Retentive forces and fatigue resistance of thermoplastic resin clasps
Introduction
The emphasis on physical appearance in contemporary society has increased the demand for esthetic dental restorations. Although the success of implant dentistry has expanded the scope of esthetic fixed prostheses, there are still many patients who for health, anatomic, psychological, or financial reasons are not candidates for implants [1]. These patients have the option of receiving partial removable dental prostheses (PRDPs) to replace missing teeth.
A major esthetical problem with PRDPs is the display of the clasp assemblies. Many methods have been used to overcome the esthetic problem such as etching the clasp arm and coat it with a layer of tooth-color resin [2], using lingual retention design [3], or proximal undercuts (also known as rotational path insertion) [4], [5], [6].
Direct retainers fabricated in a tooth-colored material and made from thermoplastic resin have been used to improve the appearance of metal clasp assemblies and are promoted for superior esthetics [7], [8], [9]. However, little information on the long-term performance of such clasps regarding retention is available in the literature.
Polyetheretherketon (PEEK) and polyetherketonketon (PEKK) are polymers from the group polyaryletherketone (PAEK) which is a relatively new family of high-temperature thermoplastic polymers, consisting of an aromatic backbone molecular chain, interconnected by ketone and ether functional groups [10]. In medicine PAEK has been demonstrated to be excellent substitute for titanium in orthopedic applications [10], [11], and it has been used in dentistry as provisional implant abutment [12].
Polyoxymethylene (POM) also known as acetal resin, an injection-molded resin has been introduced as an alternative to conventional PMMA. POM is formed by the polymerization of formaldehyde. The homopolymer, polyoxymethylene is a chain of alternating methyl groups linked by an oxygen molecule. It has a relatively high proportional limit with little viscous flow enabling it to behave elastically over a great enough range to be used as a material for clasp construction [7].
Various metallic materials have been used to fabricate the clasps of PRDPs and the physical properties of these materials have been examined [13], [14], [15], [16], [17], [18], [19], [20], [21], [22], [23]. The most common alloys used for clasps are cobalt–chromium (CoCr) alloys [21]. There have been studies that investigated the retention properties of CoCr alloys using repeated insertion/removal tests. Rodrigues et al. indicated an increase in retentive force during the simulating test [16], while retention decrease was reported by both Bridgeman et al. [20] and Kim et al. [24].
Retentive clasp arms must be flexible and should retain the PRDP satisfactorily. In addition, clasps should not unduly stress abutment teeth or be permanently distorted during service [25]. Previous studies indicated that PRDP clasps made of more elastic materials demonstrated a higher resistance to retention loss [24], [25].
Due to the low modulus of elasticity (2–4 GPa) (Table 3) [8], [10], thermoplastic resin has superior flexibility compared to the conventional CoCr alloys. Because of the reduced possibility of traumatic overloading, clasps made from thermoplastic resin can be designed to engage deeper undercuts on abutment teeth.
There are few studies that examined flexural properties of POM to determine the appropriate design for PRDP clasp [7], [8]. Arda and Arikan found that POM clasps are resistant to deformation and may offer a clinical advantage over conventional metal clasps [9]. However, to our best knowledge there are no studies evaluating the use of PEEK and PEKK as clasp materials.
Therefore, this in vitro study investigated the retentive force of different thermoplastic resin clasps during repetitive placement and removal on abutment teeth with two different thicknesses and two amounts of undercut. Conventional CoCr clasps were included as control group. The null hypothesis was that there would be no difference in the retentive force between resin clasps and cast CoCr alloy clasps.
Section snippets
Materials and methods
Three thermoplastic resins (POM, PEEK and PEKK) and a conventional CoCr alloy were evaluated in this study.
All used materials are presented in Table 1.
Results
Fig. 3, Fig. 4 show the changes in retentive force required to remove clasps from the 0.25 mm and 0.50 mm undercuts.
The mean initial retentive force ranged from 1.2 to 3.1 N for the 1.0 mm thick resin clasps and from 4.9 to 9.1 N for the 1.5 mm thick resin claps. For CoCr clasps it ranged from 11.3 to 16.3 N. The highest initial retentive force (16.3 N) was recorded in the CoCr clasps with 0.50 mm undercut, and the lowest retentive force (1.2 N) was measured in the 1.0 mm POM clasps with 0.25 mm undercut.
Discussion
Based on the data obtained in this investigation, the CoCr clasps showed significantly higher retention force as thermoplastic resin claps. Therefore, the null hypothesis that there would be no difference in the retentive force between resin clasps and cast CoCr alloy clasps was rejected.
The retentive force is dictated by tooth shape and by clasp design. Tooth shape influences retention by determining the depth of undercut available for clasping [26]. This study was designed to compare the
Conclusion
Within the limitation of this study, it was found that the thermoplastic resin clasps maintained retention over 15,000 joining and separating cycles with significantly lower retention than CoCr clasps. However, the retention of adequately designed resin clasps might be sufficient for clinical use.
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