retention and stress distribution in distal extension removable partial dentures with and without...
TRANSCRIPT
Original article
Retention and stress distribution in distal extension removable partial
dentures with and without implant association
Renata Cristina Silveira Rodrigues DDS, MSc, PhD*, Adriana Claudia Lapria Faria DDS, MSc, PhD1,Ana Paula Macedo BEng, MSc2, Maria da Gloria Chiarello de Mattos DDS, MSc, PhD3,
Ricardo Faria Ribeiro DDS, MSc, PhD4
Department of Dental Materials and Prosthodontics, Dental School of Ribeirao Preto, University of Sao Paulo, Av. do Cafe, s/n, Monte Alegre, 14040-904 Ribeirao
Preto, SP, Brazil
Received 24 November 2011; received in revised form 4 May 2012; accepted 9 July 2012
Available online 27 November 2012
Abstract
Purpose: The present study aimed to evaluate the retention and stress distribution of conventional (C) RPD and compare to RPD associated to
implant for support (IS) and retention (IR).
Methods: Frameworks were cast from cp Ti (n = 18) and Co–Cr alloy (n = 18) by plasma and injected by vacuum–pressure. Conventional RPDs were
compared to implant associated RPDs using a distal implant to support (IS) or to support and retain (IR) RPD. The specimens were subjected to
insertion/removal cycles simulating 5 years of use and the retention force (N) was measured or evaluated. A mixed linear model was used to analyze the
data (a = 0.05). Photoelastic models were qualitatively examined for stress when an occlusal load of 15 kgf was applied over support teeth and RPD.
Results: Retention force of IR RPDs is greater than IS and C RPDs for both cp Ti and Co–Cr alloy specimens. Retention force of cp Ti RPDs
increased initially and was maintained throughout 5 years of simulation test while Co–Cr RPDs presented a decrease at the beginning of the test and
had their retention force maintained throughout the test. Implant placement at residual alveolar ridge decreased stress around teeth, mainly in the
first premolar. Stress concentration in the IS RPD is slightly greater than in the IR RPD.
Conclusion: The results suggest that implant placement at the distal extension improves retention and stress distribution of RPDs.
# 2012 Japan Prosthodontic Society. Published by Elsevier Ireland. All rights reserved.
Keywords: Dental implantation; Dental prosthesis retention; Denture precision attachments; Removable partial dentures
www.elsevier.com/locate/jpor
Available online at www.sciencedirect.com
Journal of Prosthodontic Research 57 (2013) 24–29
1. Introduction
Although implant-supported fixed partial dentures are the
ideal treatment option for partially edentulous patients, bone
loss in mandibular posterior regions could require bone graft
and mandibular nerve lateralization procedures for implant
placements, representing high surgical risk and cost, discoura-
* Corresponding author. Tel.: +55 16 3602 4005; fax: +55 16 3602 4780.
E-mail addresses: [email protected] (R.C.S. Rodrigues),
[email protected] (A.C.L. Faria), [email protected] (A.P. Macedo),
[email protected] (M.d.G.C. de Mattos), [email protected] (R.F. Ribeiro).1 Tel.: +55 16 3602 4130; fax: +55 16 3602 4780.2 Tel.: +55 16 3602 4104; fax: +55 16 3602 4780.3 Tel.: +55 16 3602 4098; fax: +55 16 3602 4780.4 Tel.: +55 16 3602 4046; fax: +55 16 3602 4780.
1883-1958/$ – see front matter # 2012 Japan Prosthodontic Society. Published b
http://dx.doi.org/10.1016/j.jpor.2012.07.001
ging patients [1,2]. Thus, removable partial dentures (RPDs)
still represent an alternative of rehabilitation for these patients.
Distal extension RPDs are complex because of the teeth and
mucous support, requiring better load distribution for both
tissues to avoid vertical, horizontal and torsional forces that
may have adverse effects [3,4]. Thus, the use of distal implants
to support and retain RPDs has been reported in the literature to
minimize dislodgement, improve esthetics and mastication,
resulting in patient satisfaction in a cost-effective manner [3–5].
Cobalt–chromium (Co–Cr) alloy is the material more used
around the world to construct RPD frameworks because of low
cost, corrosion resistance, high microhardness and modulus of
elasticity and low density [6]. Titanium alloys and commer-
cially pure titanium (cp Ti) represents alternatives to Co–Cr
alloy RPD frameworks. Some titanium advantages such as
resistance, low specific weight, high corrosion resistance, good
physical and mechanical properties, low cost and excellent
y Elsevier Ireland. All rights reserved.
R.C.S. Rodrigues et al. / Journal of Prosthodontic Research 57 (2013) 24–29 25
biocompatibility increased the interest in the application of this
metal for prosthesis frameworks after 1980 decade [6–13].
Thus, titanium and titanium alloy RPD frameworks have been
searched showing good retention throughout time [6,12,13].
Several studies have researched stress distribution of distal
extension RPDs associated with implants in different positions
of alveolar residual ridge varying implant dimensions and
attachment systems [1,2,14]. Nevertheless, the retention of
conventional and implant associated RPDs, which is important
to minimize dislodgement, resulting in improved mastication
and patient satisfaction, was not evaluated yet. The null
hypothesis was that the association of an implant in residual
alveolar ridge with RPDs improves retention and stress
distribution. Thus, the aim of the present study was to evaluate
the retention and stress distribution of conventional RPD and
compare to RPD associated to implant for support and
retention.
2. Materials and methods
2.1. Specimen preparation
A metallic matrix representing a distal extension mandibular
right hemi-arch segment, presenting first and second premolar,
was fabricated from Co–Cr alloy. Undercuts of 0.25-mm (0.01-
inch) were provided in the positions established for T-bar
clasps. In addition, a mesial occlusal rest and proximal and
lingual guide-planes were prepared on the second premolar to
standardize the path of insertion. This matrix was used to
perform the use simulation test.
The matrix was relieved for the correct waxing of the
frameworks and duplicated in silicone (Silicone Master,
Talmax, Curitiba, Brazil). Casts with Rematitan Plus (Den-
taurum, Pforzheim, Germany) were used to make the cp Ti
(Tritan1 grade I, Dentaurum) specimens, and casts with Crom-
O-Cast (Polidental Industry and Commerce Ltd., Sao Paulo,
Brazil) were used to make the Co–Cr alloy (Vera PDI, Aalba
Dent. Inc., Cordelia, CA, USA) specimens.
Casts were positioned at the dental surveyor according to
their guide planes which standardized the path of insertion.
Thus, prefabricated T-bar clasp patterns (Rewax, Renfert
GmbH, Hilzingen, Germany) were positioned on the casts
following a tray obtained from a plate vacuum formed in the
first waxing, permitting to get similar framework waxings. In
addition, plastic pins (5 mm wide and 30 mm long) were
attached to a circular retention mesh (Renfert GmbH)
positioned in the area corresponding to the distal extension
partial denture base. This pins originally served as a sprue for
the molten alloy and, secondly, it was used to position the
specimens in the simulation test machine.
The specimens were cast by plasma, in the machine
Discovery Plasma (EDG Equipments and Controls Ltd., Sao
Carlos, Brazil), where the melting was made by arc melting in a
vacuum and argon inert atmosphere, with injection of the alloy/
metal into the mold by vacuum–pressure. After casting, the
specimens were removed from the cast and airborne-particle
abraded with aluminum oxide particles (80 psi = 5.62 kgf/
cm2). When nodules and burs were noted, they were removed
using tungsten burs under magnification. Co–Cr specimens
were subject to electrolytic polishing in a VRC apparatus for
15 min (R.R. Equipments for Dental Prostheses Ltd., Sao
Paulo, Brazil), and cp Ti specimens received chemical
polishing by soaking in Kroll solution (10 mL HF, 30 mL
HNO3 and 50 mL water) for 1 min.
Before the tests, all specimens were radiographically
examined to detect possible casting defects that would
contraindicate their use in the tests using a laboratorial unit
X-Control (Dentaurum, Ispringen, Germany).
Specimens were divided into three groups according to their
support system:
– conventional RPD (C);
– implant supported RPD (IS), using a distal implant with a
healing cap to improve the support;
– implant retained RPD (IR), using a distal implant with a ball
attachment and O’ring to improve the support and the
retention.
A layer (3 mm) of polyether film [15] was applied at the
distal extension of the matrix to simulate the mucosa in the C
RPD group (Fig. 1A). For the C RPDs, framework specimens
were positioned at the matrix and the base was constructed
polymerizing the resin (Stern Tek, Sterngold, Attleboro, MA,
USA) for 4 min in a light-curing unit (EDG Lux, EDG
Equipments and Controls Ltd.).
At IS RPD group, an implant (Titamax CM 5 mm � 8 mm,
Neodent, Curitiba, Brazil) was inserted with cyanoacrylate
based glue (Super Bonder, Loctite, Sao Paulo, Brazil) at the
matrix using a dental surveyor to replace the second molar. A
healing cap (Neodent) measuring 4.5 mm in diameter and
1.5 mm in height was installed in the implant with a torque of
10 N cm. After this, the framework was positioned and the base
constructed over the healing cap at the same manner of the C
RPD group (Fig. 1B).
At IR RPD group, the healing cap was replaced by a ball
attachment measuring 1.5 mm in height (Neodent) that was
installed in the implants with the recommended insertion torque
of 20 N cm. The framework was positioned at the matrix and a
cylinder with O’ring was captured using light-curing resin
(Stern-Tek) at the moment of the base construction (Fig. 1C).
2.2. Simulation test
After specimen preparation, the simulation test was
performed in an insertion/removal testing apparatus designed
at the Department of Dental Materials and Prosthodontics of the
Dental School of the Ribeirao Preto, University of Sao Paulo,
Brazil [6,12,13]. The apparatus allowed for the insertion of the
metallic framework into its terminal position on the Co–Cr
matrix passively without any load and its subsequent removal,
thus simulating the placement and removal of an RPD. The
matrix and specimen were positioned in an acrylic box of
testing apparatus that permits deionized water immersion. Tests
were performed in a wet environment at 37 � 5 8C and
Fig. 1. Matrix for conventional (A), implant supported (B) and implant retained (C) RPD frameworks.
R.C.S. Rodrigues et al. / Journal of Prosthodontic Research 57 (2013) 24–2926
temperature was controlled by a thermostat and a resistance
[12,13]. The wet environment at 37 8C was set up based on
body temperature and previous studies [12,13] that used wet
environment to better simulate the oral condition decreasing the
attrition between the matrix and framework. Deionized water
was chosen to avoid chemical interaction of the solution with
the matrix, framework and prosthetic components.
To analyze the data obtained during the simulation test,
intervals corresponding to 0, 1/2, 1, 2, 3, 4 and 5 years were
established. A total of 7205 cycles were performed, represent-
ing the simulated insertion and removal of the RPD over 5
years, estimating that the patient would perform 4 complete
cycles per day [6,12,13]. The test was performed with
41 cycles/min at a constant speed of 35.79 mm/s. The value
established for each time interval corresponded to the
arithmetic average of 10 consecutive insertion/removal cycles.
The force required for each specimen removal was captured and
stored using data acquisition software (LabView 5.0.1, National
Instruments, Austin, TX, USA).
To evaluate the effect of time and compare the different
prostheses at the retention force, the statistical analysis was
performed using a mixed linear model, which is a general-
ization of the standard linear model (ANOVA). The compar-
isons were made by orthogonal contrasts using PROC MIXED
procedure of SAS software (SAS Institute Corp., Cary, NC,
USA). This model is used in the analysis of data in which the
responses of the same specimen are grouped, and the
assumption of independence among the observations in the
same group is not adequate [16]. For the utilization of this
model, it is necessary that the errors have a normal distribution
with mean zero and constant variance. Differences were
considered significant when p < 0.05.
2.3. Photoelastic analysis
Two rectangular (68 mm � 30 mm � 15 mm) models of
polycarbonate with orifices for insertion of teeth and implant
were used as master models. In the first model, the first and the
second inferior premolars of resin (Odontofix, Ribeirao Preto,
Brazil) were inserted in the orifices with cyanoacrylate based
glue (Super Bonder) using a dental surveyor. In the second
model, not only the teeth were inserted but also an analog of the
implant (Titamax CM 5 mm � 8 mm, Neodent) was inserted in
other orifice at the position of the right inferior second molar.
Master models were impressed using a duplication silicone
(Silicone Master, Talmax) to reproduce accurately tooth
position at the photoelastic model. Implant position was
reproduced using an impression transfer. After 24 h, transfer
was unscrewed to permit master model removal.
Tooth root received a standardized layer (300 mm) of
polyether (Impregum, 3 M ESPE, Seefeld, Germany) to simulate
periodontal tissues [17]. After teeth were fit to their silicone molds
and implant (Titamax CM 5 mm � 8 mm, Neodent) was screwed
to its transfer, photoelastic resin (Araldite CY 279 and Aradur
2963, Huntsman, Everberg, Belgium) was manipulated accord-
ing to manufacturer’s instructions and poured into the mold. The
implant was directly embedded in the photoelastic resin without
any interposed material to simulate osseointegration. After 72 h,
the photoelastic model was removed and analyzed.
The healing cap and ball attachment were installed at the
implant at the same manner of the specimen preparation for
simulation test. Similarly, the base was constructed directly
over the photoelastic model and teeth were mounted over the
base and the resin (Stern Tek) polymerized for 4 min in a light-
curing unit (EDG Lux).
Photoelastic models were qualitatively examined for stress
in the field of a circular polariscope (PS-100 SF Polarimeter,
Strainoptics Technologies, North Wales, PA, USA). A digital
camera (EOS Rebel, Canon, Tokyo, Japan) was coupled to the
polariscope to photograph each situation of interest. When any
stress was noted before load applying, models were maintained
at 50 8C in an oven trough 10 min to relieve the stress. Loads
were applied with a straining frame and monitored by means of
a calibrated 50 kgf load cell (Kratos, Sao Paulo, Brazil)
mounted on the movable head of the frame and a digital display
(IKE-01, Kratos). An occlusal load of 15 kgf was applied over
support teeth and RPD. Antagonist teeth were mounted in an
ideal occlusion against support teeth and RPD using light-
curing resin (Stern-Tek). This load was selected because they
are functional load levels and they also provide a satisfactory
optical response within the model.
The stresses around teeth and implant were monitored and
recorded photographically in the field of a circular polariscope
and the monochromatic fringe pattern findings were accom-
plished for each condition of load application [18].
3. Results
3.1. Simulation test
The retention force results of different prostheses throughout
time are presented in Fig. 2. Retention force of IR RPDs is
Table 1
Comparison among conventional (C), implant supported (IS) and implant
retained (IR) RPDs.
Comparison Metal/alloy Differencea p-Value 95% CI*
Inferior Superior
C–IS Co–Cr �1.040 0.002 �1.697 �0.384
C–IR �1.767 <0.001 �2.423 �1.111
IS–IR �0.727 0.030 �1.383 �0.070
C–IS cp Ti �0.668 0.046 �1.325 �0.012
C–IR �2.526 <0.001 �3.182 �1.869
IS–IR �1.858 <0.001 �2.514 �1.201
a Difference between means of each prosthesis type for each metal/alloy.* CI, confidence interval for the estimate of mean difference.
Fig. 2. Retention force (N) throughout simulation test.
R.C.S. Rodrigues et al. / Journal of Prosthodontic Research 57 (2013) 24–29 27
statistically greater than IS and C RPDs for both cp Ti and Co–
Cr alloy specimens (Table 1).
Retention force of Co–Cr C RPDs after 5 years is
statistically greater than at 6-month, 1 and 2-year periods.
At IS RPD, retention force after 5 years is statistically greater
than at 1-year period while IR RPD presented a significant
decrease only at first six months. However, no differences were
noted for cp Ti C and IS RPDs while IR RPDs presented
retention force statistically greater after 4 and 5 years of
simulated use than at the beginning (Table 2).
3.2. Photoelastic analysis
Fringe patterns presented in Fig. 3 show the stress
distribution around support teeth and/or implant of C, IS and
IR RPD when load is applied. When load is applied over C
RPD, stress around the second (support tooth) and first
premolar is noted and residual alveolar ridge region is free of
stress (Fig. 3A). The presence of an implant at the distal
extension contributes to stress distribution eliminating the
stress around the first premolar (Fig. 3B and C). However, stress
concentration around implant and second premolar in the IS
RPD (Fig. 3B) is slightly greater than in the IR RPD (Fig. 3C).
4. Discussion
In the present study, retention force was evaluated by
simulation test and cp Ti RPDs were less retentive than Co–Cr.
Retention force of cp Ti RPDs increased initially and was
maintained throughout 5 years of simulation test while Co–Cr
presented a decrease at the beginning of the test and had their
retention force maintained throughout the test. These results are
according to some authors [6,12] that evaluated retention force
of circumferential and T bar (cp Ti and Co–Cr) clasps relating
maintenance of retention force throughout the test. Never-
theless, the abutment tooth and its effective guide-planes used
in this study consist of a rigid system while the periodontal
ligament present in the mouth allows for small tooth movement.
Because there are usually different insertion and removal paths
in the mouth, since obtaining truly effective guide-planes is
conditioned by anatomical aspects, and patients can change the
path used to move the denture at each insertion and/or removal
cycle, greater loads are produced on the tooth, thus leading to
permanent clasp deformation in a short period of time [12].
According to Sato et al. [19], when a clasp is constructed in
clinical situations, the inner surface is sandblasted and will be
abraded and have a shiny spot, decreasing friction coefficient
and consequently the retention force. The same authors also
related that, for a metal abutment, the initial period will indicate
a large friction coefficient and after the inner surface of the
clasp is abraded, the friction coefficient is lowered. Considering
that electrolytic polishing was used for framework specimen in
the present study, the contact between inner surface of clasp and
polished metallic matrix probably decreased friction coefficient
and retention force because of abrasion at the beginning of the
test. On the other hand, cp Ti exhibit high friction values and an
increased tendency for material transfer and adhesive wear
[20]. A study that evaluated wear resistance of cp Ti and
titanium alloys suggested a deformation at the border of worn
surface [21] confirming adhesive wear of cp Ti. Thus, the
increase of retention force of cp Ti specimens could be
attributed to this adhesive wear and deformation that increases
surface contact and consequently friction coefficient.
An author argued that a RPD should present a force of
approximately 20 N to hold it in place when sticky foods are
chewed and still allow patients to remove RPD while clasps
should present a retention of 5–10 N to be appropriate [22]. As
the specimen framework of the present study is made of only
one clasp, the retention force of the Co–Cr RPDs would be
appropriate for clinical use. However, cp Ti frameworks of C
and IS RPD groups presented retention force ahead of the
values recommended in the literature [22] but these results
reinforces the clinical necessity of using cp Ti clasps in more
retentive areas than Co–Cr, once low modulus of elasticity
permits to position cp Ti clasps in more retentive areas without
oblique load transmission to support teeth at the insertion and
removal, providing better esthetics [12].
The results of the present study show that prosthesis
retention was maintained throughout 5 years of simulation test
independent of the metal/alloy or type of prosthesis. Previous
studies [6,12] that evaluated RPD framework retention without
implant association had their retention force maintained
throughout the time, as noted in the present study. Thus, the
use of implant to support or to retain RPD did not affect
retention throughout the time, but the use of implant increased
Table 2
Comparison of retention force (N) throughout the time for the different prostheses.* Data are presented as mean (standard deviation).
Initial 6 months 1 year 2 years 3 years 4 years 5 years
Co–Cr C 6.6 (2.9)ab 5.1 (2.1)a 4.9 (1.4)a 5.3 (1.2)a 5.5 (1.3)ab 6.3 (1.8)ab 7.2 (2.2)b
IS 6.9 (1.4)ab 6.4 (1.9)ab 6.1 (1.8)a 6.7 (2.2)ab 6.7 (2.4)ab 7.6 (2.1)ab 7.9 (2.1)b
IR 8.7 (1.7)a 6.9 (1.0)b 7.2 (1.7)ab 7.1 (1.6)ab 7.6 (1.8)ab 7.7 (1.9)ab 8.1 (1.6)ab
cp Ti C 2.3 (0.4)a 3.1 (1.1)a 2.9 (1.2)a 3.1 (1.2)a 3.1 (1.3)a 3.3 (1.3)a 3.3 (1.0)a
IS 2.4 (0.6)a 3.9 (1.0)a 3.9 (0.9)a 3.9 (0.6)a 3.8 (0.7)a 3.8 (0.6)a 3.9 (0.7)a
IR 4.0 (0.8)a 5.4 (1.6)ab 5.5 (1.7)ab 5.7 (1.9)ab 5.7 (1.9)ab 6.2 (1.7)b 6.1 (1.5)b
* Different letters mean statistically significant difference at the line (a = 0.05).
Fig. 3. Stress distribution in the photoelastic models using a conventional (A), implant supported (B) and implant retained (C) RPD frameworks.
R.C.S. Rodrigues et al. / Journal of Prosthodontic Research 57 (2013) 24–2928
retention when compared to conventional RPD frameworks,
mainly in the IR group.
Although implant retained overdentures using ball attach-
ment/O’ring present a decrease of retention force after clinical
or simulated use [23–26], IR RPDs did not present a decrease of
retention force probably because of RPD insertion/removal
path that avoids lateral and oblique dislodgement, protecting
O’ring rubber from wear or deformation.
In addition to the better retention of IS and IR RPDs, the
main advantage of RPD/implant association is the load
transmission. According to some authors [1,2,14], implant
movement is lower than periodontal tissues, decreasing base
movement toward residual ridge. The benefits of implant
association are to prevent bone loss, decrease stress around
support teeth and to improve retention, masticatory efficiency
and comfort [2].
Photoelastic models of the present study demonstrate the
importance of an implant at residual alveolar ridge region to
decrease stress around teeth, mainly the first premolar. These
results corroborate other study [1] that found greater load
concentration around support teeth at conventional RPD and
decrease of load transmission in the region of the residual ridge
between support teeth and implant, when an implant in the
distal extension was used even load transmission around
support teeth was not decreased. IS and IR RPDs decrease load
transmission to the first premolar and increase transmission for
implant area. Additionally, the use of a ball attachment/O’ring
at the IR RPDs improved load distribution between support
teeth and implant when compared to IS RPDs, probably
because O’ring rubber partially absorbs the load.
According to a crossover study, patients that used
conventional and implant supported RPDs, preferred implant
supported RPDs because of retention, comfort, stability and
chewing. Additionally, implant supported RPDs can be an
alternative for partially edentulous patients when an implant
supported fixed prosthesis cannot be applied because of
anatomical or economic reasons [27].
Thus, the association between RPD and implant can improve
retention and load distribution, representing an interesting
alternative for patients with clinical and financial limitations.
After analyzing images of photoelasticity and results of
simulation test, it is possible to observe that the obtained results
confirm the hypothesis that the association of implant to RPD in
the distal extension residual ridge improves the retention and
stress distribution.
Acknowledgements
The authors thank from Sao Paulo State Research
Foundation – FAPESP (2006/57559-6) for the financial support
and Mr. Luiz Sergio Soares and Mr. Marcelo Aparecido Vieira
by their technical support.
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