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Article

Relevant Aspects in the Mechanical and Aging Degradation of NiTi Alloy with R-Phase in Endodontic Files

by
Patricia Sánchez
1,†,
Benedetta Vidi
2,3,†,
Cristina Rico
3,
Jesús Mena-Alvarez
3,*,
Javier Gil
1,* and
Juan Manuel Aragoneses
3,4
1
Bioengineering Institute of Technology, Facultad de Medicina y Ciencias de la Salud, Universitat Internacional de Catalunya, 08195 Sant Cugat del Vallés, Spain
2
Programa de Doctorado Ciencia de la Salud, Universidad de Alcalá, Pza. San Diego s/n, 28801 Alcalá de Henares, Spain
3
Faculty of Dentistry, Universidad Alfonso X El Sabio, C. de Emilio Muñoz, 13, 28691 Madrid, Spain
4
Department of Dental Research, Federico Henriquez y Carvajal University, Santo Domingo 10106, Dominican Republic
*
Authors to whom correspondence should be addressed.
†
These authors contributed equally to this work.
Materials 2024, 17(13), 3351; https://doi.org/10.3390/ma17133351 (registering DOI)
Submission received: 20 May 2024 / Revised: 19 June 2024 / Accepted: 24 June 2024 / Published: 6 July 2024
(This article belongs to the Special Issue Orthodontic Materials: Properties and Effectiveness of Use)
Browse Figures
Versions Notes

Abstract

:
One of the most important challenges in endodontics is to have files that have excellent flexibility, toughness, and high fatigue life. Superelastic NiTi alloys have been a breakthrough and the new R-phase NiTi alloys promise to further optimize the good properties of NiTi alloys. In this work, two austenitic phase endodontic files with superelastic properties (Protaper and F6) and two austenitic phase files with the R-phase (M-wire and Reciproc) have been studied. The transformation temperatures were studied by calorimetry. Molds reproducing root canals at different angles (30, 45, and 70°) were obtained with cooling and loads simulating those used in the clinic. Mechanical cycles of different files were realized to fracture. Transformation temperatures were determined at different number of cycles. The different files were heat treated at 300 and 500 °C as the aging process, and the transformation temperatures were also determined. Scanning and transmission electron microscopy was used to observe the fractography and precipitates of the files. The results show that files with the R-phase have higher fracture cycles than files with only the austenitic phase. The fracture cycles depend on the angle of insertion in the root canal, with the angle of 70° being the one with the lowest fracture cycles in all cases. The R-Phase transformation increases the energy absorbed by the NiTi to produce the austenitic to R-phase and to produce the martensitic transformation causing the increase in the fracture cycles. Mechanical cycling leads to significant increases in the transformation temperatures Ms and Af as well as Rs and Rf. No changes in the transformation temperatures were observed for aging at 300 °C, but the appearance of Ni4Ti3 precipitates was observed in the aging treatments to the Nickel-rich files that correspond to those with the R transition. These results should be considered by endodontists to optimize the type of files for clinical therapy.

1. Introduction

NiTi alloy presents a thermoelastic martensitic transformation and gives rise to shape memory and pseudoelasticity properties that are of interest for their application in different fields of medicine, such as orthodontics, rehabilitation, cardiovascular medicine, and endodontics, among others [1,2,3,4]. This reversible transformation is produced from the matrix phase or austenite B2 (A) and the B19′ (M) phase called martensite.
The chemical compositions of NiTi alloys have been optimized and new thermomechanical treatments have been developed with different heat treatments that allow an intermediate phase in the martensitic transformation to be obtained. This intermediate phase is called the R-phase and was also called the pre-martensitic transition. The R-phase is a rhombohedral structure between B2 and B19′. The transformation is B2 → R → B19′ [5,6].
According to Landau’s theories on the free energy associated with B2 B19′ and B2 → R → B19′, it is suggested that this multiple martensitic transformation takes place by the sequence of an increase in the deformation generated by the transformation or by an increase in the transformation entropy. In fully annealed NiTi alloys, the B19′ phase is more stable than the R-phase and consequently by cooling the B2 → B19′ transformation takes place [7].
The formation of dislocation tangles or the precipitation of coherent Ni4Ti3 compounds in nickel-rich NiTi alloys causes an obstacle to the martensitic B2 → B19′ transformation, and the R-phase appears [8,9]. The distortion in the formation of the R-phase is about 1%, which is much smaller than that associated with the direct transformation to B19′, which is about 10%; this makes the transition to the R-phase favored, and there is therefore a temperature at the beginning of the transformation to R, i.e., Rs, which is higher than the temperature at the beginning of the transformation to B19′, i.e., Ms [10,11].
If we have an endodontic file in the austenitic phase and we apply stress when introducing the file into the root canal, the austenite of the NiTi will be transformed into martensite induced by stress, exceeding levels of deformation much higher (up to 15%) compared to conventional metals [12,13]. When the clinician removes the file from the canal, and in the absence of stress, the NiTi will recover the austenite phase; i.e., a retransformation of the stress induced martensite takes place. This great elastic and flexibility behavior and its adaptation to the canal make NiTi an alloy for the application of this metal in endodontic files [14,15]. The transformation temperatures are the key to the properties and these depend fundamentally on the chemical composition. One of the biggest problems for NiTi instrumentation manufacturers is the reproducibility of the chemical composition. Normally, the alloys are equiatomic or very close to 50% atomic composition of each other, small variations in the contents of nickel or titanium will vary the transformation temperatures and therefore the phases of the alloy. Also grain sizes and dislocation density can affect transformation temperatures but not as strongly as variations in chemical composition [16,17].
Fractures that occur in endodontic files are fatigue and torsional fractures. The cracks appear in the areas of maximum stress that coincide with the point of maximum curvature in the dental canal. The fractures of NiTi files are due to the fact that the load cycles produce stress-induced martensitic transformations, and with the number of cycles, dislocations appear, and these can anchor the martensite plates and prevent them from re-transforming to austenite when the mechanical load is released [18]. These martensite plates are called stabilized martensite and cause the file to lose superelasticity and become an alloy without superelastic properties and consequently lose the extra toughness of superelastic alloys. It has been demonstrated for endodontic files that as the number of cycles of use increases, the enthalpies of transformation and retransformation are reduced until in the fracture cycle these energy values are practically zero. This decrease in enthalpies indicates that the energy to produce transformation and retransformation is decreasing because there is more and more stabilized martensite that, anchored by defects, is not susceptible to transformation [18,19,20].
The aim of this contribution is a laboratory study to determine the improvements in the fatigue behavior of alloys with the R-phase in their structure. The effect of the R-phase at different angles of application in the root canal will be studied with respect to files that do not present this R-phase. This study will make it possible to determine the advantages of this type of alloy with respect to conventional NiTi. In addition, the effects of the aging process, thermal cycling, and annealing process are analyzed. These aspects have to be considered by the clinicians to use the most suitable files with adequate treatments.

2. Materials and Methods

2.1. Materials

Four NiTi endodontic rotary files were studied.
  • Protaper UltimateTM F2 008v (Denstply Sirona, Ballaigues, Switzerland). Diameter 2.5 mm and length of working 16.0 mm. (Protaper)
  • F6 SkyTaper® files 25 mm. (Komet Lemgo, Nordrhein Westfalen, Germany). Diameter 2.5 mm and length of working 16.5 mm. (F6)
  • Reciproc®. V040252025025. 25 mm, (VDW, Munchen, Germany). Diameter 2.5 mm and length of working 16.2 mm. (Reciproc)
  • M-wire. Vortex Rotary Files. 25 mm (Dentsply Sirona, Johnson City, TN, USA). Diameter 2.5 mm and length of working 16.0 mm. (M-wire)
The chemical composition for Protaper was 49.5% in weight of nickel and 50.5% in weight of titanium, and for F6, it was 49.7% and 50.3% in weight of nickel and titanium, respectively. For Reciproc, the composition was 50.8% and 49.2% in weight of nickel and titanium, respectively, and for M-wire, 50.5% and 49.5 in weight of nickel and titanium, respectively. Other chemical elements were not detected. The chemical composition was measured by means of energy-dispersive X-ray microanalysis with a sensitivity of 0.1%.
Protaper and F6 are NiTi endodontic files with austenitic–martensite transformation. Reciproc and M-wire presented austenite with R-phase which transforms to martensite. The length of the four files studied was 25 mm in all cases.
The endodontic files used are of the brand (Figure 1) and are placed on a motor X-Smart® of Dentsply Sirona (Charlotte, NC, USA) with a speed of 300 rpm and torque of 2.2 N cm.
Endodontic cycles are performed on molds made of polyamide with properties very similar to the natural tooth obtained by 3D printing with canals with angles of 30, 45 and 70°. These are the most common tooth canal angles in patients [21]. The file force on the mold was 5.5 N, and they were lubricated every 25 cycles (5 s) with an aqueous solution of 5% sodium hypochlorite. For the determination of the force to which the file is subjected on the mold, different measurements were performed by 25 clinicians of the Clínica Universitaria Odontológica Alfonso X el Sabio, obtaining a mean value of 5.5 N with a standard deviation of 2.8 N. The high precision dynamometer was Adamel Lombhragy (X1234, Lyon, France) and is adjusted to the hand of the clinician who will perform the tests with maximum force control adjusted. The diagrams of the molds used can be seen in Figure 2.
For the test, it was important that the lubrication of the file was as similar as possible to what occurs in the clinic, and for this purpose, the instrument was soaked in the aqueous solution, which was maintained at 37 °C. This meant that the variations in the temperature of the file were negligible, as this could affect the phases present in the file if they were overheated.
Cycles to fracture were made for each type of endodontic files. The fracture files were also observed by scanning electron microscopy using a JEOL 6400 (JEOL, Tokyo, Japan) and transmission electron microscopy was performed using a JEOL 1200 EXII. Microscopy coupled with energy-dispersive X-ray microanalysis (Oxford Instruments, Oxford, UK) was used for determining the chemical composition.
The number of endodontic files used was analyzed by experiment design. The total number was 5 files for each endodontic file × 4 types of files × 3 angles studied = 60 samples.

2.2. Calorimetric Tests

Five samples for each endodontic rotary file and for each thermal treatment were analyzed, all of them 25.0 mm long and 0.46 mm in diameter. The transformation temperatures were measured by means of a calorimeter Melcor S 10. The calorimetric system used was based on a flow calorimeter, which measured differential signals (ΔT) by means of thermocouples batteries. The temperature was measured by means of a standard Pt-100 probe. All signals were digitalized through a multichannel recorder and linked to a microcomputer [20]. All signals were digitalized through a multichannel recorder and linked to a microcomputer. Ms, Rs and As transformation temperatures occur when there is a sudden increment in calorimetric signal. In the same way, the final temperatures, Mf, Rf and Af, are determined when the calorimetric signal returns to the baseline. The method used to determine the transformation and retransformation temperatures was the tangent [21,22].

2.3. Mechanical Cycles

Mechanical cycling was carried out at the 30, 45 and 70° angles. Ten files of each type and for each angle were cycled at different number of cycles to fracture. The files were cooled, as indicated above, in order to simulate clinical reality as closely as possible. For the different cycles, the transformation temperatures Ms and Af were determined calorimetrically for the Protaper and F6 files, and for the Reciproc and M-wire files, the temperatures Ms and Af were determined; for the start and end temperatures of the R-phase transformation, Rs and Rf were determined for the files tested at 45°. Fractography was studied by SEM.

2.4. Aging Treatment

The files were subjected to heat treatments of 300 and 500 °C for different times: 15, 30, 45, 60, 90 and 120 min and after the files were quenched in water at a temperature of 25 °C. Six files of each system were treated at the different temperatures and times, and the transformation temperatures Ms and Af were studied for all the samples and Rs and Rf were studied for the Reciproc and M-wire.

2.5. Preparation of the Samples for the Observation by Transmission Electron Microscopy (TEM)

The process of focused ion beam (FIB) cutting was carried out using a CrossBeam (1560XB, Carl Zeiss, Berlin, Germany). A 1 μm thick platinum strip was deposited on the top of the area of interest to protect the surface from ion beam induced damage and unwanted milling during sample preparation. Two trenches were cut by using the Ga FIB (first at a current of 10 nA and finally at 2 nA), one from each side, leaving behind a thin electron-transparent lamella supported by bulk material on two opposite sides. The specimen was attached to the micromanipulator tip via platinum deposition. After that, the lamella was removed from its trench. Further FIB thinning at a lower beam current (first 500 pA, then 200 pA, 100 pA and finally 50 pA) was performed on both sides of the wall, leading to a final membrane thickness of 50–100 nm. Finally, the lamella was transferred to a TEM grid and attached by depositing a platinum layer. TEM used was (JEOL, F1400, Tokyo, Japan) using 120 KV.

2.6. Statistical Analysis

The data were statistically analyzed using Student’s t-tests, one-way ANOVA tables and Tukey’s multiple comparison tests in order to evaluate any statistically significant differences between the sample groups. The differences were considered significant when p < 0.01. All statistical analyses were performed with MinitabTM software (Minitab release 13.0, Minitab Inc., State College, PA, USA).

3. Results

The transformation temperatures of the four types of endodontic files are shown in Table 1. In all cases, at oral temperature, the files present for the Protaper and F6 cases a single peak showing the transformation of the austenitic to martensitic phase. However, in the thermograms of the Reciproc and M-wire files there is a double peak corresponding to the appearance of the R-phase in these files. Figure 3 shows the thermograms of Protaper and F6, and Figure 4 shows the thermograms of the endodontic files corresponding to Reciproc and M-wire. The transformation temperatures are shown in Table 1.
The results of the number of cycles to fracture for each type of file at different angles of use can be observed in Figure 5. For each angle we can observe statistically significant differences between the values of Protaper and F6 with respect to the endodontic files containing R-Phase. Reciproc and M-wire values were p < 0.01.
It can be observed for all the files that the number of cycles decreases as the degree of inclination of the endodontic file increases. This fact is due to the higher bending moment of the file. Likewise, it can be seen how the number of cycles of the Reciproc and M-wire files that present the R-phase fracture at a higher number of cycles than the Protaper and F6 files that do not present the R-phase in their microstructure.
Calorimetric studies were carried out at different cycles of the different milling files to determine the transformation temperatures at the beginning of the martensitic transformation (Ms) and the temperature at the end of the retransformation to austenite (Af), which indicates how easy it is to cause the appearance of martensite and the temperature necessary to cause the return to the austenitic phase. For the Reciproc and M-wire files, the transformation temperatures for the initiation of the transformation from austenite to R-phase were determined, as well as those for the retransformation from the R-phase to the fully austenitic structure. Figure 6 corresponds to the Ms and Af temperatures for the files without the R-phase and Figure 7 for the samples showing the intermediate transformation to the R-phase.
Figure 8 shows the results of the transformation temperatures for the four types of files at a temperature of 300 °C during different dwell times. As can be seen, in no case are significant changes seen in any of the transformation temperatures determined.
Figure 9 shows the transformation temperatures at different times when the aging temperature is 500 °C. In the latter case, it can be seen that the transformation temperatures for the milling cutters with the presence of the R-phase show an increase in transformation temperatures, which means that the formation of the martensitic phase and the transition to the R-phase is favored, and the increases in Af show that it is necessary to further increase the temperature to cause the transformation from martensite to austenite.
It has been observed by Transmission Electron Microscopy the effects of thermal aging treatments for nickel-rich files that produce the appearance of precipitates Ni-rich that causes a variation in the chemical composition of the matrix causing the variation of the properties. The precipitates observed in the R-phase samples for the 50.8 wt.% files can be seen in Figure 10 with an elongated morphology [23,24,25].
Fractography studies were carried out by scanning electron microcopy on the endodontic files and in all cases the fractures due to fatigue were observed. Figure 11 shows the fractography, observing the crack nucleation zone, propagation and ductile fracture.

4. Discussion

The endodontic files studied have very similar dimensions and designs, which will allow us to determine the influence of the R phase on the fatigue behavior at different angles. The chemical compositions for Protaper were 49.5% and for F6 49.7% in weight of nickel. The files with R phase present a higher content of nickel, 50.8 and 50.5 % in weight of nickel for Reciproc and M-wire, respectively. In all cases, the phase present is austenite, which ensures the superelastic behavior of the files. However, the Reciproc and M-wire files have been shown to exhibit the R-phase.
As is well known, at body temperature (37 °C) the endodontic files are in austenitic phase (T > Ms), i.e., they present the possibility to produce stress-induced martensitic transformation. That is, when the endodontic file is flexed in the stress zones, the austenite transforms to stress-induced martensite, which gives it flexibility. If the temperature is lower than the temperature Mf, temperature at which the whole alloy is martensite, the endodontic file will present the shape memory property and can be easily deformed. However, the endodontic file does not have the ability as in the case of austenite to absorb energy for stress-induced martensitic transformation [26,27]. The flexibility of the file is due to the possibility that the martensite plates are oriented in the direction of mechanical stress. These martensite plates can orient themselves and even grow at each other’s expense, with the plates with better crystalline orientation increasing in size with respect to the disfavored ones. This self-accommodation mechanism allows energy absorption and is due to the thermoelasticity of the transformation [28,29].
The experimental results of this study are in agreement with the investigations of Prati et al. [30,31]. These researchers obtained a numerical simulation using the finite element method of the stresses produced in dental canals by NiTi endodontic files. In this work it was observed that the highest stress values were produced in healthy teeth and with a good mineralization, it was observed that the conicity between values of 4 and 6% did not produce statistically significant differences. It was also found that an important factor in the von Mises stress and strain values corresponded to the modulus of elasticity of the files. Therefore, the presence of the R-phase modifying the elastic behavior of the files produces important changes as we have seen in this research. The different designs studied by these authors showed that all files produced a concentration of stresses in the curvature of the root canal area approximately 7 mm from the apex.
As can be seen from the results in Figure 5, the fatigue cycle values of the R-phase files are much higher, with statistically significant differences (p < 0.01) with respect to those without R-phase.
This work validates the finite element study of Santos et al. [32] It can be seen that the endodontic files with the lowest bending values are the microstructures with R-phase. The two-phase structures with austenite and R-phase increase bending and the one that presents higher bending values is when the microstructure presents the austenitic structure. Consequently, the R-phase files are more flexible without affecting their rotational stress behavior. These results obtained by the finite element method are validated with our results where it has been verified that the presence of R phase behaves better in fatigue without loss of bending requirements.
It can be observed in both types of files that the mechanical cycles cause an increase in the transformation temperatures Ms and Af, i.e., the martensite phase increases the stability range. Firstly, the mechanical cycles create lattice defects that have an internal energy associated with them. This energy helps the martensitic transformation in the same way that it has been observed that the fine grain size causes an increase in the Ms temperature due to the energy of the grain boundary [33,34]. The explanation for the temperature Af is due to the anchoring of the martensite plates in the defects produced by the mechanical cycles. The plates are stabilized in the defects and an increase in heating temperatures is necessary to unblock the plates and allow them to re-transform to the austenitic phase. Sometimes, heating is not sufficient to return to the austenitic phase due to the stability of the martensite. When this happens, we can only return to austenite by increasing the temperature to the austenization values of the equilibrium diagram above 850 °C [35]. Stressing the material with stabilized martensite will cause it to break, as it has no more energy absorption mechanisms. After the elastic behavior of the martensite, its orientation and the coalescence of plates, NiTi fractures. It can also be seen that in the Reciproc and M-wire files the temperatures Rs and Rf do not vary as much as Ms and Af due to the low energy dispersion in the R-transition [36,37,38,39]. This can be corroborated by the small hysteresis of the R-transitions observed in the calorimetry compared to the B19’ transformations. The same effect has been reported for the stress-induced transformations in the pseudoelastic curves obtained.
NiTi ageing processes occur in Ni-rich alloys, forming coherent Ni4Ti3 precipitates that cause the nickel content of the matrix phase to decrease, leading to concentration gradients around the precipitates [40,41,42]. The decrease of nickel increases the transformation temperatures Rs. In the same way, the formation of the precipitates generates a deformation field generated by the coherent precipitates that favor the formation of the R-phase. However, it is the role of the chemical composition gradient that most strongly affects the increase of the transformation temperatures Rs.
From Figure 9, it can be seen that for the 4 files studied for ageing at 300 °C, no changes can be observed in the transformation temperatures and, therefore, there is no formation of precipitates. However, it can be seen that at a temperature of 500 °C, in the files rich in nickel content, which are those with R phase, there is an increase in the Rs and Rf temperatures, which indicates the appearance of precipitates. As the treatment time increases, the number of precipitates increases and therefore the nickel impoverishment in the provoke matrix increases by almost 20 °C in the Rs temperature for times from 120 °C to a temperature of 500 °C. Some authors describe that precipitates can appear from treatments as low as 250 °C, with very fine and coherent precipitates appearing. However, possible changes in transformation temperatures occur at longer residence times (50 h), and here we have only studied a time period of up to 2 h [43,44].
As is well known, in general, endodontic files do not exceed temperatures of 130 °C due to autoclave sterilization processes. In some cases, it has been possible to exceed these values in the mouth, but they are punctual cases due to unusual friction, but they last a very short time. In this research, we wanted to see the limits of the aging of NiTi alloys used in endodontics and to demonstrate that there is no possible change of properties with the usual temperatures in the use of endodontic files. However, sometimes, some orthodontists and endodontists perform thermal annealing treatments to eliminate dislocations and stabilize martensite plates that impair the superelastic behavior of wires or files. These are heat treatments, where temperatures can range from 500 to 800 °C, that usually last about 15 min and require the subsequent quenching in water [44,45]. In these cases, these treatments must be taken into account.
One of the aspects to take into consideration is that during the mechanical and chemical preparation of root canals with rotary endodontic files, an accidental extrusion of debris beyond the apex can occur. The term flare-up is commonly used to indicate a clinical condition in which pain and swelling of the oral mucosa and soft facial tissues are observed following root canal therapy of a dental element. The work of Villani et al. [46] found that the apical extrusion of debris occurs both with the reciprocating technique with continuously rotating instruments. The association between mucosal inflammation and pain and debris extrusion during the shaping phase needs to be demonstrated with in vivo clinical investigations.
One of the limitations of this study is that only rotational and not reciprocating NiTi files have been performed. One of the future studies could be the realization of the same study in this other type of files. One of the aspects that clinicians should take into account in endodontic therapy is the use of files with rotational or reciprocating movement. Nouri et al. [47] found that there is no significant difference in the penetration of root canals as long as they are straight or moderately curved. For more pronounced curvatures, it has been found that reciprocating files tend to perform better but the results are not conclusive. The differences cannot be attributed to the microstructure of the endodontic file but to the stress distribution caused by the reciprocal movement and the better adaptation to the canal reaching the apical forament as well as the better distribution of loads with respect to the axis of rotation (back-and-forth rotation) [48].
Fractography shows that it is produced by fatigue-torsion as usual in endodontic files, observing that the final part of the fracture is ductile, which indicates a good toughness of the material. No brittle fracture was observed in any area of the fracture surface. Undoubtedly, the presence of precipitates will cause a change in the fracture behavior of the file, decreasing the ductility. Another factor to be taken into account in the behavior of NiTi endodontic files is the physicochemical properties of the surface as well as the variation of the microstructures due to the effect of heat treatments. This aspect was studied by Azizi et al. [49] where they compared conventional (OShape) and heat-treated (OCurve) NiTi endodontic files. The results illustrated that heat treatments increase the fatigue life (p < 0.05) compared to conventional ones. The authors point out that the formation of a TiO2 layer causes compressive states on the surface and causes a delay in crack nucleation. Another interesting aspect is the influence of the sterilization process where the autoclave causes an increase of martensite in the heat-treated files. The results of the studies of Azizi at al. [49] conclude that heat treatments improve the mechanical behavior of the files as well as a better adaptation to the root canal and have opened a field of research for the optimization of heat treatments in order to obtain more flexible files with better mechanical behavior in the long term.

5. Conclusions

Increased insertion angles in canals reduce the service time of endodontic files. NiTi files with R-phase presence improve the durability of the files due to the additional transformation from B2 to R-phase and from R-phase to B19’. This increase in absorbed energy (toughness) leads to better fatigue behavior of R-phase files. Clinicians should note that mechanical cycling affects the properties of the files by increasing the transformation temperatures Ms and Af which favors transformation as well as hinders retransformation. For files with the presence of R phase, it has been found that the temperatures Rs and Rf increase less significantly due to the small hysteresis of the transition to the R phase. The aging processes only affect NiTi files when heat treatments are performed at 500 °C due to the appearance of Ni4Ti3 precipitates for the alloys presenting R transition because they are nickel-rich alloys. Therefore, clinicians should avoid annealing heat treatments to improve superelasticity above 500 °C as NiTi file loses properties. These results can help clinicians understand its properties and improve the use of endodontic files.

Author Contributions

Conceptualization, P.S., B.V., J.M.-A. and C.R.; methodology, J.G., P.S., C.R. and J.M.A.; software, J.G.; validation, B.V. and P.S.; formal analysis, J.M.A. and J.M.-A.; investigation, C.R., P.S., B.V. and J.G.; resources, J.M.A. and J.G.; data curation, J.M.-A. and P.S.; writing—original draft preparation, C.R. and J.G.; writing—review and editing, J.G.; visualization, J.M.A.; supervision, J.G.; project administration, J.M.A. and P.S.; funding acquisition, P.S. and J.M.A. All authors have read and agreed to the published version of the manuscript.

Funding

This research received no external funding.

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

The authors can provide details of the research upon request by letter and commenting on their needs.

Acknowledgments

The authors are grateful to the Universidad Alfonso X el sabio y el Banco de Santander for the administrative and technical support and research project MINECO (PID2022-137496OB-I00).

Conflicts of Interest

The authors declare no conflicts of interest.

References

  1. Huang, X.; Liu, Y. Effect of annealing on the transformation behavior and superelasticity of NiTi shape memory alloy. Scr. Mater. 2001, 45, 153–160. [Google Scholar] [CrossRef]
  2. Urbina, C.; de la Flor, S.; Ferrando, F. R-phase transformation in NiTi alloys. Mater. Sci. Eng. A 2009, A501, 197–206. [Google Scholar] [CrossRef]
  3. Urbina, C.; de la Flor, S.; Ferrando, F. R-phase influence on different two-way shape memory training methods in NiTi shape memory alloys. J. Alloys Compd. 2010, 490, 499–507. [Google Scholar] [CrossRef]
  4. Kim, J.I.; Miyazaki, S. Effect of nano-scaled precipitates on shape memory behavior of Ti-50.9 at.% Ni alloy. Acta Mater. 2005, 53, 4545–4554. [Google Scholar] [CrossRef]
  5. Van Humbeeck, J. Shape memory alloys: A material and a technology. Adv. Eng. Mater. 2001, 3, 837–850. [Google Scholar] [CrossRef]
  6. Duerig, T.W.; Melton, K.N.; Stöckel, D.W. Engineering Aspects of Shape Memory Alloys; Duering, T.W., Ed.; Butterworth-Heinemann: London, UK, 2013; pp. 22–33. [Google Scholar]
  7. Zhang, X.; Song, J.; Huang, C.; Xia, B.; Chen, B.; Sun, X.; Xie, C. Microstructures evolution and phase transformation behaviors of Ni-rich TiNi shape memory alloys after equal channel angular extrusion. J. Alloys Comp. 2011, 509, 3006–3012. [Google Scholar] [CrossRef]
  8. Srivastava, A.K.; Schryvers, D.; Van Humbeeck, J. Grain growth and precipitation in an annealed cold-rolled Ni50.2Ti49.8 alloy. Intermetallics 2007, 15, 1538–1547. [Google Scholar] [CrossRef]
  9. Zheng, Y.; Jiang, F.; Li, L.; Yang, H.; Liu, Y. Effect of ageing treatment on the transformation behaviour of Ti–50.9 at.% Ni alloy. Acta Mater. 2008, 56, 736–745. [Google Scholar] [CrossRef]
  10. Tomozawa, M.; Kim, H.Y.; Miyazaki, S. Microactuators using R-phase transformation of sputter-deposited Ti-47.3 Ni shape memory alloy thin films. J. Intell. Mater. Syst. Struct. 2006, 17, 1049–1058. [Google Scholar] [CrossRef]
  11. Hughes, J.L. Evaluation of Nitinol for Use as a Material in the Construction of Orthopaedic Implants; DAMD 17-74-C-4041; US Army Medical Research and Development Command: Frederick, MD, USA, 1997; pp. 306–315. [Google Scholar]
  12. Miura, F.; Mogi, M.; Ohura, Y.; Hamanaka, H. The super-elastic property of the Japanese NiTi alloy wire for use in orthodontics. Am. J. Orthod. Dentofac. Orthop. 1986, 90, 1–10. [Google Scholar] [CrossRef]
  13. Gil, F.X.; Manero, J.M.; Planell, J.A. Relevant aspects in the clinical applications of NiTi shape memory alloys. J. Mater. Sci. Mater. Med. 1996, 7, 403–406. [Google Scholar] [CrossRef]
  14. Shen, Y.; Qian, W.; Abtin, H.; Gao, Y.; Haapasalo, M. Fatigue Testing of Controlled Memory Wire Nickel-Titanium Rotary Instruments. J. Endod. 2011, 37, 997–1001. [Google Scholar] [CrossRef] [PubMed]
  15. Saber, S.E.D.M.; Nagy, M.M.; Schafer, E. Comparative evaluation of the shaping ability of ProTaper Next, iRaCe and Hyflex CM rotary NiTi files in severely curved root canals. Int. Endod. J. 2015, 48, 131–136. [Google Scholar] [CrossRef]
  16. Gil, F.X.; Rodríguez, D.; Planell, J.A. Grain growth kinetics of pure titanium. Scr. Met. Mat. 1995, 33, 1361–1366. [Google Scholar] [CrossRef]
  17. Arciniegas, M.; Aparicio, C.; Manero, J.M.; Gil, F.J. Low elastic modulus metals for joint prosthesis: Tantalum and nickel–titanium foams. J. Eur. Ceram. Soc. 2007, 27, 3391–3398. [Google Scholar] [CrossRef]
  18. Gil, F.J.; Fernández, E.; Manero, J.M.; Planell, J.A.; Sabrià, J.; Cortada, M.; Giner, L. A study of load cycling in a NiTi alloy with superelastic behaviour used in dental prosthetic fixators. Biomed. Mat. Eng. 1996, 6, 153–158. [Google Scholar]
  19. Sánchez, P.; Vidi, B.; Mena-Alvarez, J.; Gil, J.; Rico, C.; Aragoneses, J.M. Effect of Stabilized Martensite on the Long-Term Performance of Superelastic NiTi Endodontic Files. Materials 2023, 16, 4089. [Google Scholar] [CrossRef] [PubMed]
  20. Gil, F.J.; Planell, J.A. Thermal cycling and ageing effects in NiTi shape memory alloys used in biomedical applications. J. Biomech. 1998, 1001, 135. [Google Scholar]
  21. Duerig, T.W.; Bhattacharya, K. The influence of the R-phase on the superelastic behavior of NiTi. Shape Mem. Superelasticity 2015, 1, 153–161. [Google Scholar] [CrossRef]
  22. Martins, J.N.R.; Silva, E.J.N.L.; Marques, D.; Belladonna, F.; Simões-Carvalho, M.; Vieira, V.T.L.; Antunes, H.S.; Fernandes, F.M.B.; Versiani, M.A. Design, metallurgical features, mechanical performance and canal preparation of six reciprocating instruments. Int. Endod. J. 2021, 54, 1623–1637. [Google Scholar] [CrossRef]
  23. Wang, X.; Li, K.; Schryvers, D.; Verlinden, B.; Van Humbeeck, J. R-phase transition and related mechanical properties controlled by low-temperature aging treatment in a Ti–50.8 at. % Ni thin wire. Scr. Mate. 2014, 72, 21–24. [Google Scholar] [CrossRef]
  24. Olbricht, J.; Yawny, A.; Pelegrina, J.L.; Eggeler, G.; Yardley, V.A. Characteristics of the stress-induced formation of R-phase in ultrafine-grained NiTi shape memory wire. J. All.Comp. 2013, 579, 249–252. [Google Scholar] [CrossRef]
  25. Tirry, W.; Schryvers, D. Quantitative determination of strain fields around Ni4Ti3 precipitates in NiTi. Acta Mater. 2005, 53, 1041–1049. [Google Scholar] [CrossRef]
  26. Arciniegas, M.; Casals, J.; Manero, J.M.; Peña, J.; Gil, F.J. Study of hardness and wear behaviour of NiTi shape memory alloys. J. Alloys Compd. 2008, 460, 213–219. [Google Scholar] [CrossRef]
  27. Godoy-Gallardo, M.; Manzanares-Céspedes, M.C.; Sevilla, P.; Nart, J.; Manzanares, N.; Manero, J.M.; Gil, F.J.; Boyd, S.K.; Rodríguez, D. Evaluation of bone loss in antibacterial coated dental implants: An experimental study in dogs. Mater. Sci. Eng. C Mater. Biol. Appl. 2016, 69, 538–545. [Google Scholar] [CrossRef] [PubMed]
  28. Rodrigues, C.T.; Duarte, M.A.H.; de Almeida, M.M.; de Andrade, F.B.; Bernardineli, N. Efficacy of CM-Wire, M-Wire, and Nickel-Titanium Instruments for Removing Filling Material from Curved Root Canals: A Micro–Computed Tomography Study. J. Endod. 2016, 42, 1651–1655. [Google Scholar] [CrossRef] [PubMed]
  29. Pereira, E.S.; Peixoto, I.F.; Viana, A.C. Physical and mechanical properties of a thermomechanically treated NiTi wire used in the manufacture of rotary endodontic instruments. Int. Endod. J. 2012, 45, 469–474. [Google Scholar] [CrossRef] [PubMed]
  30. Prati, C.; Foschi, F.; Nucci, C.; Montebugnoli, L.; Marchionni, S. Appearance of the root canal walls after preparation with NiTi rotary instruments: A comparative SEM investigation. Clin. Oral Investig. 2004, 8, 102–110. [Google Scholar] [CrossRef] [PubMed]
  31. Prati, C.; Tribst, J.P.M.; Dal Piva, A.M.d.O.; Borges, A.L.S.; Ventre, M.; Zamparini, F.; Ausiello, P. 3D Finite Element Analysis of Rotary Instruments in Root Canal Dentine with Different Elastic Moduli. Appl. Sci. 2021, 11, 2547. [Google Scholar] [CrossRef]
  32. Santos Lde, A.; Resende, P.D.; Bahia, M.G.; Buono, V.T. Effects of R-Phase on Mechanical Responses of a Nickel-Titanium Endodontic Instrument: Structural Characterization and Finite Element Analysis. Sci. World J. 2016, 2016, 7617493. [Google Scholar] [CrossRef]
  33. Godoy-Gallardo, M.; Guillem-Marti, J.; Sevilla, P.; Manero, J.M.; Gil, F.J.; Rodriguez, D. Anhydride-functional silane immobilized onto titanium surfaces induces osteoblast cell differentiation and reduces bacterial adhesion and biofilm formation. Mater. Sci. Eng. C Mater. Biol. Appl. 2016, 59, 524–532. [Google Scholar] [CrossRef] [PubMed]
  34. Manero, J.M.; Gil, F.J.; Padrós, E.; Planell, J.A. Applications of environmental scanning electron microscopy (ESEM) in biomaterials field. Microsc. Res. Tech. 2003, 61, 469–480. [Google Scholar] [CrossRef] [PubMed]
  35. Goo, E.; Sinclair, R. The B2 to R transformation in Ti50Ni47Fe3 and Ti49.5Ni50.5 alloys. Acta Metall. 1985, 33, 1717–1723. [Google Scholar] [CrossRef]
  36. Olbricht, J.; Yawny, A.; Pelegrina, J.L.; Dlouhy, A.; Eggeler, G. On the stress-induced formation of R-phase in ultra-fine-grained Ni-rich NiTi shape memory alloys. Metall. Mater. Trans. A 2011, 42, 2556–2574. [Google Scholar] [CrossRef]
  37. Kim, J.I.; Liu, Y.; Miyazaki, S. Ageing-induced two-stage R-phase transformation in Ti–50.9 at. % Ni. Acta Mater. 2004, 52, 487–499. [Google Scholar] [CrossRef]
  38. Wu, S.K.; Lin, H.C.; Yen, Y.C.; Chen, J.C. Wire drawing conducted in the R-phase of TiNi shape memory alloys. Mater. Lett. 2000, 46, 175–180. [Google Scholar] [CrossRef]
  39. Van Humbeeck, J.; Kustov, S. Active and passive damping of noise and vibrations through shape memory alloys: Applications and mechanisms. Smart Mater. Struct. 2015, 14, S171. [Google Scholar] [CrossRef]
  40. Schryvers, D.; Tirry, W.; Yang, Z.Q. Measuring strain fields and concentration gradients around Ni4Ti3 precipitates. Mater. Sci. Eng. A 2006, 438, 485–488. [Google Scholar] [CrossRef]
  41. Zhiqing, Y.; Schryvers, D. Study of changes in composition and EELS ionization edges upon Ni4Ti3 precipitation in a NiTi alloy. Micron 2006, 37, 503–507. [Google Scholar]
  42. Wang, X.B.; Amin Ahmadi, B.; Schryvers, D.; Verlinden, B.; Van Humbeeck, J. Effect of annealing on the transformation behavior and mechanical properties of two nanostructured Ti-50.8 at. % Ni thin wires produced by different methods. Mater. Sci. Forum 2013, 738, 306–310. [Google Scholar]
  43. Espinar, E.; Llamas, J.M.; Michiardi, A.; Ginebra, M.P.; Gil, F.J. Reduction of Ni release and improvement of the friction behaviour of NiTi orthodontic archwires by oxidation treatments. J. Mater. Sci. Mater. Med. 2011, 22, 1119–1125. [Google Scholar] [CrossRef] [PubMed]
  44. Briceño, J.; Romeu, A.; Espinar, E.; Llamas, J.M.; Gil, F.J. Influence of the microstructure on electrochemical corrosion and nickel release in NiTi orthodontic archwires. Mater. Sci. Eng. C Mater. Biol. Appl. 2013, 33, 4989–4993. [Google Scholar] [CrossRef] [PubMed]
  45. Gil, F.J.; Solano, E.; Peña, J.; Engel, E.; Mendoza, A.; Planell, J.A. Microstructural, mechanical and citotoxicity evaluation of different NiTi and NiTiCu shape memory alloys. J. Mater. Sci. Mater. Med. 2004, 15, 1181–1185. [Google Scholar] [CrossRef] [PubMed]
  46. Villani, F.A.; Zamparini, F.; Spinelli, A.; Aiuto, R.; Prati, C. Apical debris extrusion and potential risk of endodontic flare-up: Correlation with rotating and reciprocating instruments used in daily clinical practice. Guárnale Ital. Endod. 2024, 38, 301–310. [Google Scholar]
  47. Nouri, H.; Amini, K.; Jahromi, M.Z. Comparison of full rotation and reciprocating movements in regaining apical patency during endodontic retreatment. Dent. Res. J. 2021, 18, 85. [Google Scholar]
  48. Berutti, E.; Paolino, D.S.; Chiandussi, G.; Alovisi, M.; Cantatore, G.; Castellucci, A. Root canal anatomy preservation of WaveOne reciprocating files with or without glide path. J. Endod. 2012, 38, 101–104. [Google Scholar] [CrossRef]
  49. Azizi, A.; Prati, C.; Schiavon, R.; Fitzgibbon, R.M.; Pirani, C.; Iacono, F.; Pelliccioni, G.A.; Spinelli, A.; Zamparini, F.; Puddu, P.; et al. In-Depth Metallurgical and Microstructural Analysis of Oneshape and Heat Treated Onecurve Instruments. Eur. Endod. J. 2021, 6, 90–97. [Google Scholar] [CrossRef]
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Figure 1. Different NiTi endodontic files studied. Reciproc and M wire present R-phase.
Figure 1. Different NiTi endodontic files studied. Reciproc and M wire present R-phase.
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Figure 2. Scheme of the different molds for endodontics tests. The 30°, 45° and 70° angles were used, which are common angles in clinical practice [21].
Figure 2. Scheme of the different molds for endodontics tests. The 30°, 45° and 70° angles were used, which are common angles in clinical practice [21].
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Figure 3. Thermograms of F6 and Protaper endodontic files (heating and cooling cycles). Three different samples studied for each type of files.
Figure 3. Thermograms of F6 and Protaper endodontic files (heating and cooling cycles). Three different samples studied for each type of files.
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Figure 4. Thermograms of M-wire and Reciproc endodontic files (heating and cooling cycles). Three different samples studied for each type of files. In the thermograms the peaks of R-phase are identified.
Figure 4. Thermograms of M-wire and Reciproc endodontic files (heating and cooling cycles). Three different samples studied for each type of files. In the thermograms the peaks of R-phase are identified.
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Figure 5. Number of cycles to fracture for different types of files and different angles. Letters signify statistically significant differences with a p < 0.01 with respect to the number of cycles to fracture. When the letters are equal there are no statistically significant differences between them. If the letters are different, it means that there are statistically significant differences with a p < 0.01.
Figure 5. Number of cycles to fracture for different types of files and different angles. Letters signify statistically significant differences with a p < 0.01 with respect to the number of cycles to fracture. When the letters are equal there are no statistically significant differences between them. If the letters are different, it means that there are statistically significant differences with a p < 0.01.
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Figure 6. Ms and Af transformation temperatures at different number of cycles for test realized at 45° with Protaper and F6 files.
Figure 6. Ms and Af transformation temperatures at different number of cycles for test realized at 45° with Protaper and F6 files.
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Figure 7. Ms and Af transformation temperatures and Rs and Rf for the R transition at different number of cycles for test realized at 45° with Reciproc and M-wire files.
Figure 7. Ms and Af transformation temperatures and Rs and Rf for the R transition at different number of cycles for test realized at 45° with Reciproc and M-wire files.
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Figure 8. Transformation temperatures for each type of file treated at 300 °C for different times.
Figure 8. Transformation temperatures for each type of file treated at 300 °C for different times.
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Figure 9. Transformation temperatures for each type of file treated at 500 °C for different times.
Figure 9. Transformation temperatures for each type of file treated at 500 °C for different times.
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Figure 10. Precipitates observed by Transmission Electron Microscope produced by aging in Ni-rich samples.
Figure 10. Precipitates observed by Transmission Electron Microscope produced by aging in Ni-rich samples.
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Figure 11. Fractography of the NiTi endodontic file. In this case, it corresponds to the M-wire.
Figure 11. Fractography of the NiTi endodontic file. In this case, it corresponds to the M-wire.
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Table 1. Transformation and retransformation temperatures in °C for different endodontic files.
Table 1. Transformation and retransformation temperatures in °C for different endodontic files.
Endodontic FileMsMfAsAfRsRf
Protaper24 ± 315 ± 13 ± 434 ± 3--
F622 ± 412 ± 2−4 ± 330 ± 2--
Reciproc 36 ± 535 ± 325 ± 540 ± 720 ± 229 ± 4
M-wire25 ± 422 ± 215 ± 429 ± 610 ± 318 ± 3
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Sánchez, P.; Vidi, B.; Rico, C.; Mena-Alvarez, J.; Gil, J.; Aragoneses, J.M. Relevant Aspects in the Mechanical and Aging Degradation of NiTi Alloy with R-Phase in Endodontic Files. Materials 2024, 17, 3351. https://doi.org/10.3390/ma17133351

AMA Style

Sánchez P, Vidi B, Rico C, Mena-Alvarez J, Gil J, Aragoneses JM. Relevant Aspects in the Mechanical and Aging Degradation of NiTi Alloy with R-Phase in Endodontic Files. Materials. 2024; 17(13):3351. https://doi.org/10.3390/ma17133351

Chicago/Turabian Style

Sánchez, Patricia, Benedetta Vidi, Cristina Rico, Jesús Mena-Alvarez, Javier Gil, and Juan Manuel Aragoneses. 2024. "Relevant Aspects in the Mechanical and Aging Degradation of NiTi Alloy with R-Phase in Endodontic Files" Materials 17, no. 13: 3351. https://doi.org/10.3390/ma17133351

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