Assessment of the Functional Properties of 316L Steel Alloy Subjected to Ion Implantation Used in Biotribological Systems

Clinical trials conducted in many centres worldwide indicate that, despite advances made in the use of biomaterials for medical applications, tribocorrosive wear remains a significant issue. The release of wear residue into body fluids can cause inflammation and, as a result, implant failure. Surface modification is one of the methods used to improve the mechanical, tribological, and fatigue properties of biomaterials. In this article, the authors investigated the impact of ion implantation on improving the functional properties of implant surfaces. This paper presents morphology, geometric surface structure, hardness, and tribological test results for layers obtained by ion implantation with nitrogen and oxygen ions on alloy 316L. The surface morphology and thickness of the implanted layer were examined using scanning microscopy. Atomic force microscopy was used to evaluate the geometric structure of the surface. Instrumented indentation was used to measure nanohardness. Model tribo tests were carried out for reciprocating motion under conditions of dry friction and lubricated friction with Ringer’s solution. The tribological tests showed that the implanted samples had a lower wear than the reference samples. Nitrogen ion implantation increased the hardness of 316L steel by about 45% and increased it by about 15% when oxygen ions were used.


Introduction
The increase in the number of osteoarticular injuries has intensified research on biotribology and biomaterials [1]. As a result, new materials and advanced surface treatments are being developed and tested with the aim of improving tribological properties, corrosion resistance, and biocompatibility.
Clinical trials conducted worldwide show that corrosive and mechanical wear on the implant surface remains a major issue despite ongoing efforts. The release of metal wear particles into body fluids can lead to metallosis in soft tissues and the formation of pseudotumors [2][3][4]. Inflammatory reactions that develop due to corrosion and metallosis caused by toxic and allergic reactions are due to a change in the body fluid pH resulting from the presence of metal wear debris. Implants remain in constant contact with body fluids, which have a high concentration of chloride ions that are strongly corrosive to metals. The process is intensified by the presence of proteins and amino acids in body fluids. Under normal conditions, body fluids have a pH in the range of 7.35-7.45. Implantation modifies neutral pH, which drops to about 5.2 and returns to normal after approximately 14 days [5,6].
Metals and alloys used in implantation should have a good corrosion resistance, biotolerance (non-toxicity), an appropriate chemical composition, a fine-particle structure, high strength, no tendency to form clots, and easy mechanical processing [7][8][9][10]. The most commonly used implant materials are alloyed steels characterized by excellent strength parameters, a high biocompatibility allowing implant-bone osseointegration, a structure that ensures high corrosion resistance, and very good technological properties that enable the use of advanced treatments. The property enhancement of implant steels, including AISI 316, aims to increase corrosion resistance under a body fluid environment. This is how 316L steel appeared on the market [11][12][13]. The corrosion resistance of 316L stainless steel was significantly increased by adding molybdenum. As a result, the chromium compounds stabilized and formed a passive layer on the steel surface in the presence of chloride ions.
To mitigate the adverse effects of wear debris on the human body, researchers typically alter the functional properties of implanted materials by modifying the implant surface layer [14,15]. This study investigated nitrogen and oxygen ion implantation, aiming at improving the functional properties of 316L steel for biomedical applications [16][17][18][19]. The importance of this method in surface engineering has been confirmed by a significant number of studies and publications [20,21]. Although initially used only in nuclear physics, over time the method has found application in various industries, including electronics, materials, and medicine [22][23][24][25][26].
Ion implantation is a process in which atoms of any element are implanted into the core of the substrate material at a high kinetic energy. The atoms of the doped elements are ionized in the ion source, then accelerated in an electric field to energies ranging from several keV to several MeV. As a result of this process, the atoms of the base material "mix" with the implanted ions. The implanted ions penetrate the material core to a depth of 0.01 to 1 µm [25]. Figure 1 shows a schematic diagram of the implantation process.
that ensures high corrosion resistance, and very good technological properties tha the use of advanced treatments. The property enhancement of implant steels, in AISI 316, aims to increase corrosion resistance under a body fluid environment how 316L steel appeared on the market [11][12][13]. The corrosion resistance of 316L s steel was significantly increased by adding molybdenum. As a result, the chromiu pounds stabilized and formed a passive layer on the steel surface in the presence ride ions.
To mitigate the adverse effects of wear debris on the human body, research cally alter the functional properties of implanted materials by modifying the imp face layer [14,15]. This study investigated nitrogen and oxygen ion implantation at improving the functional properties of 316L steel for biomedical applications The importance of this method in surface engineering has been confirmed by a sig number of studies and publications [20,21]. Although initially used only in nucle ics, over time the method has found application in various industries, including e ics, materials, and medicine [22][23][24][25][26].
Ion implantation is a process in which atoms of any element are implanted core of the substrate material at a high kinetic energy. The atoms of the doped e are ionized in the ion source, then accelerated in an electric field to energies rangi several keV to several MeV. As a result of this process, the atoms of the base "mix" with the implanted ions. The implanted ions penetrate the material core to of 0.01 to 1 µm [25]. Figure 1 shows a schematic diagram of the implantation proc An implantation profile is a measure of the implanted layer thickness. It is defining the distribution of implanted ions at different depths in the base mate thickness of the resulting layer depends on the properties (atomic weight) of th and doping materials, ion energy, ion current density, and doping duration. Du kinetic nature of the process, any material can be doped with virtually any elemen enables materials with the assumed functional properties to be obtained. As a res possible to obtain a very high dopant concentration (up to 50%). In addition, the is characterized by a very high purity and can be carried out at low temperatures

Materials and Methods
Type 316L alloy with the chemical composition shown in Table 1 was chose amination. This steel type is characterized by a high corrosion resistance in an e ment of weak organic acids. However, it is susceptible to pitting and crevice corr the presence of chloride ions. Therefore, to improve its functional properties, ion tation with nitrogen and oxygen ions was applied. An implantation profile is a measure of the implanted layer thickness. It is a curve defining the distribution of implanted ions at different depths in the base material. The thickness of the resulting layer depends on the properties (atomic weight) of the doped and doping materials, ion energy, ion current density, and doping duration. Due to the kinetic nature of the process, any material can be doped with virtually any element, which enables materials with the assumed functional properties to be obtained. As a result, it is possible to obtain a very high dopant concentration (up to 50%). In addition, the process is characterized by a very high purity and can be carried out at low temperatures [26].

Materials and Methods
Type 316L alloy with the chemical composition shown in Table 1 was chosen for examination. This steel type is characterized by a high corrosion resistance in an environment of weak organic acids. However, it is susceptible to pitting and crevice corrosion in the presence of chloride ions. Therefore, to improve its functional properties, ion implantation with nitrogen and oxygen ions was applied. The grinding and polishing of sample surfaces were key steps in their preparation. Another important factor was the appropriate selection of the machining parameters, as these affect the performance of the components. The 20 × 20 × 5 mm plate-shaped samples were ground using a Pace Technologies grinder. Silicon carbide sandpaper with a grit size ranging from 120 to 2500 µm was used. The final step was polishing with cloths using a 1 µm grade diamond paste. After grinding and polishing, the surface roughness values were in the range of Ra = 1.5-2 µm. Prior to ion implantation, the samples were cleaned ultrasonically in ethyl alcohol and then implanted with nitrogen and oxygen ions using disruptive technology, hardion TM by Idonus (Hauterive/Neuchâtel, Switzerland). The ion dose was 5 × 10 17 N + /cm 2 and 5 × 10 17 O + /cm 2 , with an energy of 35 keV.
Tribological tests were configured for reciprocating motion using an Anton Paar TRB 3 tribometer. The choice of the motion type was based on a literature analysis, which showed that human joints work in a characteristic motion [27] that can be modelled as reciprocating motion. Figure 2 shows the friction pair diagram.
Ba-lance 16.5-18.5 10.0-13.0 2.0-2.5 <0.03 <1.0 <2.0 <0.045 <0 The grinding and polishing of sample surfaces were key steps in the Another important factor was the appropriate selection of the machining these affect the performance of the components. The 20 × 20 × 5 mm plate-sh were ground using a Pace Technologies grinder. Silicon carbide sandpaper ranging from 120 to 2500 µm was used. The final step was polishing with c µm grade diamond paste. After grinding and polishing, the surface rou were in the range of Ra = 1.5-2 µm. Prior to ion implantation, the samples ultrasonically in ethyl alcohol and then implanted with nitrogen and oxy disruptive technology, hardion TM by Idonus (Hauterive/Neuchâtel, Switze dose was 5 × 10 17 N + /cm 2 and 5 × 10 17 O + /cm 2 , with an energy of 35 keV. Tribological tests were configured for reciprocating motion using a TRB 3 tribometer. The choice of the motion type was based on a literature a showed that human joints work in a characteristic motion [27] that can b reciprocating motion. Figure 2 shows the friction pair diagram.  Table 2 compiles the test parameters. The counter-sample in the teste was a ball 6 mm in diameter made of Al2O3 (III) with an Ra equal to 0.32 were repeated five times for each friction pair with the given parameters composition of the lubricant used is summarized in Table 3.   Table 2 compiles the test parameters. The counter-sample in the tested friction pairs was a ball 6 mm in diameter made of Al 2 O 3 (III) with an Ra equal to 0.32 µm. The tests were repeated five times for each friction pair with the given parameters. The chemical composition of the lubricant used is summarized in Table 3.  Bovine serum is the recommended lubricant for wear testing, but its poor availability and rapid oxidation influenced our decision to use Ringer's solution.
A combined confocal and interferometric profiler Leica DCM8 was used to measure the post-implantation geometric structure of the surface. The axonometric images, surface profile, and essential amplitude parameters are given in Section 3.1.
Observations of the surface morphology, cross-sections of the samples, and linear analyses of the implanted layer chemical composition were performed using a Phenom XL scanning electron microscope equipped with an EDS energy dispersion spectrometer. The accelerating voltage was 15 kV and the magnifications used were ×1000, ×3000 and ×5000. Test surface micrographs before tribological tests are shown in Section 3.2, whereas Section 3.3 illustrate linear analyses of the implanted layers.
The hardness of the tested materials was determined by instrumented indentation using an Anton Paar ultra-nanoindentation tester with a Berkovich indenter tip geometry and a radius of~100 nm. The velocity of the loading force increase was 2 mN/min (the force increased linearly as a function of time). A load of 1 mN was applied. Once the maximum force setpoint was reached during the test, the force was reduced at the same rate as the increasing force until the indenter extended entirely above the sample surface. For the load-unload cycle, a graph of indenter load versus penetration depth was generated. The hardness test results are shown in Section 3.4. The mechanical properties were assessed using the Olivier Pharr method, according to which [28,29]: where: E, v-Young's modulus and Poisson's ratio of the tested material; E i , v i -Young's modulus and Poisson's ratio of the indenter's material; S-contact stiffness (tangent of the inclination angle of the unloading curve); A-contact area calculated from the contact depth and indenter's geometry calibration.
The results of tribological tests are shown in Section 3.5. The chart shows friction coefficient µ as a function of the number of recorded friction pair cycles. The Leica DCM8 confocal microscope in interferometric mode was used to examine the geometric structure of wear tracks after tribological tests on the samples and counter-samples (Section 3.6). Axonometric images, profiles, and wear depths on the cross-section were obtained from the tests. Optical measurements also allowed the determination of the wear mechanism of the friction pairs. Observations of the surface morphology and wear tracks after friction were performed using a Phenom XL scanning electron microscope. The results are shown in Section 3.7.
Contact angle measurements were performed using the Attension Theta tensiometer. The static contact angle was determined in a procedure involving the precise placement of droplets of distilled water (approx. 5 µL) on the sample surface, followed by immediate measurement. Analysis was performed automatically by the software. The droplets were applied to the disc in different parts of the sample. The measurement was repeated five times. The contact angle is an angle formed by intersecting tangent planes at the liquidsolid interface. A surface is hydrophilic (high wettability) when its static contact angle is <90 • and hydrophobic (low wettability) when the contact angle is >90 • . Biomaterials used as cardiovascular system implants (e.g., stents) should be both hydrophobic and non-thrombogenic for the continuous movement of fluid connective tissue-blood. The contact angle measurements are shown in Section 3.8.

Confocal Microscopy Results
A detailed analysis of the surface geometric structure is based on an informed selection of amplitude parameters, which are a valuable source of information on the design and operation of the surfaces tested [19,30]. However, the assessment of surface topography based on only one parameter-Sa (arithmetic mean height)-provides insufficient information on the measured profile. Thus, the parameters Sp-maximum peak height; Sv-maximum valley depth; Sz-maximum height of the surface; Sq-squared mean height; Ssk-asymmetry coefficient (skewness); and Sku-flattening (clustering) coefficient (kurtosis) were used in the analysis. These parameters are more sensitive to the presence of valleys and peaks. Figure 3 and Table 4 show the axonometric images, surface profiles, and amplitude parameters of the reference and the implanted samples.

Confocal Microscopy Results
A detailed analysis of the surface geometric structure is based on an informed se tion of amplitude parameters, which are a valuable source of information on the des and operation of the surfaces tested [19,30]. However, the assessment of surface topog phy based on only one parameter-Sa (arithmetic mean height)-provides insufficient formation on the measured profile. Thus, the parameters Sp-maximum peak height; S maximum valley depth; Sz-maximum height of the surface; Sq-squared mean heig Ssk-asymmetry coefficient (skewness); and Sku-flattening (clustering) coefficient (k tosis) were used in the analysis. These parameters are more sensitive to the presenc valleys and peaks. Figure 3 and Table 4 show the axonometric images, surface profi and amplitude parameters of the reference and the implanted samples.   The analysis of the geometrical structures of the reference surface and the implan samples revealed that the values of all parameters (Sp, Sv, Sz, Sa, and Sq) were lower th those of the reference sample. These lower values indicate that implantation ensu smooth surfaces. A positive value of Ssk informs us of the presence of steep ridges a peaks with sharp tips on the surface of the reference sample. A decrease in the value Ssk to −0.67 in the case of a sample implanted with nitrogen ions indicates a gradual l of sharpness-an increase in the curvature radius of the tips. The analysis of the amplitu parameters of the sample implanted with oxygen ions showed that its surface was a p eau with gentle slopes and rounded tips. These surface features have a direct influence the wear mechanism and wear intensity of the tested components.   The analysis of the geometrical structures of the reference surface and the implanted samples revealed that the values of all parameters (Sp, Sv, Sz, Sa, and Sq) were lower than those of the reference sample. These lower values indicate that implantation ensures smooth surfaces. A positive value of Ssk informs us of the presence of steep ridges and peaks with sharp tips on the surface of the reference sample. A decrease in the value of Ssk to −0.67 in the case of a sample implanted with nitrogen ions indicates a gradual loss of sharpness-an increase in the curvature radius of the tips. The analysis of the amplitude parameters of the sample implanted with oxygen ions showed that its surface was a plateau with gentle slopes and rounded tips. These surface features have a direct influence on the wear mechanism and wear intensity of the tested components.        Figures 4-6 reveal the granular characteristics of all samples. Granularity was more pronounced in the reference sample than in those implanted with nitrogen and oxygen ions. In addition, a higher etched area void fraction was observed on the surface implanted with nitrogen ions. As a result, the surface became more homogeneous, as confirmed by the geometric structure examination.

Assessment of Implanted Layers
Thickness assessment involved the preparation of a metallographic section on the transverse cross-section. The thickness of the implanted layer was difficult to evaluate, as the boundary between the implanted layer and the substrate was not clear. Only brighter and darker zones were observed, and these were impossible to measure. The depth of the nitrogen and oxygen ion implantation was determined through linear analyses.
surface became more homogeneous, as confirmed by the geometric structure exami tion.

Assessment of Implanted Layers
Thickness assessment involved the preparation of a metallographic section on transverse cross-section. The thickness of the implanted layer was difficult to evaluate the boundary between the implanted layer and the substrate was not clear. Only brigh and darker zones were observed, and these were impossible to measure. The depth of nitrogen and oxygen ion implantation was determined through linear analyses.   The gradual change in colour from brighter (upper part of the layer) to the darker (lower part of the layer) indicates the typical nature of the layers modified by ionic implantation-i.e., the lack of a clear boundary between the modified surface layer and the 316L core. From Figures 7 and 8, it follows that the nitrogen ions penetrated the sample to a depth of 500 nm at the same process parameters, with an average effective penetration range of 180 nm. In the case of the oxygen ions, the maximum penetration depth was about 350 nm, with an average range of about 60 nm. The percentage content of other elements constituting the alloy increased with depth and the loss of the implanted layer. The gradual change in colour from brighter (upper part of the layer) to the darker (lower part of the layer) indicates the typical nature of the layers modified by ionic implantation-i.e., the lack of a clear boundary between the modified surface layer and the 316L core. From Figures 7 and 8, it follows that the nitrogen ions penetrated the sample to a depth of 500 nm at the same process parameters, with an average effective penetration range of 180 nm. In the case of the oxygen ions, the maximum penetration depth was about 350 nm, with an average range of about 60 nm. The percentage content of other elements constituting the alloy increased with depth and the loss of the implanted layer. Figure 9 shows an example penetration depth curve for a nominal loading force of 1 mN with a marked maximum force for which h max indentation is determined. The penetration depth measurements were the basis for determining the most important mechanical parameters. Table 5 compiles the mean values of the parameters obtained from five measurements.  Figure 9 shows an example penetration depth curve for a nominal loading force of 1 mN with a marked maximum force for which hmax indentation is determined. The penetration depth measurements were the basis for determining the most important mechanical parameters. Table 5 compiles the mean values of the parameters obtained from five measurements.  The curves presented in Figure 9 indicate that, compared to the reference sample, the deposited layers are more elastic, as shown by the indentation curve slope and the plastic and elastic behaviour values. Moreover, the lower Wtot value of the implanted samples proves that the deposited layers are less susceptible to deformation due to service loads. The instrumented hardness tests clearly showed improved hardness after implantation. Nitrogen ion implantation provided an approximately 45% higher efficiency and a 20% increase in the Young's modulus values. Oxygen ion implantation increased the Young's modulus values by about 5%. The same increase can be observed in the contact area values. The nanohardness results indicate that the nitrogen ion-implanted samples should have the most beneficial tribological characteristics.  The curves presented in Figure 9 indicate that, compared to the reference sample, the deposited layers are more elastic, as shown by the indentation curve slope and the plastic and elastic behaviour values. Moreover, the lower Wtot value of the implanted samples proves that the deposited layers are less susceptible to deformation due to service loads. The instrumented hardness tests clearly showed improved hardness after implantation. Nitrogen ion implantation provided an approximately 45% higher efficiency and a 20% increase in the Young's modulus values. Oxygen ion implantation increased the Young's modulus values by about 5%. The same increase can be observed in the contact area values.

Nanohardness of Deposited Layers
The nanohardness results indicate that the nitrogen ion-implanted samples should have the most beneficial tribological characteristics. The results of the tribological tests indicate that, under dry friction, the implanted samples displayed the lowest resistance to motion. The average coefficients of friction were comparable in all samples when Ringer's solution was used as a lubricant. During dry sliding, a rapid increase in the friction coefficient was observed for the nitrogen ionimplanted sample between cycles 1 and 5000, after which the increase became less rapid. In the final stage, the maximum coefficient value was about 0.61. Compared to the reference sample, the coefficient's mean value decreased by about 20%. Under lubricated conditions, the reference sample recorded the lowest resistance to motion. During cycle 5000, the friction coefficient rose sharply from 0.06 to about 0.4, most likely due to the wear debris present at the sample -ball interface. The wear debris was present until the end of the test, as indicated by the unchanged value of the µ parameter, which was 0.42.

Assessment of Surface Geometric Structure of Samples and Counter-Samples
After tribological tests, the wear tracks on the samples and counter-samples were measured and average depths and wear areas of the samples and counter-samples (balls) were determined from three series of measurements. The test results are shown in Figures  11-19. Tables 6 and 7 summarise the amplitude parameters of the wear tracks. The results of the tribological tests indicate that, under dry friction, the implanted samples displayed the lowest resistance to motion. The average coefficients of friction were comparable in all samples when Ringer's solution was used as a lubricant. During dry sliding, a rapid increase in the friction coefficient was observed for the nitrogen ionimplanted sample between cycles 1 and 5000, after which the increase became less rapid. In the final stage, the maximum coefficient value was about 0.61. Compared to the reference sample, the coefficient's mean value decreased by about 20%. Under lubricated conditions, the reference sample recorded the lowest resistance to motion. During cycle 5000, the friction coefficient rose sharply from 0.06 to about 0.4, most likely due to the wear debris present at the sample -ball interface. The wear debris was present until the end of the test, as indicated by the unchanged value of the µ parameter, which was 0.42.

Assessment of Surface Geometric Structure of Samples and Counter-Samples
After tribological tests, the wear tracks on the samples and counter-samples were measured and average depths and wear areas of the samples and counter-samples (balls) were determined from three series of measurements. The test results are shown in Figures 11-19. Tables 6 and 7        14, x FOR PEER REVIEW 13 of 21       After tribological tests, the analysis of the surface geometric structure revealed the fastest wear rates in the reference sample and in the sample implanted with oxygen ions under both dry and lubricated friction. Despite the lower resistances to motion obtained when Ringer's solution was used, the wear of the samples was several times higher compared to that of the nitrogen ion-implanted material. Microscopic examination revealed an abrasive wear mechanism in all cases under analysis.       After tribological tests, the analysis of the surface geometric structure revealed the fastest wear rates in the reference sample and in the sample implanted with oxygen ions under both dry and lubricated friction. Despite the lower resistances to motion obtained when Ringer's solution was used, the wear of the samples was several times higher compared to that of the nitrogen ion-implanted material. Microscopic examination revealed an abrasive wear mechanism in all cases under analysis. Figures 17-19 show examples of optical and axonometric wear track images for a counter-Al 2 O 3 ball pair. For sliding with RS lubrication, the highest counter-sample wear was recorded in friction pairs 316L-Al 2 O 3 and 316L O + -Al 2 O 3 , where the ball wear was 138.9 µm 2 and 427.3 µm 2 , respectively. For 316L N + , the ball wear was 65% lower than that of the reference sample and over 80% lower compared to that of the oxygen ion-implanted sample. The analysis of the amplitude parameters showed an increased roughness of the friction surfaces (samples and balls) due to the tests.

Assessment of Wear Mechanism
To conduct a more detailed analysis and identify the wear mechanisms inovlved, SEM observations of wear tracks were performed. The results are compiled in    19 show examples of optical and axonometric wear track images for a counter-Al2O3 ball pair. For sliding with RS lubrication, the highest counter-sample wear was recorded in friction pairs 316L-Al2O3 and 316L O + -Al2O3, where the ball wear was 138.9 µm 2 and 427.3 µm 2 , respectively. For 316L N + , the ball wear was 65% lower than that of the reference sample and over 80% lower compared to that of the oxygen ion-implanted sample. The analysis of the amplitude parameters showed an increased roughness of the friction surfaces (samples and balls) due to the tests.

Assessment of Wear Mechanism
To conduct a more detailed analysis and identify the wear mechanisms inovlved,   19 show examples of optical and axonometric wear track images for a counter-Al2O3 ball pair. For sliding with RS lubrication, the highest counter-sample wear was recorded in friction pairs 316L-Al2O3 and 316L O + -Al2O3, where the ball wear was 138.9 µm 2 and 427.3 µm 2 , respectively. For 316L N + , the ball wear was 65% lower than that of the reference sample and over 80% lower compared to that of the oxygen ion-implanted sample. The analysis of the amplitude parameters showed an increased roughness of the friction surfaces (samples and balls) due to the tests.

Assessment of Wear Mechanism
To conduct a more detailed analysis and identify the wear mechanisms inovlved,     Wear track surface analysis indicated abrasive wear as a dominant mechanism in the reference sample. Ploughing and cutting resulting from secondary wear debris displaced between the interacting surfaces increased wear intensity. The moving wear particles caused cracks or plastic deformations in the form of grooves. More or less intense traces of wear occurred on all tested samples, with the most pronounced tracks (wide and deep) observed on the reference surfaces.
Far narrower and shallower tracks were observed on the implanted samples, as confirmed by examining the surface geometric structure. SEM images of the deposited layers indicate that the agglomerates of wear debris were pressed into the sample surface during the frictional wear tests. A comprehensive analysis of the surface geometric structure after tribological tests demonstrated that the implanted layer was not removed in the case of the sample ion-implanted with nitrogen. Wear track surface analysis indicated abrasive wear as a dominant mechanism in the reference sample. Ploughing and cutting resulting from secondary wear debris displaced between the interacting surfaces increased wear intensity. The moving wear particles caused cracks or plastic deformations in the form of grooves. More or less intense traces of wear occurred on all tested samples, with the most pronounced tracks (wide and deep) observed on the reference surfaces.
Far narrower and shallower tracks were observed on the implanted samples, as confirmed by examining the surface geometric structure. SEM images of the deposited layers indicate that the agglomerates of wear debris were pressed into the sample surface during the frictional wear tests. A comprehensive analysis of the surface geometric structure after tribological tests demonstrated that the implanted layer was not removed in the case of the sample ion-implanted with nitrogen. Figure 26 presents an example of the contact angles of the tested surfaces using distilled water. Mean values of the recorded contact angles for the applied measuring liquid are shown in Table 8.

Contact Angle
between the interacting surfaces increased wear intensity. The moving wear particles caused cracks or plastic deformations in the form of grooves. More or less intense traces of wear occurred on all tested samples, with the most pronounced tracks (wide and deep) observed on the reference surfaces.
Far narrower and shallower tracks were observed on the implanted samples, as confirmed by examining the surface geometric structure. SEM images of the deposited layers indicate that the agglomerates of wear debris were pressed into the sample surface during the frictional wear tests. A comprehensive analysis of the surface geometric structure after tribological tests demonstrated that the implanted layer was not removed in the case of the sample ion-implanted with nitrogen. Figure 26 presents an example of the contact angles of the tested surfaces using distilled water. Mean values of the recorded contact angles for the applied measuring liquid are shown in Table 8.  Contact angle measurements confirmed the effect of ion implantation on wettability. The tests showed that 316L and 316L O + steels are hydrophilic. The highest contact angles were displayed by the sample implanted with nitrogen ions. They were about 50% larger compared to the reference sample and about 40% larger compared to the sample implanted with oxygen ions. In the case of cardiovascular implants, the hydrophobicity of the surface is desirable for the continuous movement of fluid connective tissue-blood.  Contact angle measurements confirmed the effect of ion implantation on wettability. The tests showed that 316L and 316L O + steels are hydrophilic. The highest contact angles were displayed by the sample implanted with nitrogen ions. They were about 50% larger compared to the reference sample and about 40% larger compared to the sample implanted with oxygen ions. In the case of cardiovascular implants, the hydrophobicity of the surface is desirable for the continuous movement of fluid connective tissue-blood.