# Design and Performance Evaluation of Porous Titanium Alloy Structures for Bone Implantation

Authors: Jianping Shi; Huixin Liang; Jie Jiang; Wenlai Tang; Jiquan Yang
Journal: Mathematical Problems in Engineering
 (2019)

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## Abstract

Implant parts prepared by traditional design and manufacturing methods generally have problems of high stiffness and heavy self-weight, which may cause stress shielding effect between the implanted part and the host bone, and eventually cause loosening of the implanted part. Based on the implicit surface function equations, several porous implant models with controlled pore structure were designed. By adjusting the parameters, the apparent elastic modulus of the porous implant model can be regulated. The biomechanical simulation experiment was performed using CAE software to simulate the stress and elastic modulus of the designed models. The experimental results show that the apparent elastic modulus of the porous structure scaffold is close to that of the bone tissue, which can effectively reduce the stress shielding effect. In addition, the osseointegration status between the implant and the host bone was analyzed by implant experiment. The pushout test results show that the designed porous structures have a good osseointegration effect.


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## Body

## 1. Introduction

At present, design methods for implant part are mostly based on CT (computed tomography) scan, reverse reconstruction, or forward modeling in design software. Implant parts prepared by traditional design and manufacturing methods generally have problems of high stiffness and heavy self-weight, and stress shielding effect would occur between the parts and the host bone after implantation, which may cause loosening of the implant and lead to reducing implant life directly [1–6].Due to its excellent mechanical properties, good biocompatibility, and low fitting error, porous implants have become hot topics in recent years [7, 8]. Porous implant parts with a unique interconnected pore structure can promote the formation of mineralized layers on the implant surface and attract protein adsorption. It also facilitates the adhesion, proliferation, and differentiation of osteoblasts and promotes the growth of osteoblasts. At the same time, nutrition and oxygen transport and metabolite excretion can be achieved. In addition, the porous structure is also conducive to the growth of blood vessels and nerves, so it is an ideal part for the implant. However, for porous implant parts, most of the current design methods are the combination of a fully porous structure and a solid model. These methods often face challenges such as low efficiency of the modeling process, low molding quality, or poor biocompatibility. According to the requirements of implant tissue engineering, in addition to the need for biomechanical properties, the porous structure implants must also provide a good microenvironment for the bone tissue cells. The traditional bone implants generally only have the geometric shape of the lesion, and their internal pore structure still needs to be remodeled [9–11].In the field of artificial implant modeling, the current research mainly focuses on the design of an implant model that combines both mechanical and biological properties. Wang et al. used the Boolean operation of the original solid model and the standard porous model to obtain a bionic scaffold microporous bone model structure [12]. Parthasarathy et al. put forward a hierarchical cell structure modeling method for the acetabular cup, making the elastic properties of the implant similar to that of the surrounding bone tissue and achieving biological fixation [13]. Khanoki et al. proposed a heterogeneous lattice structure based on multiscale mechanics and design optimization to reduce the risk of concurrent bone resorption and graft failure [14]. Gibson et al. optimized the design of components for the requirements of the overall mechanical structure of the implanted parts, and the optimized design rules broke many traditional limitations [15]. Porous implant parts constructed by these methods have less consideration for the influence of the porous structure on the implant and the surrounding tissue [16–19].Porous structural implants are important matrices for the construction of tissue-engineered bone tissue, and they are also important microenvironment providers that bone cells rely on in the growth process. Therefore, it is required that the implant not only needs to have a precise geometric shape of the bone tissue part of the lesion but also needs a certain number of interconnected pores inside the implant. The most important thing is to ensure that the mechanical properties are close to the bone tissue and to avoid stress shielding between them.Because of the impressive capability of producing porous structures with a controlled architecture precisely owing to their layer-wise building approach and direct link with a computer-aided design (CAD) model, 3D printing (also called additive manufacturing) techniques have been described as crucial production techniques towards a more controlled bone scaffolds [20]. The selective laser melting (SLM) process is one of the recently developed additive manufacturing techniques that emerged in the late 1980s and early 1990s [21], which can create functional, complex metal parts directly, bringing a high degree of freedom to design works. Compared to conventional manufacturing techniques, SLM offers a wide range of advantages, such as reduction of production steps, a high level of flexibility, a high material use efficiency, and a near net shape production [22]. Moreover, due to the additive and layer-wise production, the SLM process is capable of producing complex geometrical features that cannot be obtained using conventional production routes. And the SLM-built porous biological metal scaffolds have presented positive results in both in vitro and in vivo studies [23].Based on the technical characteristics of 3D printing technology, this article takes the functional design as the guiding ideology to study the modeling methods of porous structural implant parts. The simulation tests and implantation experiments of the designed porous parts were carried out to analyze their mechanical properties and biocompatibility. The results show that the biological properties and mechanical properties of the porous implant parts achieve the desired consequences.


## 2. Materials and Methods

### 2.1. Model Designing

Through the different adjustments of the combined transformation of triangular periodic functions, a series of implicit surfaces with periodic changes can be constructed. In the constructed surface function, the most representative surface is a three-dimensional periodic miniaturized surface (TPMS). Three-dimensional periodic miniaturized surfaces are approximately defined as follows:(1)∅r=∑k=1KAkcos2πhk⋅rλk+pk=C,where Ak denotes the amplitude factor, hk denotes the vector of the k-th grid in the derivative space, r denotes the position vector of the Euclidean space, λk denotes the periodic wavelength value of the function, pk denotes the function phase offset, and C denotes a constant.Based on equation (1), in order to obtain richer porous structural units, a function or constant is usually added to the implicit surface function. Taking P surface as an example, a distance constant t is added to its constructor to form a new Pt surface, and its construction equation can be shown by the following equation:(2)fp=acosx+bcosy+ccosz+t,where distance constant t is used to express the value of the point distance on the minimal surface from the implicit function (fpx,t). When the distance t is smaller than a certain threshold, the surfaces represented by the implicit function are continuous, and the surface is graphically represented as shown in Figure 1(a). When the distance t is greater than a certain constant threshold, the surface represented by the implicit function will no longer be continuous, and the surface is graphically represented as shown in Figure 1(c). At this time, the implicit function is no longer suitable for modeling of a continuous porous structure. It is usually possible to obtain a porous structure model with different volume fractions by changing the value of t.Figure 1
P surfaces represented by implicit functions corresponding to different distance constants t: (a) 0.5; (b) 1; (c) 2.
(a)
(b)
(c)Three kinds of porous structural models were designed, and the values of parametert in the implicit function equations are shown in Table 1. The design specifications of the three cylinders were Φ8m×10mm, and the models are shown in Figure 2.Table 1
Porous implant model corresponding to different values of the parametert.
Models
1
2
3
Values of the parametert
−0.4
0
0.4
Diameter of pore (mm)
0.37
0.50
0.63Figure 2
Three kinds of porous structure models. (a) Model 1. (b) Model 2. (c) Model 3.
(a)
(b)
(c)


### 2.2. FEA Simulation

The finite element simulation (FEA) software ABAQUS was used to simulate and test the porous model. In the simulation process, the porous model was set to a linear, elastic, and homogeneous model. The elastic modulus of the part material was set to 105 GPa, Poisson’s ratio was 0.31, and the yield strength was set to 830 MPa. The loading values and boundary conditions for the model simulation were described in a previous article published by the author [24]. To facilitate the simulation analysis, a low-thickness cylinder was added to both ends of the porous structure to ensure that each porous structural model exerts the same force. A compressive stress of 30 MPa was applied at the top of the model. The bottom of the model is completely restrained and fixed. The porous model was mesh subdivided. Models 1, 2, and 3 were meshed with 968335, 833442, and 700461 tetrahedral elements, respectively. Through the calculation iteration, the strain and stress distribution of the model was finally obtained.


### 2.3. 3D Printing

The Ti6Al4V titanium alloy powder produced by the German EOS company was used as the printing powder material. The composition and mass fractions of the metal powder are shown in Table2.Table 2
Chemical composition of titanium alloy powder (% by mass fraction).
Material
Ti
Al
V
O
Fe
C
N
H
Content
Bal
6.00
4.00
0.15
0.10
0.03
0.01
0.01The specimens were fabricated with an SLM machine (EOSINT M290; EOS GmbH, Germany) using the optimized processing parameters (Table3). Selective laser melting of porous scaffolds is characterized by a controllable and precise layer-wise material addition process that allows generating complex structures by selectively melting successive layers of metal powder, using a focused and computer-controlled laser beam, as seen in Figure 3.Table 3
Optimized process parameters used in SLM fabrication.
Laser power
Scan speed
Hatch spacing
Layer thickness
Laser focus
Atmosphere
180 W
1200 mm/s
0.1 mm
0.03 mm
0.08 mm
ArFigure 3
Sketch map of SLM printing process.


### 2.4. Animal Experiment

A total of 6 male Bama minipigs were enrolled in this study (6 months old). All animal studies (including the euthanasia procedure which was performed using lidocaine and propofol) were done in compliance with the regulations and guidelines of the ethics committee of Drum Tower Hospital affiliated to Medical School of Nanjing University and conducted according to the ARRIVE and the IACUC guidelines.All the implants were implanted at the distal region and proximal region of the right tibia bone. Cefuroxime sodium was intramuscularly injected for 3 days after operation to avoid infection. Tetracycline hydrochloride and Calcein were injected for the following fluorescence observation. All animals were sacrificed at the 5th week after operation to measure the osseointegration between the implants and the surrounding bone tissue.


### 2.5. Performance Evaluation

Micro-CT scan, histological analysis, and biomechanical testing were used to observe the parts of the porous implant. The tibia bones were harvested and scanned in a M1001 micro-CT system (Hiscan Information Technology, Jiangsu, PRC) at 90 kV, 89μA, field of view (FOV) of 63.9 mm, and a nominal isotropic image voxel size of 62.4 μm. The obtained images were converted to DICOM files for the following analysis.The harvested femurs were fixed in formalin and then rinsed with distilled water, dehydrated through graded alcohols, and embedded in polymethyl methacrylate (PMMA) without decalcification. Thin sections of 30μm thickness were cut using a diamond-coated saw (310 CP; EXAKT, Germany). The sections were stained with Goldner trichrome staining and then observed using a fluorescence microscope (Olympus Corp., Tokyo, Japan).In order to test the bonding strength between the porous implant and the host bone, the porous implants were subjected to release experiment test, and the test principle is shown in Figure4(a). The removed sacrum samples were repaired and fixed on the test platform of the electronic dynamic and static material testing machine (ElectroPuls 3000, Instron, USA). The top punch of the test instrument was vertically aligned with the porous metal implant. During the test, a slow feed was applied at a loading speed of 0.1 mm/s, as shown in Figure 4(b).Figure 4
Pushout test of implant. (a) Schematic diagram of the pushout test and (b) the device of release experiment.
(a)
(b)


## 2.1. Model Designing

Through the different adjustments of the combined transformation of triangular periodic functions, a series of implicit surfaces with periodic changes can be constructed. In the constructed surface function, the most representative surface is a three-dimensional periodic miniaturized surface (TPMS). Three-dimensional periodic miniaturized surfaces are approximately defined as follows:(1)∅r=∑k=1KAkcos2πhk⋅rλk+pk=C,where Ak denotes the amplitude factor, hk denotes the vector of the k-th grid in the derivative space, r denotes the position vector of the Euclidean space, λk denotes the periodic wavelength value of the function, pk denotes the function phase offset, and C denotes a constant.Based on equation (1), in order to obtain richer porous structural units, a function or constant is usually added to the implicit surface function. Taking P surface as an example, a distance constant t is added to its constructor to form a new Pt surface, and its construction equation can be shown by the following equation:(2)fp=acosx+bcosy+ccosz+t,where distance constant t is used to express the value of the point distance on the minimal surface from the implicit function (fpx,t). When the distance t is smaller than a certain threshold, the surfaces represented by the implicit function are continuous, and the surface is graphically represented as shown in Figure 1(a). When the distance t is greater than a certain constant threshold, the surface represented by the implicit function will no longer be continuous, and the surface is graphically represented as shown in Figure 1(c). At this time, the implicit function is no longer suitable for modeling of a continuous porous structure. It is usually possible to obtain a porous structure model with different volume fractions by changing the value of t.Figure 1
P surfaces represented by implicit functions corresponding to different distance constants t: (a) 0.5; (b) 1; (c) 2.
(a)
(b)
(c)Three kinds of porous structural models were designed, and the values of parametert in the implicit function equations are shown in Table 1. The design specifications of the three cylinders were Φ8m×10mm, and the models are shown in Figure 2.Table 1
Porous implant model corresponding to different values of the parametert.
Models
1
2
3
Values of the parametert
−0.4
0
0.4
Diameter of pore (mm)
0.37
0.50
0.63Figure 2
Three kinds of porous structure models. (a) Model 1. (b) Model 2. (c) Model 3.
(a)
(b)
(c)


## 2.2. FEA Simulation

The finite element simulation (FEA) software ABAQUS was used to simulate and test the porous model. In the simulation process, the porous model was set to a linear, elastic, and homogeneous model. The elastic modulus of the part material was set to 105 GPa, Poisson’s ratio was 0.31, and the yield strength was set to 830 MPa. The loading values and boundary conditions for the model simulation were described in a previous article published by the author [24]. To facilitate the simulation analysis, a low-thickness cylinder was added to both ends of the porous structure to ensure that each porous structural model exerts the same force. A compressive stress of 30 MPa was applied at the top of the model. The bottom of the model is completely restrained and fixed. The porous model was mesh subdivided. Models 1, 2, and 3 were meshed with 968335, 833442, and 700461 tetrahedral elements, respectively. Through the calculation iteration, the strain and stress distribution of the model was finally obtained.


## 2.3. 3D Printing

The Ti6Al4V titanium alloy powder produced by the German EOS company was used as the printing powder material. The composition and mass fractions of the metal powder are shown in Table2.Table 2
Chemical composition of titanium alloy powder (% by mass fraction).
Material
Ti
Al
V
O
Fe
C
N
H
Content
Bal
6.00
4.00
0.15
0.10
0.03
0.01
0.01The specimens were fabricated with an SLM machine (EOSINT M290; EOS GmbH, Germany) using the optimized processing parameters (Table3). Selective laser melting of porous scaffolds is characterized by a controllable and precise layer-wise material addition process that allows generating complex structures by selectively melting successive layers of metal powder, using a focused and computer-controlled laser beam, as seen in Figure 3.Table 3
Optimized process parameters used in SLM fabrication.
Laser power
Scan speed
Hatch spacing
Layer thickness
Laser focus
Atmosphere
180 W
1200 mm/s
0.1 mm
0.03 mm
0.08 mm
ArFigure 3
Sketch map of SLM printing process.


## 2.4. Animal Experiment

A total of 6 male Bama minipigs were enrolled in this study (6 months old). All animal studies (including the euthanasia procedure which was performed using lidocaine and propofol) were done in compliance with the regulations and guidelines of the ethics committee of Drum Tower Hospital affiliated to Medical School of Nanjing University and conducted according to the ARRIVE and the IACUC guidelines.All the implants were implanted at the distal region and proximal region of the right tibia bone. Cefuroxime sodium was intramuscularly injected for 3 days after operation to avoid infection. Tetracycline hydrochloride and Calcein were injected for the following fluorescence observation. All animals were sacrificed at the 5th week after operation to measure the osseointegration between the implants and the surrounding bone tissue.


## 2.5. Performance Evaluation

Micro-CT scan, histological analysis, and biomechanical testing were used to observe the parts of the porous implant. The tibia bones were harvested and scanned in a M1001 micro-CT system (Hiscan Information Technology, Jiangsu, PRC) at 90 kV, 89μA, field of view (FOV) of 63.9 mm, and a nominal isotropic image voxel size of 62.4 μm. The obtained images were converted to DICOM files for the following analysis.The harvested femurs were fixed in formalin and then rinsed with distilled water, dehydrated through graded alcohols, and embedded in polymethyl methacrylate (PMMA) without decalcification. Thin sections of 30μm thickness were cut using a diamond-coated saw (310 CP; EXAKT, Germany). The sections were stained with Goldner trichrome staining and then observed using a fluorescence microscope (Olympus Corp., Tokyo, Japan).In order to test the bonding strength between the porous implant and the host bone, the porous implants were subjected to release experiment test, and the test principle is shown in Figure4(a). The removed sacrum samples were repaired and fixed on the test platform of the electronic dynamic and static material testing machine (ElectroPuls 3000, Instron, USA). The top punch of the test instrument was vertically aligned with the porous metal implant. During the test, a slow feed was applied at a loading speed of 0.1 mm/s, as shown in Figure 4(b).Figure 4
Pushout test of implant. (a) Schematic diagram of the pushout test and (b) the device of release experiment.
(a)
(b)


## 3. Results

### 3.1. Physical Characteristic

The EOS metal 3D printing device was used to print the designed porous structure model, and the printed porous titanium alloy parts are shown in Figure5. Figure 5(a) is a side view of the printed parts, and Figure 5(b) is a top view of the printed parts. By observing, the parts are structurally complete, without missing or collapse. The surface of the part has fine pores in addition to the designed holes, and the surface roughness of the parts is high.Figure 5
3D printed titanium porous parts. (a) Side view of the printed parts. (b) Top view of the printed parts.
(a)
(b)Figure6 shows the SEM images of the printed porous parts. It can be seen from the figure that the pore structure of the three structures are different in size. Through measurement, the diameters of the holes in samples 1, 2, and 3 are about 382 μm, 513 μm, and 618 μm, respectively. These structural modalities are fully consistent with the model design structure, which infers that the printing accuracy is completely satisfied with the design requirements. In addition, as can be seen from the SEM images, there are fine microstructures on the surface of the part, and the diameters are about 10–100 μm. According to studies, these types of pore structures are very favorable for the adhesion and proliferation of bone tissue cells.Figure 6
SEM images of the printed porous parts. (a) Model 1. (b) Model 2. (c) Model 3.
(a)
(b)
(c)


### 3.2. FEA Result

Compression performance is a very important mechanical indicator of porous implants. In Figure7, the simulation test results show that the designed porous structure exhibits different mechanical properties. As the pore morphology changed, the resulting stress conditions also changed. The compression experiment results show that the stress cloud diagram of each model has its own characteristics by applying the same effect of compressive stress. With the increase of pressure load, the maximum stress values in Model 1, Model 2, and Model 3 gradually increased, which were 188.41 MPa, 285.25 MPa, and 385.30 MPa, respectively.Figure 7
Stress cloud of porous structure compression simulation. (a) Model 1. (b) Model 2. (c) Model 3.
(a)
(b)
(c)During the experiment, the total compressive deformation of Model 1 is the smallest of the three models. Due to the smallest structural pore size, the overall compressive stress experienced by the model is approximately evenly divided, and the maximum stress in Model 1 is also the smallest. On the contrary, the total compressive deformation of Model 3 is the largest, the model pore is the largest, and the compressive strength of the model structure is the weakest. Under the same load conditions, Model 3 was first crushed, indicating that the parts with larger pore diameters in the internal pore structure of the model have poor pressure resistance. According to the simulation data, the apparent elastic modulus of Model 1 is the largest, Model 3 is the smallest, and the characteristics of Model 2 are between Model 1 and Model 3. Among them, the apparent elastic modulus of Model 3 is the closest to the elastic modulus of bone tissue.


### 3.3. Osseointegration Properties

The results of pushout test to verify the osseointegration properties of porous implants are shown in Figure8. It shows the bending stress and strain curves of the samples, and the curve is close to the bending strength curve of bone. All samples have a period of linear elastic strain. When a certain maximum value is reached, the curve turns. At this time, the implant should be slid in the host bone under the action of thrust and finally pushed out with the continuous application of thrust. The stress and strain curves of Sample 1 and Sample 2 are similar. The entire curve of Sample 3 is shifted, which may be caused by the false preloading of Sample 3 when the implant part is clamped on the test equipment. In the figure, the curves of the initial elastic phases of the three structures are basically close. This is due to the fact that the implants of the implant and the host bone are relatively firm at the initial stage. The curve at this time mainly represents the bending characteristics of the bone tissue when compressed. The experimental results showed that the strength of Sample 3 combined with the bone tissue was the best, its ultimate pushout stress reached 27 MPa, the implant basically had no slippage during the pushout process, and the whole process had a good linearity. The bond strength between Sample 2 and bone tissue is relatively weak, and its ultimate pushout stress is about 22.5 MPa. Sample 1 also had a large ultimate pushing stress, but slip occurred during its ejection.Figure 8
Osseointegration properties of the samples.


### 3.4. Histological Analysis

The growth situation of the bone tissue around the implanted scaffolds is shown in Figure8. Figure 9(a) shows the micro-CT image of the tibia bones with the implanted porous scaffolds, the areas indicated by the arrow in the figure indicate the formation of the new bone. The results of fluorescent staining of the scaffold bone tissue section are shown in Figure 9(b). It can be seen that the new born osteogenic tissue are tightly wrapped around the porous scaffolds, and the new growth bone can be observed from inside the pores of the scaffolds. Figure 9(c) shows the results of hard tissue section staining in which the black areas represent the scaffold and the blue-green areas represent the new bone tissue. From the above three detection methods, the tight bond between the new bone and the porous scaffolds can be observed, and the bone can also be found to grow inside the scaffolds. This is also the reason for the excellent performance of the launch force in biomechanical testing.Figure 9
The growth situation of the bone tissue around the implanted scaffolds. (a) Micro-CT image of the tibia bones with the implanted porous scaffolds; (b) results of fluorescent staining of the scaffold; (c) the results of hard tissue section staining.
(a)
(b)
(c)


## 3.1. Physical Characteristic

The EOS metal 3D printing device was used to print the designed porous structure model, and the printed porous titanium alloy parts are shown in Figure5. Figure 5(a) is a side view of the printed parts, and Figure 5(b) is a top view of the printed parts. By observing, the parts are structurally complete, without missing or collapse. The surface of the part has fine pores in addition to the designed holes, and the surface roughness of the parts is high.Figure 5
3D printed titanium porous parts. (a) Side view of the printed parts. (b) Top view of the printed parts.
(a)
(b)Figure6 shows the SEM images of the printed porous parts. It can be seen from the figure that the pore structure of the three structures are different in size. Through measurement, the diameters of the holes in samples 1, 2, and 3 are about 382 μm, 513 μm, and 618 μm, respectively. These structural modalities are fully consistent with the model design structure, which infers that the printing accuracy is completely satisfied with the design requirements. In addition, as can be seen from the SEM images, there are fine microstructures on the surface of the part, and the diameters are about 10–100 μm. According to studies, these types of pore structures are very favorable for the adhesion and proliferation of bone tissue cells.Figure 6
SEM images of the printed porous parts. (a) Model 1. (b) Model 2. (c) Model 3.
(a)
(b)
(c)


## 3.2. FEA Result

Compression performance is a very important mechanical indicator of porous implants. In Figure7, the simulation test results show that the designed porous structure exhibits different mechanical properties. As the pore morphology changed, the resulting stress conditions also changed. The compression experiment results show that the stress cloud diagram of each model has its own characteristics by applying the same effect of compressive stress. With the increase of pressure load, the maximum stress values in Model 1, Model 2, and Model 3 gradually increased, which were 188.41 MPa, 285.25 MPa, and 385.30 MPa, respectively.Figure 7
Stress cloud of porous structure compression simulation. (a) Model 1. (b) Model 2. (c) Model 3.
(a)
(b)
(c)During the experiment, the total compressive deformation of Model 1 is the smallest of the three models. Due to the smallest structural pore size, the overall compressive stress experienced by the model is approximately evenly divided, and the maximum stress in Model 1 is also the smallest. On the contrary, the total compressive deformation of Model 3 is the largest, the model pore is the largest, and the compressive strength of the model structure is the weakest. Under the same load conditions, Model 3 was first crushed, indicating that the parts with larger pore diameters in the internal pore structure of the model have poor pressure resistance. According to the simulation data, the apparent elastic modulus of Model 1 is the largest, Model 3 is the smallest, and the characteristics of Model 2 are between Model 1 and Model 3. Among them, the apparent elastic modulus of Model 3 is the closest to the elastic modulus of bone tissue.


## 3.3. Osseointegration Properties

The results of pushout test to verify the osseointegration properties of porous implants are shown in Figure8. It shows the bending stress and strain curves of the samples, and the curve is close to the bending strength curve of bone. All samples have a period of linear elastic strain. When a certain maximum value is reached, the curve turns. At this time, the implant should be slid in the host bone under the action of thrust and finally pushed out with the continuous application of thrust. The stress and strain curves of Sample 1 and Sample 2 are similar. The entire curve of Sample 3 is shifted, which may be caused by the false preloading of Sample 3 when the implant part is clamped on the test equipment. In the figure, the curves of the initial elastic phases of the three structures are basically close. This is due to the fact that the implants of the implant and the host bone are relatively firm at the initial stage. The curve at this time mainly represents the bending characteristics of the bone tissue when compressed. The experimental results showed that the strength of Sample 3 combined with the bone tissue was the best, its ultimate pushout stress reached 27 MPa, the implant basically had no slippage during the pushout process, and the whole process had a good linearity. The bond strength between Sample 2 and bone tissue is relatively weak, and its ultimate pushout stress is about 22.5 MPa. Sample 1 also had a large ultimate pushing stress, but slip occurred during its ejection.Figure 8
Osseointegration properties of the samples.


## 3.4. Histological Analysis

The growth situation of the bone tissue around the implanted scaffolds is shown in Figure8. Figure 9(a) shows the micro-CT image of the tibia bones with the implanted porous scaffolds, the areas indicated by the arrow in the figure indicate the formation of the new bone. The results of fluorescent staining of the scaffold bone tissue section are shown in Figure 9(b). It can be seen that the new born osteogenic tissue are tightly wrapped around the porous scaffolds, and the new growth bone can be observed from inside the pores of the scaffolds. Figure 9(c) shows the results of hard tissue section staining in which the black areas represent the scaffold and the blue-green areas represent the new bone tissue. From the above three detection methods, the tight bond between the new bone and the porous scaffolds can be observed, and the bone can also be found to grow inside the scaffolds. This is also the reason for the excellent performance of the launch force in biomechanical testing.Figure 9
The growth situation of the bone tissue around the implanted scaffolds. (a) Micro-CT image of the tibia bones with the implanted porous scaffolds; (b) results of fluorescent staining of the scaffold; (c) the results of hard tissue section staining.
(a)
(b)
(c)


## 4. Discussion

In the present study, we developed several porous implant models with controlled pore structure, and the apparent elastic modulus of the porous implant model can be regulated by adjusting the parameters.There are many factors that affect the growth of bone tissue into porous implants, and the pore morphology, pore size, and implant biocompatibility are all important factors affecting osseointegration. The porous structure in the implant not only mechanically locks the interface between the implant and the host bone, but it can also promote the proliferation of osteoblasts when the pore size can be reduced to the cellular level (1–100μm). The porous titanium alloy implant components designed and printed in this study have complex pore structures. The experimental results show that three types of porous titanium alloy implant components can be combined with bone tissue after implantation. According to the pushout test, Sample 3 has the best bonding strength among all implanted parts. There may be two reasons: on the one hand, the pore size in Sample 3 is suitable for bone tissue growth, and on the other hand, the mechanical properties of Sample 3 are close to those of bone tissue, which can promote bone tissue growth and avoid stress-shielding between bone and implanted parts.Traditional scaffold fabrication methods such as solvent casting, gas pore forming, and electrospinning often fail to produce satisfactory three-dimensional scaffolds and internal microstructures. 3D printing technology can print out scaffolds with good mechanical properties, adjustable pores, and complex spatial structures. With the advent of 3D printing technology, scaffolds with porous structures designed by different methods can be manufactured. A traditional porous design method cannot achieve the ideal structure of scaffold design. In this study, the porous scaffold based on TPMS parameterized construction has continuous curvature and controllable pore structure, which can promote the growth of bone tissue [25–27].At present, one of the main causes of bone graft loosening is that the bond between the graft and the bone is not firm. In this study, an integrated porous bone-promoting graft was made directly through the TPMS design method and 3D printing technology. It was verified by the mechanical test and animal implantation experiments. The experimental results show that the apparent elastic modulus of the porous structure scaffold is close to that of the bone tissue, which can effectively reduce the stress shielding effect. And the pushout test results show that the designed porous structures have a good osseointegration effect.


## 5. Conclusion

The porous titanium alloy implants studied in this study can improve the interface area between the porous implant and the host bone, and the porous structure of the interconnecting pores in the porous titanium alloy can provide an effective channel for the vascularization of bone tissue, which provides the necessary conditions for the growth of bone tissue. In addition, the mechanical property mismatch between the implant and the host bone is a major cause of the resulting stress-shielding effect at the binding interface, which is also responsible for the loosening of implant components after implantation. The porous structure designed in this paper can effectively regulate the apparent elastic modulus of the porous implant. By making the elastic modulus between the implant and the host bone close, the feature facilitates the conduction of stress at the interface, which reduces or eliminates stress shielding between the implant and the host bone. Therefore, a suitable structure of the porous implant is more conducive to the formation of osseointegration of the implant and the bone tissue, which has practical significance for improving the initial and long-term stability of the implant. The method brings new ideas for clinical treatment.



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*Source: 5268280-2019-10-09.xml*