Dental alloys have been used in dentistry for prosthetic rehabilitation for hundred years.1 Precious or alternative alloys are still in use for metallic structures of fixed dental prosthesis. However, the use of precious alloys is limited because of their high costs, and for this reason, non-precious dental alloys have been introduced to the dental field.2 Currently, the most used non-precious metallic alloys are cobalt-chromium (Co-Cr) and nickel-chromium (Ni-Cr), as their hardness, elasticity modulus, and tensile strength are suitable for metal ceramic restorations.3 However, the European Union and ADA have proposed to retire alloys containing nickel because of the possible allergic interaction of nickel with humans.4 Therefore, recently, the widespread use of Co-Cr alloys has been seen in the dental field.

Conventional casting method is the most frequently used technique for manufacturing Co-Cr alloy fixed dental prostheses. In recent years, modern computer-aided technologies for manufacturing individual prostheses have been gaining popularity in the field of dental technology.5 Computer-aided design (CAD) and computer-aided manufacturing (CAM) technologies are used frequently in the dental field to fabricate prostheses ranging from crowns to long-span fixed dental prosthesis and from removable prostheses to dental implants.6 The term CAD/CAM implies that the system can be used both for designing a product and for controlling the manufacturing process.7 The actual fabrication of a Co-Cr product is carried out by computer numerical control (CNC) milling machines or direct metal laser sintering (DMLS) machines.8,9 These systems were developed to address a number of disadvantages of the traditional casting method like human induced errors, production cost and dimensional stability.10,11

The microstructure of metal alloys is strongly influenced by the manufacturing process.12 Moreover, the quality of a material and thus the clinical chances of success are directly affected by controlling the manufacturing environment.13-15 New manufacturing processes such as metal injection molding and powder-metallurgical techniques are being developed to achieve dental alloys with better microstructure and mechanical properties.10,16 With the industrial production of Co-Cr in the form of blanks, increasingly homogeneous metal structures can be obtained. These blanks have been used in CNC milling machines for manufacturing crowns, long-span fixed dental prosthesis and other prosthetic devices.2 In dentistry, manufacturing techniques such as casting and CNC milling methods are well known to dentists and dental technicians. Only recently, the DMLS technique has started gaining attention in this field. However, the manufacturing stages of this technique and factors that affect product quality are not well known.

Sintering is a method used to create objects from powders. The effects of sintering are based on atomic diffusion, which occurs much faster at higher temperatures.17 During sintering, the atoms in powder particles diffuse across particle boundaries; this fuses the particles together to create a single solid piece.18 DMLS is an additive metal fabrication technology that involves the use of a high-powered Ytterbium (Yb)-fiber optic laser.19 In this technology, metal powder is melted locally with a focused laser beam and fused into a solid part. The parts are built up additively, layer by layer, each of which is 10-30 µm thick.20 When compared to casting technique, DMLS technology affords highly accurate production of materials with higher surface quality and increased mechanical properties.11,21

When metal alloys are manufactured with sintering techniques, a heat treatment process called "annealing" is used to advance the material toward its equilibrium state.22 The procedure for annealing an object involves heating it above the critical temperature, maintaining it at a stable temperature, and then cooling it down.23,24 The most important aims of annealing are to increase ductility of an object, accelerate relief of internal stresses, soften material, and refine the structure by making it homogeneous.9,22,23 After manufacturing Co-Cr prosthetic sub structures by using the DMLS technique, annealing is required to obtain homogeneous metallic structures.9,20 However, changes in temperature, atmosphere, or both of them during the annealing process affect the microstructure and hardness of the alloy.24

Many techniques are available for evaluating the structural characteristics of metal alloys. Small angle X-ray scattering (SAXS) is one such technique used for the structural characterization of solid and fluid materials in the nanometer (nm) range. Measurements are commonly performed in transmission geometry by using a narrow, well-collimated, and intense X-ray beam. Some typical applications comprise the determination of nanoparticle and pore size distributions of specific surface areas and the structural analysis in inhomogeneous particles. Further, the technique may yield information about the aggregation behavior of nanoparticles.25 Detailed information about the nanostructure of metallic materials, such as the analyses of fractal dimensions, distance distribution function, and fitting function, may be obtained by using data from SAXS analysis. In the analysis of fractal dimension, the mass fractals are examined and information about the structural formation of the solid object is obtained. The analysis of the distance distribution function yields the distribution of particle dimensions or of the inter-particle distances. The obtained data indicate the structural homogeneity of the object.26 SAXS profiles for nanosized surface aggregates can be modeled by an intensity equation defined by the addition of scattering intensity functions related to cylindrical and lamellar aggregations [I(q) = I₁(q) + I₂(q)] with a software program (IGOR Pro 1998-2008 WaveMetrics). The cylindrical and lamellar functions are used in the fitting procedure; thus, detailed information about the length of the cylinders and the thickness of the layers in the structural formation of the object may be obtained.25,26

The aim of this study was to compare the nanostructures and hardness of Co-Cr dental alloys manufactured with different techniques and to find the effect of annealing conditions to the alloys that was produced with DMLS method.

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Five groups of Co-Cr dental alloy samples were manufactured in a rectangular form measuring 4 mm × 2 mm × 2 mm. In Group I, conventional Co-Cr (Remanium® 2000+, Dentaurum, Pforzheim, Germany) samples were manufactured by the lost wax technique in an induction-casting machine (Fornax GEU, Bego, Bremen, Germany). After modeling with green inlay casting wax (n=15) (Bego, Bremen, Germany), specimens were sprued and invested in phosphate-bonded investment (Bellavest SH, Bego, Bremen, Germany). After the final setting of the investment, each ring was put into a furnace (Miditherm MP, Bego, Bremen, Germany) to evaporate the wax material. Casting was accomplished according to the manufacturer's instructions. After cooling at room temperature, the samples were cleaned and sandblasted by airborne abrasion with 250 µm Al₂O₃ particles. The samples in Group II were obtained from the center of a prefabricated Co-Cr milling blank (Remanium® star milling blank, Dentaurum, Pforzheim, Germany) manually by using a diamond bur under water-cooling (n=15). The surfaces of the samples were finished with 400 grit sandpaper (CarbiMet 2 Paper Discs, Buehler, Lake Bluff, IL, USA) and sandblasted by airborne abrasion with 250 µm Al₂O₃ particles.

The samples in Groups III, IV, and V were manufactured with a DMLS machine (M2 Cusing, ConceptLaser GmBH, Lichtenfels, Germany) after 3D CAD (n=15 for each group). For laser-aided production of samples, Co-Cr nanopowder (Remanium® star CL, Dentaurum, Pforzheim, Germany) was used. After production, the samples were randomly divided into 3 groups (Groups III, IV, and V). In Group III, the samples were only sandblasted by airborne abrasion with 250 µm Al₂O₃ particles after manufacturing. In Group IV, the samples were annealed in argon atmosphere (XD 1600A, Zhengzhou Brother Furnace, Co., Ltd, Henan, China) under controlled temperature according to the manufacturer's instructions. During annealing, the samples were heated to 1150℃ over the course of 173 minutes, stabilized at this temperature for 232 minutes, cooled to 300℃ in 593 minutes, removed from the furnace, and left to cool at room temperature. In Group V, the samples were annealed in atmospheric oxygen condition (XD 1600A, Zhengzhou Brother Furnace, Co., Ltd, Henan, Chinaunder) the same controlled annealing process with Group IV. In both Groups IV and V, all samples were sandblasted by airborne abrasion with 250 µm Al₂O₃ particles after annealing.

The nanostructure was examined with the SAXS method by using a HECUS-SAXS system3 (Hecus X-ray systems, Brucker Austria GmbH, Graz, Austria) with CuKα (λ = 1.54 Å) radiation operated at 50 kV and 50 mA, line collimation, and position sensitive detectors (~54 µm resolution, 1024 channels). SAXS measurements were performed at room temperature in a 600 second time interval. Analyses of fractal dimension, distance distribution function, and fitting function were performed according to the SAXS measurements. In analyses of fractal dimension, logarithmic plots were prepared for the samples and fitted to Equation 1 to analyze the fractal structure with spherical fractal units. Equation 1 is well known scattering intensity function for densed/fractal nanostructured systems25 and can be written as follows:

In the formulation P(q) is including information about; number of particles per unit volume (ø), volume of particle (V_p), electron density (Δρ) and form factor ([F(qR_g²)]²), F(x) is the globular form of the nanoaggregations and S(q) is the structure function accounting for short range spatial correlated particles. Also, bkgd (or bkg) in the formulation indicates the background scattering density, R_g, ξ, and D_f are size of fractal unit, cluster and maximum sizes of fractal regions, respectively. These structural parameters were also calculated according to the fitted curves of SAXS analyses.

In analyses of distance distribution function, the effective radius of the particles (Rg) and maximum effective size of the nanoparticles (maximum extent) were also calculated according to the fitted curves of SAXS analyses.

The fitting function was used for calculating the radius and length of the cylinders and also the bilayer thickness of the lamellas. Thus, the SAXS data of the samples fit the sum of the cylindrical and lamellar functions. The cylindrical function used in the fitting procedure is expressed as follows.

The form factor of cylindrical particles, P₁(q), is given as follows.

Here, q is the scattering vector; α is the angle between the cylinder axis and the scattering vector; and L, H, r, and V are the length, semi-length, radius, and volume, respectively, of the cylinder. In addition, ø is the particle volume fraction, ρ_cyl is the scattering length density for the cylinder, ρ_solv is the scattering length density for the solvent, and J₁(x) is the Bessel function.

The lamellar function used in the fitting procedure is defined below as

Here, P₂(q), the form factor of lamellar particles, is given by

Here, δ is the bilayer thickness, σ is the polydispersity (alteration in bilayer thickness), q is the scattering vector, Δρ is the scattering contrast, and ρ_bil and ρ_solv are the scattering length densities for the bilayer and solvent, respectively.

The Rockwell hardness (HRC) was measured under 150 kgf/50 s (Time TH3000, Geneq Inc., Montréal, Canada) with a 120° diamond cone and recorded digitally. SPSS software program (SPSS 15.0, SPSS Inc., Chicago, IL, USA) was used to statistically analyze hardness measurements. Descriptive statistics were presented as mean ± standard deviation. One-way analysis of variance (ANOVA) was used for comparisons of continuous variables. Tukey's honestly significant difference (HSD) test was used for post hoc analysis. A P value of less than .05 was accepted as statistically significant.

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The results of the SAXS analysis are as follows; small-angle data were recorded in the q range of 4-500 Å^-1, where q is the magnitude of the scattering vector. SAXS data for the 5 samples are presented in Fig. 1. The accuracy of the obtained structural sizes was in the range of 0.4-1.1 Å.

In the analysis of fractal dimension, as the negative slope (di) of the plots of LnI (q) and Lnq at regions where q is large provides information about the surface characteristics (LnI (q) - Lnq = di), the results indicated that the surface of the samples had small spherical formations. The fractal dimension (D_f) remained invariant in the range 1 < di < 3 across all samples after the fitting procedure (Table 1). As shown in Fig. 2, these values gave the information about the structural formation of the metallic samples.

Table 2 presents the effective radius of the particles (R_g) and the maximum distance between the nanoparticles (maximum extent) in Å, according to the analysis of distance distribution function. According to the minimum electron intensity and particle distance data, the lowest particle distance distribution was determined in Group II and then Groups IV, I, V and III were followed in order. The effect of annealing at argon atmosphere (Group IV) to the particle size and distance of the alloy was obvious than annealing at atmospheric condition (Group V).

Lamellar ordering may occur by slightly ordered cylindrical particles. Therefore, adoption of this model would appear to be appropriate for these types of surface morphologies. Table 3 presents the radius and length of the cylinders as well as the thickness of the layers for all groups of samples after the calculation of cylindrical and lamellar functions that were used for the fitting procedure. While Group IV presented the maximum radius of the cylinders, Groups III, V, I and II followed it by a decrease (Group IV > III > V > I > II). Likewise, Group III presented the maximum length of the cylinders and Groups II, IV, V, I followed it by a decrease (Group III > II > IV > V > I). Also, the bilayer thickness of the lamellas was decreased as follows: Group II > III > V > I > IV.

Mean Rockwell hardness (± SD) measurements, converted to Brinell and Vickers hardness values according to EN ISO 18265-App. G27, and mean tensile strengths are presented in Table 4 for each group. The obtained hardness values of the groups aligned as follows in descending order: Group III > Group I > Group II > Group V > Group IV.

A statistically significant difference was observed between annealed groups (Groups IV and V) for hardness (P<.001) (Fig. 3).

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In dentistry, non-precious alloys are more widely used than precious alloys to manufacture metal sub-structures. Currently, the most commonly used non-precious alloys are nickel-chromium (Ni-Cr) and cobalt-chromium (Co-Cr) alloys.2 However, the biocompatibility of Ni-Cr alloys has been questioned due to the possible damages to the health of patients and professionals in dental laboratories.28,29 Wataha et al.30,31 reported that the stability of Ni-Cr alloys was poor in acidic solutions or in the presence of acidic plaque, which causes the release of Ni. Thus, more biocompatible non-precious dental alloys would be preferable for metal ceramic restorations. Grimaudo3 suggested that Co-Cr alloys were an alternative to Ni-Cr alloys in metal ceramic systems because they are more biocompatible, relatively well tolerated, and do not weaken the physical properties of metal-based porcelain restorations. Indeed, Co-based alloys are extensively used as wear- or corrosion-resistant materials for metal sub-structures in fixed partial dentures.32 Chromium (Cr), molybdenum (Mo), tungsten (W), nickel (Ni), and silicon (Si) are mainly used with Co-based dental alloys.10,32 In particular, Cr is a strong carbide former and provides additional strength as a solute as well as resistance to corrosion and oxidation in the alloy.32 In the present study, dental alloys based on Co-Cr were used to manufacture the samples for all groups.

In addition to the alloy structure, the manufacturing process influences the microstructure of the metal alloys. The wear resistance, mechanical properties, biocompatibility, and corrosion resistance may also be influenced by the microstructure, which depends on the thermal treatment applied to the material.10 In dentistry, Co-Cr alloys with Mo or W can be manufactured by techniques such as casting, milling, and DMLS. In the present study, all of these manufacturing methods were used and compared in terms of the nanostructure and hardness of the resultant samples they produced.

Environmental factors affect the product quality in the casting and DMLS techniques. Bauer et al.13 demonstrated that when noble and basic alloys are cast in an uncontrolled environment, the metals are exposed to deleterious gases and elements, which influence their mechanical properties such as internal porosity. DMLS is a new technology in dentistry for manufacturing Co-Cr metal ceramic substructures, and therefore, the steps of the procedure and the factors that affect product quality are not well known.

In the DMLS technique, Co-Cr nanoparticles fuse by applying Yb-fiber optic laser, and parts are built up layer by layer, each of which is 30 µm thick.33 After completion of the manufacturing with DMLS, brittle and non-homogeneous metal objects are obtained.10,11 For this reason, an annealing process must be applied for strength and homogeneity.34 In the literature, annealing investigations have been performed on noble and semi-noble dental alloys.24,35,36 Guo et al.24 evaluated the effect of annealing on Pd-Ag dental alloys in a nitrogen atmosphere under different temperatures and reported that changes in temperature during annealing affect the microstructure and hardness of the alloy. In this study, the effects of annealing and different atmospheric conditions on Co-Cr dental alloys were tested to evaluate the changes in nanostructure and hardness.

The nanostructure was evaluated by SAXS analysis. The data from this analysis were also used in the analyses of the fractal dimensions, distance distribution function, and fitting function. Fractal dimension analysis gives information about surface characteristics. In the plot of LnI(q) - Lnq, the negative slope gives the value of "di" (Fig. 2). A di value of 4 signifies a nearly flat surface (very little irregularity of surface fractals); that of 3 < di < 4 signifies surface fractals (differently oriented and disjointed planks); and that of 1 < di < 3 signifies mass fractals (small spherical entities that have volumetric mass fractals with covered surfaces). According to the data of the present study, all groups were fit to the mass fractal structure (1 < di < 3) and exhibited a dendritic formation with small spherical entities irregularly stacked upon each other in layers. In literature, this dendritic arrangement is accepted as typical for Co-based dental alloys.10,22 Interdendritic portions or carbide precipitation for Co-Cr alloys may be observed with different analysis techniques.10

Analysis of the distance distribution function provides information about the distances between particles, and the data of this analysis give the information about the homogeneity of the examining material. Comparison of the obtained data (Table II) showed that the effective radius of the particles (Rg) and the inter-particle distance (maximum extent) for Groups I, III, and V were similar to but greater than those for Groups II and IV. Nanostructural differences for the groups are attributed to the different manufacturing techniques. However, the difference between annealed groups (Groups IV and V) may be explained by the atmospheric conditions during annealing. The most homogeneous structure is expected in Group IV, as the manufacturing process accomplished completely.

Moreover, the data of the fitting function presented that all samples in the study displayed cylindrical rods and lamellas. The cylindrical function gives information about the structure of the cylinders of the samples. The radius and length of the cylinders also affect the length of the dendrites. According to the data of the cylindrical functions, Group I exhibited narrow and short cylinders. In Group II, these cylinders were much narrower and taller than those in Group I. Upon comparing the groups manufactured with DMLS, the following could be observed. In Group IV, the cylinders were nearly equal but much shorter than those in Group III; in Group V, the cylinders were narrower than those in Group III and shorter than those in Group IV. The lamellar function gives the information about the distance between the layers. Nomura et al.37 and Telu et al.38 also examined the lamellar formation of Co-Cr alloys by using XRD analysis. Telu et al.38 showed that decreasing the bilayer thickness increased the homogeneity of the alloy. Across groups, the maximum and minimum bilayer thicknesses were observed in Groups I and IV, respectively. The results of the fitting function in the present study show that the most homogeneous group was Group IV. A detailed understanding of the precipitation process that occurs during annealing of these groups will require the use of a transmission electron microscope (TEM).

As mentioned before, the manufacturing conditions affect not only the structure but also the hardness of the alloys. Uncontrolled environments during casting and annealing adversely affect the mechanical properties of the alloy. The primary role of the furnace atmosphere in non-ferrous annealing is to protect the product from excessive oxidation. To ensure this, the oxygen partial pressure of the atmosphere must be less than that necessary to form an oxide layer. In systems at atmospheric pressure, flushing with an inert gas (argon or nitrogen) is sufficient to reduce the oxygen level.34 Mackert et al.39 reported that when a Pd-Ag alloy was annealed in oxygen, hardness variations occurred owing to an increase in the oxidation layer. The hardness comparisons in the present study showed that the argon atmosphere effectively reduced the hardness of Co-Cr alloys [Group IV < Group V]. The maximum hardness was observed in Group III. This suggests that the inner stresses after manufacturing, having caused increased brittleness of the alloy structure, also increased hardness. Under a noble gas atmosphere, the hardness decreases because of the decreased oxidation level. This acquired specification also increases the manipulability of the metal structure. A high quality product usually requires a bright finish, which is well known in an oral environment to reduce bacterial accumulation.40 Thus, the use of an inert atmosphere should be critical for the appearance of the finished product. In a future study, observing the surface quality of metals manufactured with the DMLS technique and annealed in argon will be important. Furthermore, the structural changes and hardness values after porcelain firing cycles under different temperatures and porcelain-metal bonding characteristics of Co-Cr alloys should be investigated.

According to the analysis data and Rockwell hardness measurements, all groups behaved in different ways because of differences in manufacturing. The general nanostructure of the samples was composed of small spherical entities that were stacked atop one another in a dendritic form-a structure that may also be defined as cylindrically shaped clusters that includes spherical units. Although the effective radius of the spherical particles was very similar between the groups, the inter-particle distances differed. In addition, the radius and length of the cylinders as well as the thickness of the layers differed.

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As the manufacturing with DMLS technique is becoming widespread in dentistry, the production steps should be well known. Especially, annealing is an important process in this technique. Increased inter-particle distance and increased bilayer thickness for non-annealed alloys indicate a non-homogeneous form and long dendrites. For the decreased hardness and homogeneity of the Co-Cr metal ceramic substructures annealing in argon atmosphere is essential. Annealing in oxygen relieves the inner stresses but the layers could not get closer and thus the hardness increase. For this reason, it must be well known by the prosthodontist that annealing environment is also important for DMLS manufacturing of the Co-Cr dental alloys.

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