KnE Engineering | XIX International scientific-technical conference “The Ural school-seminar of metal scientists-young researchers” | pages: 65–73

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1. Introduction

Various materials and techniques have been developed to facilitate bone-healing process and reduce its healing period. Tissue engineering of bone scaffolds may offer a different variety to native autoscaffolds, which are in short supply. Metallic biomaterials are widely used in bone surgery for different approaches. Titanium and its alloys are preferred as implant materials, as they are highly biocompatible, osteoconductive and resistant to corrosion [1]. Young's modulus as well as tensile strength, ductility, fatigue life, fretting fatigue life, wear properties, functionalities, etc., should be adjusted to the levels that are suitable for structural biomaterials used in implants that replace hard tissue [2].

Many studies promote the fabrication of scaffolds consisting of a viable porous bone-like metal. Introduction of porosity and pore interconnectivity improves mechanical fixation and osteointegration by allowing extensive body fluid transport through the porous implant. This can provoke bone tissue ingrowth, consequently leading to the development of a stable interface between the scaffold and host tissue [3]. When an implant is populated with osteogenic cells, these cells not only migrate on the surface of the implant but also inside the pores of the implant [4]. So the introduction into operative trauma and orthopedics clinical practice porous titanium augments obtained based on additive prototyping undoubtedly requires an active study of the fundamental principles of bone tissue regeneration.

Advantages of the manufacturing process have led to the evaluation of porous titanium as the bone-like base material [5]. For manufacturing the porous titanium implants, such methods as selective laser melting, electron beam melting and direct metal laser sintering have proven to be relevant methods as they offer the opportunity to produce patient-individual implants for different approaches quickly and cost-efficiently. The porous surfaces of DMLS titanium parts have been demonstrated to be favorable for cell adhesion, migration and ingrowth and these properties result in a strong bone-implant contact [6].

Mechanical properties are especially important in scaffolds for hard and ductile tissues such as bone because the scaffolds must also interact with their physiological surroundings to transmit mechanical signals to cells and regulate cell behavior (i.e., differentiation, motility, and contractility). The stiffness of scaffold can have effects at a transcriptional level, determining whether stem cells make the decision to become cells as functionally diverse as osteoblasts [7]. Mechanical mismatch of implant and bone defects frequently leads to loosening of the implant. The higher Young's modulus of titanium compared to that of cortical or trabecular bone resulting in stress shielding is of major concern [8,9,10].

Due to advantages of the titanium structures produced by DMLS, we designed and produced a porous augment for experimental estimation of its osteointegration properties with microindentation and energy dispersive X-ray microanalysis.

2. Material and Methods

The porous titanium implant (PTI) was an experimental medical device and consisted of cubic samples with the side of 5 mm, which were produced by direct metal laser sintering (DMLS) on an EOSINT 280. As a raw material, a powder was used from the (α + β)-titanium alloy Ti-6Al-4V Eli. The dimensions and geometry of the unit cell of the porous structure provided open-porosity in the samples under study of the order of 55%.

Preliminary finite element calculations in the ABAQUS software have shown the importance of adequate design of the internal architecture of a cellular material. As a result, the cellular structure was used as the base architecture for volumetric modeling by the finite element method, the unit cell of which was a diamond structure, which consisted of cylinders oriented in space at an angle of 109 28' to each other. In the software package Solid Works, 3D models of a unit cell with different pore fractions were constructed. Samples were designed in the form of a parallelepiped with open porosity. The pore size was 680 μm, the spacer size varied in the interval 400-1300 μm, so the relative porosity of the sample was set in the interval 50...80%. Ti-6Al-4V titanium alloy was used as the model material, as the most commonly used alloy for manufacturing medical implants.

Twenty-four 6 months female Shinshila rabbits weighing (3.11 ± 0.31) kg were used. The animals were kept in individual cages (22 C, 55% humidity, and a 12-h light/dark cycle) and were fed and watered ad libitum. The study protocol was approved by the Ethics Committee of Ural Medical University (December 2016, protocol №10). These rabbits were randomly divided into two groups (test and control groups). Operation was performed under general anesthesia - intramuscular xylazine 20 mg - 1 ml - 0.2 ml/kg and tiletamine - 6 mg/kg. To potentiate anesthesia, 0.25% of novocaine was used, which was also used with hydraulic tissue dissection property. Augmentation procedure was performed bilaterally. Both shins were shaved and washed with 10% povidone iodine solution.

Surgical access was performed to the medial tibia condyle by soft tissues sharp dissection; the periosteum was displaced in the distal direction. The anatomical reference point for further action was the general tendon fixation of pes anserinus superficialis. With a diamond metal cutting disc we produced a quadruple spacing (7x8 mm) in the medial condyle of the tibia before the anatomical formation above the depth of the cortical plate of the bone without penetrating the cavity of the knee joint, after which the desired rectangular part of the bone was extracted. A dynamic force displacement (using a hammer and an impactor) of the proximal condyle fragment in the distal direction was performed to make a defect for modelling the intraarticular impressional fracture. To manage such fracture an open reduction was done. Rabbits from test group were augmented with PTI by press fit type, controls were not augmented. The periosteum, muscle fascia, and skin were then sutured in separate layers. An analgesic (1 mg/kg tramadol) and an antibiotic (25 mg/kg cefazolin) were administered intramuscularly preoperatively and twice per day for three postoperative days.

Five rabbits of test group and three rabbits of control were euthanized via an intravenous tiletamine overdose at 6, 12 and 25 weeks after the scaffold placement. The proximal tibias were fixed in 10% formalin.

Bone samples for further research after cooling with liquid nitrogen to prevent bone structure thermal destruction and to reduce the bone-implant viscosity were sliced (5 mm distally from the joint surface to lay the cut at the middle of PTI) with diamond metal cutting disc. Further, grinding was carried out using an abrasive wheel and final polishing with a colloidal silica suspension. After that, the samples were degreased and cleaned in an ultrasonic bath in acetone. The adhesive glue was applied in a thin layer and the sample was stabilized using digital pressure.

Vickers Hardness (VHN) of the bone was assessed by using a microhardness dynamic indenter (PMT-3 microhardness tester, Russia). Ten continuous indentations were made around each critical zones (less than 500 µm). The hardness is defined as the test force divided by the apparent area of the indentation at maximal force. The holding time was 15 seconds, and the applied load was 5N. The diagonals of the prints were measured at a 200-fold magnification, and the Vickers microhardness value was calculated by the formula:

VH=0,189×Fd2,

where F is the applied load, [N]; d is the length of the diagonal, [mm].

The same samples were examined by scanning electron microscopy (SEM) in a FEG SEM ZEISS CrossBeam AURIGA. The Ca/P ratio was calculated using the accompanying Oxford Inca software the same critical zones. Reference standards and synthetic pure samples with similar Ca/P ratio (tricalcium phosphate, Ca 3 (PO 4 ) 2 , and hydroxyapatite) were used for calibration. Prior to each session, the smooth surface of all pellets was coated with a conductive carbon layer (Fig. 1).

STATA software was utilized for the statistical analysis of the results. Data are reported as median with interquartile range (IQR) and confidence intervals (CI). In the analysis of the data, parametric (Student's test) and non-parametric methods (Wilcoxon test, Kruskal-Wallis) and independent (Mann-Whitney test) variants were used, as well as the Shapiro-Wilk test to verify the normality of distributions. The degree of interconnection of traits was estimated using Pearson correlation coefficient and nonparametric Spearman coefficient. Statistical significance was considered at p < 0.05.

fig-1.jpg
Figure 1
Photomicrograph of trabecular bone tissue site with an augmented porous titanium implant.

3. Results

No operative or postoperative complications were encountered. All of the rabbits tolerated surgery well and survived until the final experimental time. No wound opening or infections were observed. At sacrifice the macroscopic evaluation revealed maintenance of correct position of sample in the defect site.

There was a significant increase in both mineral and mechanical properties of bone samples in test group in all times as compared to control group (Table 1).

Table 1

Ca/P ratio and microhardness of test and controls groups (median, 95% Confidence interval).


Time of augmentation Ca/P ratio Microhardness [HV]
Test group Control Test group Control
6 weeks 1.42 (1.28-1.64)* 1.94 (1.92-1.98) 66 (63-69)* 87 (74-91)
12 weeks 1.54 (1.16-1.89)* 1.95 (1.91-1.98) 82 (74-88) 88 (84-91)
25 weeks 2.03 (1.74-2.17) 1.94 (1.91-1.98) 99 (94-102)* 87 (84-91)
*p < 0.05

The Pearson correlation test between the microhardness parameter and the Ca / P ratio revealed the strong relationship (r = 0.808, r 2 = 0.65).

4. Discussion

Ca and P are the main elements of the bone mineral matrix. The relative content of Ca and P, however, is critical for sustaining mineral homeostasis and bone metabolism and their co-dependence is evident for bone growth and development [11]. It is therefore a suitable biomarker for the assessment of bone mineral homeostasis, which an energy-dispersive (EDX) analysis is physically able to measure from relative mass variations of Ca and P in different bone samples. Kourkoumelis N. et all evaluated the Ca/P ratio at different sites of normal and osteoporotic rabbit bones using two spectroscopic techniques: auger electron spectroscopy and EDX. They found Ca/P ratio of normal trabecular bone as 1.88 ± 0.04 (mean ± SD). They also came to conclusion that there is no significant difference between samples from different genders or among cortical bone sites (Ca/P ratio for rear tibia was 2.14 ± 0.04) [12]. Other data were obtained in the study of Sobczak A. et all. The calcium to phosphorus ratio in the animal bony samples had value of 1.67 and amounted to 1.70 [13]. According to Zuo Q. et all Ca/P ratio of human subchondral bone was 1.52 ± 0.04 [14].

In our study, the Ca/P ratio in perifocal zone at 6 weeks of implantation was 1.42 (1.28-1.64) that was 1.37 times lower comparing controls. This may indicate the presence of immature bone tissue, which undergoes mineralization processes. At 25 weeks of implantation ratio was 1.42 (1.28-1.64), that was 1.05 times higher comparing controls (p > 0.05), which may indicate the mineralization processes completion and the presence of mature lamellar bone tissue, which in its characteristics does not differ from the control group.

Another important characteristic of bone tissue in terms of mechanical properties is the Vickers microhardness. Soares P.B. et all studied the Vicker's hardness and elastic modulus surround cortical bone to dental implant in different regions. Ten cylindrical implants with morse taper interface (Titamax CM, Neodent; 3.5 mm diameter and 7 mm a height) were inserted in rabbit tibia. Mean and standard deviation of Vickers microhardness was 120.1 ± 43.7 [15]. According to Stea S. et all who evaluated bone microhardness at the interface with hydroxyapatite - coated stainless - steel pins as test group and uncoated pins were implanted as controls. Pins were transversally inserted into the diaphyses of sheep tibiae and were loaded in for 6 weeks. The mean hardness at the interface with the pins was 56.9 Vickers, whereas at the interface with the uncoated pins it was 62.2. Authors came to conclusions that, 6 weeks postsurgery, the bone growing into the threadings of a loaded screwed implant reached maturity at a degree lower than that of the host both uncoated and coated implants [16]. Giavaresi G. et all evaluated bone microhardness in implants perifocal zone inserted in sheep femoral cortical bone at different times to compare the in vivo osseointegration of titanium screws. It was concluded that titanium implants showed the lowest value for the inner thread area at 8 weeks (49.8 ± 3.8 HV). These findings confirm that osseointegration may be accelerated by adequate surface roughness and bioactive ceramic coating such as Ca-P [17].

In our study, the Vickers microhardness in perifocal zone at 6 weeks of implantation was 66 (63-69) HV that was 1.32 times lower comparing controls (p < 0.05). At 25 weeks of implantation Vickers microhardness was 99 (94-102) HV, that was 1.14 times higher comparing controls (p < 0.05), which may indicate the maturation processes completion, characteristics of which to some extent exceed the control group. In our study, with an increase in the observation period, a distinct relationship was observed between the mineralization parameter of bone tissue and its microhardness (r = 0.808, r 2 = 0.65), so it can be assumed that porous titanium implants have a good integration properties into the trabecular bone defect.

5. Conclusion

The results of this study suggest that porous titanium implants are effective in trabecular bone augmentation when employed as a bone substitute as evidenced through Ca/P ratio and microhardness estimation. Though animal models cannot be directly translated to clinical application, investigation into the use of porous titanium implants in a clinical setting may be appropriate to further characterize its efficacy.

Acknowledgements

We hereby acknowledge the support of the Ministry of Science and Education of the Russian Federation, in accordance to the decree of the Government of April 9, 2010, №218, project number 03.G25.31.0234.

The work was carried out using the laboratory equipment ”Structural methods of analysis and properties of materials and nanomaterials” of the Center of Ural Federal University.

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