait DS, Dumont ER, Ross CF, Grosse IR.
The effects of modeling simplications on craniofa-
cial nite element models: the alveoli (tooth sockets)
and periodontal ligaments. Journal of Biomechanics
2011; 44:1831-1838.