An innovative biofabrication technique was developed to engineer three-dimensional constructs that resemble the architectural features, components, and mechanical properties of in vivo tissue. This technique features a newly developed sacrificial material, BSA rubber, which transfers detailed spatial features, reproducing the in vivo architectures of a wide variety of tissues.
Tissue scaffolds play a crucial role in the tissue regeneration process. The ideal scaffold must fulfill several requirements such as having proper composition, targeted modulus, and well-defined architectural features. Biomaterials that recapitulate the intrinsic architecture of in vivo tissue are vital for studying diseases as well as to facilitate the regeneration of lost and malformed soft tissue. A novel biofabrication technique was developed which combines state of the art imaging, three-dimensional (3D) printing, and selective enzymatic activity to create a new generation of biomaterials for research and clinical application. The developed material, Bovine Serum Albumin rubber, is reaction injected into a mold that upholds specific geometrical features. This sacrificial material allows the adequate transfer of architectural features to a natural scaffold material. The prototype consists of a 3D collagen scaffold with 4 and 3 mm channels that represent a branched architecture. This paper emphasizes the use of this biofabrication technique for the generation of natural constructs. This protocol utilizes a computer-aided software (CAD) to manufacture a solid mold which will be reaction injected with BSA rubber followed by the enzymatic digestion of the rubber, leaving its architectural features within the scaffold material.
In the tissue engineering field the ability to fabricate tissue scaffolds is vital. A suitable tissue scaffold has a 3D structure, is composed of biocompatible materials, and mimics in vivo tissue architecture to facilitate cell and tissue growth and remodeling. This scaffold must allow the transport of nutrients and the removal of wastes1-4. One of the main obstacles in the production of these scaffolds is the ability to recapitulate specific geometrical features into a biocompatible material. Several biofabrication techniques have been reported to control the geometrical features of these scaffolds, examples are electrospinning5-8, solvent-casting9, stereolithography10, and 3D-printing11, among others. These techniques fall short in providing a relatively easy transfer of controllable internal and external architectural features, are expensive, are limited by their resolution and printability (e.g., nozzle gauge, material restriction), or require post-fabrication techniques which demands a long period of time to produce viable scaffolds12.
In many commercial fabrication systems, the creation of internal voids, channels, and features is achieved using sand or other suitable removable or sacrificial materials. The metal or plastic part is formed around the sand mold, and once it is solidified, the sand is removed. In much the same manner, the next generation of biomaterials needs the biosand equivalent. Therefore, the BSA rubber was developed as a substitute for biosand. The BSA rubber is a newly formulated material that consists of bovine serum albumin crosslinked with glutaraldehyde. The ultimate goal is to recreate specific architectural features into a biodegradable collagen scaffold. The characteristics of the sacrificial biorubber that maintains dimensional fidelity with the mold of the original tissue are described.
Several combinations of BSA and glutaraldehyde concentrations were tested using a variety of solvents. This material was created by the reaction between BSA and glutaraldehyde. BSA rubber can be reaction injected into the intricate geometries of the tissue molds. Crosslinked BSA is trypsin labile and readily digested by the enzyme at mild pH and temperature conditions. Conversely, intact type I collagen is very resistant to trypsin digestion. These features were capitalized to selectively remove the BSA rubber leaving the collagen behind. The present work consisted of determining the ideal parameters needed to obtain a labile mold that can deliver specific architectural features to a biocompatible scaffold. The specific features that were evaluated included mixability, enzyme digestion, load bearing, and ability to be reaction injected into a negative mold. The combination of 30% BSA and 3% glutaraldehyde fulfills these requirements. This protocol provides the necessary guidelines to create these three-dimensional scaffolds. The prototype consists of a collagen scaffold that represents a branched architecture with one inflow and two outflow channel with diameters of 4- and 3-mm, respectively. This technique has the potential to mimic macro- and micro-environments of the tissue of interest. This technology provides a viable technique to deliver a specific geometrical instructive to a biodegradable material in a relatively easy and timely matter with high fidelity, which can be tuned to mimic the in vivo tissue elasticity and other characteristics of the tissue of interest.
1. Determine the Percentage of Solids in the Collagen Batch
2. Preparation of the BSA Rubber
3. Molds Treatment
Note: The prototype described in this paper uses a custom made stainless steel Y mold piece. The mold contains an inflow and two outflow channels of 4 and 3 mm, respectively. First, clean molds, spray them with unsaturated lard, and sterilize them. Prepare the molds following the procedure described below.
4. Reaction Injection of the BSA Rubber
Note: All the materials and solution should be keep cold until ready to use to prevent premature setting of the BSA rubber in the next steps.
5. Adjusting the Collagen Concentration
Note: The collagen should be kept on ice at all times during the process.
6.Casting Collagen on BSA Rubber
7. Enzyme Digestion of the BSA Rubber
The results demonstrate that this biofabrication technique is efficient in generating 3D scaffolds that can mimic the spatial arrangement seen in in vivo tissue. The architectural features are vital parameters for tissue engineering application, playing a crucial role in the in vivo cell interaction and functionality of the tissue.
The consistency and mixability of the BSA rubber was an important parameter in producing a BSA rubber that is homogeneous and is able to maintain its intended shape. The solubility of proteins is determined by intermolecular effects, such as the protein-protein interaction, and the interaction with the solvent, which induces changes on the overall protein behavior. The conductivity of the BSA solution was measured, which is an indication of the salt concentration of the solutions. Table 1 lists the combinations of BSA, solvent, and glutaraldehyde tested. As expected, the samples that had the highest conductivity (2x PBS solvent) facilitated the solubility of the BSA.
Another parameter used to determine the appropriate condition for the development of this sacrificial material was the reaction rate. The reaction time of the BSA decreased as the concentration of glutaraldehyde increased, as expected. The fixative reacts with the α-amino groups of the amino acids, the N terminal amino group of peptides, and the sulfhydryl group of cysteine. The glutaraldehyde reacts predominantly with the BSA through the amino groups of lysine to form the intermolecular covalent bonds (Figure 1A) 14. After an incubation period, the samples showed a color change from pale yellow to dark yellow and brown, increasing in intensity with increased glutaraldehyde concentration (Figure 1B). The 20%, 30%, and 40% BSA with 2% glutaraldehyde in water did not form a rubber. The 40% BSA solution, due to its high viscosity and the highly reactive fixative, resulted in varying strength along the rubber. This behavior can be caused by the difficulty of the glutaraldehyde in penetrating the protein chains homogeneously. The solvent greatly influenced the solubility of the protein as well as its reaction with the fixative. The 2x PBS solutions were easily mixable. The BSA solution with water was difficult to mix. BSA solubility is greatly affected by the conductivity of the solvent (Table 2), causing conformational changes in the protein. The most promising samples were the 30% BSA with 3% glutaraldehyde in 1x PBS and 2x PBS.
To ensure that the rubber was able to sustained loading forces, a compression test was performed. The mechanical properties of four samples of BSA rubber were measured: 30% BSA 3% glutaraldehyde in 2x PBS, 30% BSA 3% glutaraldehyde in 1x PBS, 20% BSA 3% glutaraldehyde in 2x PBS and 20% BSA 2% glutaraldehyde in 1x PBS. The sine waves showed a very small phase change between the load and displacement curves (Supplement Figure 2) that are transferred to the stress and strain curves (Supplement Figure 3). Based on the stress and strain curves, the first three samples showed hysteresis in between loading and unloading (Figure 2A-2C). These three specimens behaved as a viscoelastic material that contains elastic and viscous properties when forces were applied. The 20% BSA 2% glutaraldehyde showed signs of permanent deformation (Figure 2D). The 30% BSA 3% glutaraldehyde in 1x PBS and 2x PBS showed a similar behavior (Figure 2E-one loading and unloading cycle). The elastic modulus was determined from the linear portion of these four samples (Figure 2F). The concentration of the phosphate solvent significantly increased the elastic modulus at the range tested (p=0.03). The 20% BSA 2% glutaraldehyde in 1x PBS deformed easily, showing a lower elastic modulus.
To evaluate the enzymatic digestion of the rubber, the reaction rate was calculated based on the disappearance of the BSA rubber when placed in contact with the enzyme at specific time point. The enzymatic digestion process was treated as a batch reactor. A comparison between the starting rubber concentration prior to treatment and the rubber left after being lyophilized was made to obtain the kinetics of the digestion. Figure 3 shows the rate of reaction for each sample in relation to the concentration of glutaraldehyde and BSA, solvent, and the residence time. A clear trend was observed between the crosslinker concentrations and the reaction rate of dissociation of the entity. Statistical analysis was performed at each time point. For the 15-hr time point, the glutaraldehyde concentration significantly affected the reaction rate resulting in a p value of 0.02 (Supplement Table 4). After that time point, both the glutaraldehyde and the BSA concentration significantly affected the rate (Supplement Table 5-7). The most influential factor overall was the glutaraldehyde concentration, indicated by a more significant p value. The increase in glutaraldehyde concentration decreased the reaction rate of the digestion of the rubber entity.
The amount of protein dissolved by trypsin was determined using a BCA assay (Figure 4). A common trend was observed: the lower the concentration of the fixative, the more protein was digested from the BSA rubber. Trypsin interacted with the rubber sample by cleaving the BSA and the newly created covalent bonds formed by the glutaraldehyde, thus dissolving the overall structure over time. It seems that with the 1x PBS there is more solubilized protein at an earlier time point compared to the 2x PBS. Over time, there is an increase of proteins in solution at 15 hr, which continued to increase until 48 hr and then it decreased. This might be due to the trypsin constantly cleaving the proteins and, thus, creating smaller peptides and amino acids. It can also be attributed to the assay's limitations, which can only read peptides that are composed of three or more amino acids. Statistical analysis showed that the BSA and glutaraldehyde concentration significantly affected the release of the protein from the BSA rubber (p<0.05). An increase in BSA concentration caused an increase of protein in the supernatant, while an increase in glutaraldehyde caused a decrease in dissolved protein.
To measure the dissociation of this sacrificial material, the rubber was weighed (wet basis) before placing it in contact with the trypsin. The equivalent of dry weight of the rubber placed in the enzyme digestion solution was determined using the values shown in Supplement Figure 1. The enzyme solution reacted with the BSA rubber, and thus, solubilized the protein. The rubber remaining after the treatment was lyophilized O/N and weighed. Figure 5 shows that the solvent influenced the dissociation of the rubber. At the same concentration of BSA and glutaraldehyde, the 2x PBS solvent rubbers retained more of their material compared to the 1x PBS.
Three solid mold pieces were fabricated: Loop Mold (Supplement Figure 4A), Stability Piece (Supplement Figure 4B), and Y Mold (Figure 6A, left). The stainless steel Y mold piece was created using the Microlution machine (Figure 6A, right). This mold was reaction injected with 30% BSA and 3% glutaraldehyde in 2x PBS (Figure 6B, left). The rubber was allowed to react O/N at 4 °C. The rubber was casted with collagen (Figure 6B, center) and then enzyme digested (Figure 6B, right). Preliminary data suggested that at pH 7.8 and a temperature of 30 °C for 15 hr, the BSA rubber can be digested with minimal impact on the collagen scaffold. After 15 hr, the rubber is weakened by the enzyme and loose enough that it leaves the channels without affecting the geometrical features of the collagen. A 3D collagen scaffold was created that has specific geometrical features. Figure 6B (right) shows a 4 mm diameter channel inside a collagen hydrogel after enzyme digestion of the BSA rubber. The channel was measured with a caliper to ensure that the original dimension was maintained. Indeed, the new channel in the collagen hydrogel was 4 mm. The BSA rubber molds can hold dimensions as small as 300 µm, which was tested using the stability mold (Figure 7). These scaffolds were tested for residual glutaraldehyde and we found no residue after the Mosconas washes.
Figure 1. BSA rubber. (A) BSA rubber reaction. The glutaraldehyde crosslinks the BSA by creating covalent bonds. (B) BSA Rubber. Different concentrations of BSA, concentrations of glutaraldehyde, and type of solvent were casted on 24-well plates and reacted O/N at 4 °C. Please click here to view a larger version of this figure.
Figure 2. Stress-Strain curves of BSA rubbers. Stress-Strain curves of BSA rubbers. (A) 30% BSA 3% glutaraldehyde in 2x PBS; (B) 30% BSA 3% glutaraldehyde in 1x PBS; (C) 20% BSA 3% glutaraldehyde in 2x PBS; and (D) 20% BSA 2% glutaraldehyde in 1x PBS (3 cycles). The curves A-C show rubbers that have some hysteris, but return to their original shape. Sample D shows a rubber with a very low elastic modulus that easily deforms permanently during the loading and unloading processes. Sample A and B showed a very similar behavior as seen in one loading and unloading cycle on graph E (representative of one cycle of each sample). The elasticity was influenced by the concentration of the fixative and the solvent used (F). The samples displayed a significant increase in modulus with an increase of salts (**p<0.05). A higher fixative concentration caused a significant increase in the elasticity of the BSA rubbers (*p<0.05). Please click here to view a larger version of this figure.
Figure 3. Reaction rate of the disintegration of the BSA rubber. As the fixative increases, the reaction rate decreases for all samples in 1x PBS (A), 2x PBS (B), and water (C). The 40% BSA 2% glutaraldehyde in 2x PBS shows one of the highest rates of reaction. This is due to the difficulty encountered in making the BSA protein homogeneous. (blue: 20% BSA, purple: 30% BSA, and red: 40% BSA). Please click here to view a larger version of this figure.
Figure 4. Protein quantification after enzyme digestion. As the fixative increases, the protein dissolved from the rubbers decreases for all samples in 1x PBS (A), 2x PBS (B), and water (C). (blue: 20% BSA, purple: 30% BSA, and red: 40% BSA). Please click here to view a larger version of this figure.
Figure 5. Rubber digestion. We determined the amount of rubber digested by comparing the starting and end dry basis products. We obtained the least amount of digestion on the 6% glutaraldehyde sample and the most at 30% BSA 2% glutaraldehyde in 1x PBS. Please click here to view a larger version of this figure.
Figure 6. Branched prototype. (A) Representation of branch vasculature. Shown on the left is the solid created in Mastercam which was converted to G Code and fabricated using the Microlution 363-S as seen on the right. The stainless steel mold piece represents a 4 mm inflow channel with two-3mm outflow channels. (B) 3D collagen scaffold. Shown on the left is the BSA rubber made using the mold shown above. The center shows the rubber embedded in the collagen hydrogel. Shown on the right are the channels left within the collagen scaffold after the rubber was enzyme digested. Please click here to view a larger version of this figure.
Figure 7. BSA channel. A 300 µm BSA channel was removed from the stability piece mold. There is a thin layer of mold release agent around the channel. The additional area is clearly distinguished under a microscope and can be easily removed. Please click here to view a larger version of this figure.
BSA (%) | Glutaldehyde (%) |
20 | 2 |
20 | 3 |
20 | 6 |
30 | 2 |
30 | 3 |
30 | 6 |
40 | 2 |
40 | 3 |
40 | 6 |
Table 1. BSA rubber parameters. BSA and fixative were mixed at a 4:1 ratio using three different solvents.
Sample | Conductivity (mS/cm) | pH | |
BSA (%) | Solvent | ||
30 | 2x PBS | 11.43 | 7.06 |
30 | 1x PBS | 6.35 | 7.05 |
30 | DI | 2.39 | 6.76 |
20 | 2x PBS | 13.00 | 6.92 |
20 | 1x PBS | 8.67 | 7.09 |
20 | DI | 2.08 | 6.90 |
Table 2. Conductivity and pH of BSA samples. The conductivities and pH of the BSA solutions was measured in the presence of different solvents. An increase in conductivity is shown between 2x and 1x PBS.
BSA (%) | Glutaraldehyde (%) | Solvent | Observations | |||
20 | 2 | 1x PBS | Soft, easy deformable material | |||
20 | 3 | 1x PBS | Soft but more sturdy than the 2% glutaraldehyde | |||
20 | 6 | 1x PBS | Stiff, a little brittle | |||
30 | 2 | 1x PBS | Good consistency | |||
30 | 3 | 1x PBS | Good consistency | |||
30 | 6 | 1x PBS | Brittle | |||
40 | 2 | 1x PBS | Very inconsistent in creating a gel/rubber consistency | |||
40 | 3 | 1x PBS | The consistency vary along the sample | |||
40 | 6 | 1x PBS | Brittle | |||
20 | 2 | 2x PBS | Soft, easy deformable material but more sturdy than the 1x PBS sample | |||
20 | 3 | 2x PBS | Soft but stiffer than the 2% | |||
20 | 6 | 2x PBS | Good consistency | |||
30 | 2 | 2x PBS | Good consistency, more studry than with 1x PBS | |||
30 | 3 | 2x PBS | Good consistency, more studry than with 1x PBS | |||
30 | 6 | 2x PBS | Good mixability but britle | |||
40 | 2 | 2x PBS | The consistency vary along the sample | |||
40 | 3 | 2x PBS | The consistency vary along the sample | |||
40 | 6 | 2x PBS | The consistency vary along the sample and it was brittle | |||
20 | 2 | Water | Did not form a gel/rubber material | |||
20 | 3 | Water | Formed a gel but seem stiffer than the 1x PBS and 2x PBS, inconsistent | |||
20 | 6 | Water | Formed a gel but seem stiffer than the 1x PBS and 2x PBS, inconsistent | |||
30 | 2 | Water | Did not form a gel/rubber material | |||
30 | 3 | Water | Formed a gel but seem stiffer than the 1x PBS and 2x PBS, inconsistent | |||
30 | 6 | Water | Formed a gel but seem stiffer than the 1x PBS and 2x PBS, inconsistent | |||
40 | 2 | Water | Did not form a gel/rubber material | |||
40 | 3 | Water | The consistency vary along the sample — stiffer on top | |||
40 | 6 | Water | The consistency vary along the sample — stiffer on top |
Table 3. BSA rubber. After the BSA rubber reacted O/N, an 8-mm biopsy punch hole of the sample was taken. This table contains some visual observations of the consistency and appearance of the samples.
Supplement Figure 1. Solid percentage. The percentage of solids from each rubber was determined (dry weight/wet weight). The solvent did not affect the percentage of solids (p>0.05). Please click here to download this file.
Supplement Figure 2. Sine wave of 30% BSA 3% glutaraldehyde 2x PBS. The compressive load and displacement of the sample are shown as functions of the elapsed time. Please click here to download this file.
Supplement Figure 3. Sine wave of 30% BSA 3% glutaraldehyde 2x PBS. The stress and strain of the sample were calculated and plotted as a function of elapsed time. There is a small phase shift, indicative of the viscoelastic behavior of the rubber. Please click here to download this file.
Supplement Figure 4. Mastercam solids. (A) Loop and (B) stability pieces. After designing these using Mastercam, the G code was imported and a stainless steel or brass piece using the Microlution machine or a PLA piece using the Makerbot 3D Replicator. Please click here to download this file.
Limits | Min | Max | ||
Load (N) | -17 | 3 | ||
Displacement (mm) | -1.5 | 0.3 | ||
Wave | Level 1 | Level 2 | Frequency (Hz) | Cycle |
Sine | -15 | -3 | 1 | 5,000 |
Data Acquisition | ||||
Scan time | 1.008 | |||
Scan points | 360 | |||
Number of Scans | 5 | |||
Subsequent Scan | 1.008 sec between scan |
Supplement Table 1. Compression testing parameters. Using a sine wave, the relationship between the load and displacement was determined for the four types of rubber. Please click here to download this file.
ANOVA Results | |||||
df | SS | MS | F | Significance F | |
Regression | 3 | 9.85E+02 | 3.28E+02 | 4.70E+02 | 1.06E-18 |
Residual | 20 | 1.40E+01 | 6.99E-01 | ||
Total | 23 | 9.99E+02 | |||
Regression Analysis | |||||
Coefficients | Standard Error | t Stat | P-value | ||
Intercept | 1.74E+00 | 8.23E-01 | 2.12E+00 | 4.70E-02 | |
BSA (%) | 7.82E-01 | 2.09E-02 | 3.74E+01 | 5.49E-20 | |
Glutaraldehyde (%) | 3.17E-01 | 1.03E-01 | 3.09E+00 | 5.71E-03 | |
Solvent | 2.61E+01 | 2.22E+01 | 1.18E+00 | 2.53E-01 |
Supplement Table 2. Statistical analysis of the percentage of solids in the BSA rubber. The BSA and glutaraldehyde significantly affected the percentage of solids. The solvent did not influence the percentage of solids. Please click here to download this file.
ANOVA Results | |||||
df | SS | MS | F | Significance F | |
Regression | 3 | 3.06E+05 | 1.02E+05 | 1.18E+01 | 4.00E-03 |
Residual | 7 | 6.07E+04 | 8.67E+03 | ||
Total | 10 | 3.67E+05 | |||
Regression Analysis | |||||
Coefficients | Standard Error | t Stat | P-value | ||
Intercept | 6.50E+02 | 4.25E+01 | 1.53E+01 | 1.23E-06 | |
BSA (%) | 4.67E+00 | 3.80E+01 | 1.23E-01 | 9.06E-01 | |
Solvent | 1.02E+02 | 3.80E+01 | 2.67E+00 | 3.20E-02 | |
Glutaraldehyde (%) | 1.16E+02 | 5.70E+01 | 2.03E+00 | 8.21E-02 |
Supplement Table 3. Statistical analysis of the elastic modulus related to the PBS concentration. The PBS concentration significantly affected the elastic modulus. The increase of salts in the solvent caused an increase in the elastic modulus. Please click here to download this file.
ANOVA Result | |||||
df | SS | MS | F | Significance F | |
Regression | 3 | 6.15E-15 | 2.05E-15 | 3.68E+00 | 1.67E-02 |
Residual | 60 | 3.34E-14 | 5.57E-16 | ||
Total | 63 | 3.96E-14 | |||
Regression Analysis | |||||
Coefficients | Standard Error | t Stat | P-value | ||
Intercept | 3.74E-08 | 1.37E-08 | 2.74E+00 | 8.03E-03 | |
BSA (%) | 3.89E-10 | 3.62E-10 | 1.07E+00 | 2.88E-01 | |
Glutaraldehyde (%) | -5.92E-09 | 1.83E-09 | -3.23E+00 | 2.02E-03 | |
Solvent | -6.78E-08 | 3.76E-07 | -1.80E-01 | 8.58E-01 |
Supplement Table 4. Statistical analysis of the reaction rate after 15 hr of enzyme digestion. The glutaraldehyde concentration significantly affected the reaction rate of the digestion of the rubber by decreasing at higher glutaraldehyde concentrations. Please click here to download this file.
ANOVA Results | |||||
df | SS | MS | F | Significance F | |
Regression | 3 | 7.36E-15 | 2.45E-15 | 3.62E+01 | 1.21E-13 |
Residual | 62 | 4.20E-15 | 6.78E-17 | ||
Total | 65 | 1.16E-14 | |||
Regression Analysis | |||||
Coefficients | Standard Error | t Stat | P-value | ||
Intercept | 2.98E-08 | 4.77E-09 | 6.25E+00 | 4.22E-08 | |
BSA (%) | 4.56E-10 | 1.26E-10 | 3.62E+00 | 6.03E-04 | |
Glutaraldehyde (%) | -6.04E-09 | 6.15E-10 | -9.82E+00 | 3.00E-14 | |
Solvent | -6.57E-08 | 1.31E-07 | -5.02E-01 | 6.17E-01 |
Supplement Table 5. Statistical analysis of the reaction rate after 24 hr of enzyme digestion. The BSA and glutaraldehyde concentration significantly affected the reaction rate of the digestion of the rubber. At higher glutaraldehyde concentrations, there is a decrease in the reaction rate. At higher BSA concentrations, there is an increase in the reaction rate. Please click here to download this file.
ANOVA Results | |||||
df | SS | MS | F | Significance F | |
Regression | 3 | 3.10E-15 | 1.03E-15 | 2.74E+01 | 1.64E-11 |
Residual | 64 | 2.42E-15 | 3.78E-17 | ||
Total | 67 | 5.52E-15 | |||
Regression Analysis | |||||
Coefficients | Standard Error | t Stat | P-value | ||
Intercept | 2.17E-08 | 3.50E-09 | 6.20E+00 | 4.55E-08 | |
BSA (%) | 2.13E-10 | 9.20E-11 | 2.31E+00 | 2.39E-02 | |
Glutaraldehyde (%) | -3.94E-09 | 4.53E-10 | -8.70E+00 | 1.90E-12 | |
Solvent | 3.04E-08 | 9.57E-08 | 3.18E-01 | 7.51E-01 |
Supplement Table 6. Statistical analysis of the reaction rate after 48 hr of enzyme digestion. The BSA and glutaraldehyde concentration significantly affected the reaction rate of the digestion of the rubber. At higher glutaraldehyde concentrations, there is a decrease in the reaction rate. Please click here to download this file.
ANOVA Results | |||||
df | SS | MS | F | Significance F | |
Regression | 3 | 2.19E-15 | 7.29E-16 | 3.05E+01 | 3.56E-12 |
Residual | 61 | 1.46E-15 | 2.39E-17 | ||
Total | 64 | 3.64E-15 | |||
Regression Analysis | |||||
Coefficients | Standard Error | t Stat | P-value | ||
Intercept | 1.05E-08 | 2.84E-09 | 3.69E+00 | 4.80E-04 | |
BSA (%) | 3.61E-10 | 7.48E-11 | 4.83E+00 | 9.48E-06 | |
Glutaraldehyde (%) | -3.07E-09 | 3.69E-10 | -8.33E+00 | 1.21E-11 | |
Solvent | 3.97E-08 | 7.80E-08 | 5.09E-01 | 6.12E-01 |
Supplement Table 7. Statistical analysis of the reaction rate after 72 hr of enzyme digestion. The BSA and glutaraldehyde concentration significantly affected the reaction rate of the digestion of the rubber. At higher glutaraldehyde concentrations, there is a decrease in the reaction rate. At higher BSA concentrations, there is an increase in the reaction rate. Please click here to download this file.
Biofabrication is a highly multidisciplinary field in which biology and engineering principles merge to generate complex materials that mimic native tissue. In order to achieve this, there is a need to develop techniques that use the information gathered from in vivo tissue and translate it into an in vitro scaffold. In this way, a platform can be engineered that closely resembles the architectural, functional, and mechanical properties of the in vivo tissue. The optimal scaffolding material should possess certain properties, such as being biocompatible, mimic the mechanical properties of the tissue of interest, be capable of controlled degradation, able to support cell viability, and capable of allowing tissue remodeling2,3.
A multitude of fabrication techniques have been developed to generate viable, three-dimensional constructs. These technologies fall into two major categories: conventional and advanced. The conventional techniques include the use of synthetic and natural traditional materials to make porous structures. Some examples are solvent-casting, freeze drying, and melt molding. Disadvantages of these techniques include poor control of porosity within the structure (pore size and pore interconnectivity) and difficulty making internal channels within the scaffolds. Advanced techniques include stereolithography, molding, 3D printing, and electrospinning, among others1. These techniques have drawbacks such as the lack of long-range microarchitecture channels, material selection to provide optimal mechanical strength while being capable of dispensing through small-diameter nozzles, optimization dependent on the material, require extensive post-processing that might be toxic, and restriction in the design of inner architectures in an in vitro construct. A major drawback in 3D printing is the availability of biomaterials that are adequate cell carriers, while also having the mechanical properties required to maintain a defined architectural organization12. The technology presented here incorporates both conventional and advanced fabrication techniques. The best of both worlds is derived from the convergence of computer-aided manufacturing to create, or import, the desired architecture with the development of an enzyme-labile rubber. The stainless steel molds were created using a milling machine, but their fabrication isn't limited to this technique. Using a 3D Printer (e.g., Makerbot), the same molds were fabricated from polylactic acid (PLA). The negative molds were milled using architectural directives designed by the CAD program, which provides solid molds that create an easy and reliable transfer of features to any material. This technology is significant in that it allows not only the control of the external tissue composition, but also of the highly complex internal architecture. The work presented here focuses primarily on the characterization of the BSA rubber, which can be mixed homogeneously, is easily digested in a reasonable amount of time, was resistant to alterations in its structure, and is able to mimic minute features, while holding its stability during the casting process. The limitation of this technique was tested and the sacrificial material's resolution can maintain dimensions as small as 300 µm in diameter. However, Figure 7 show that the channel is surrounded by a thin layer of mold release agent. Using a microscope, this additional area is clearly distinguished and can be removed to have the desired dimension. This biofabrication technique allows the replication of a wide variety of internal structures that range from macro- to micro-scale.
Serum albumin is the most abundant protein in the circulatory system. Since the proteins are polyelectrolytes, solubility was determined by electrostatic interactions15-17. It has been shown that at low salt concentrations, there is a salting-in effect on the protein facilitating its solubility18. Glutaraldehyde is a crosslinking agent that causes changes in the properties of albumin. The color change seen in Figure 1 is attributed to the formation of the aldimine linkages19-21. The glutaraldehyde reacts predominantly with the BSA through the amino groups of lysine to form the intermolecular covalent bonds14. Data indicates that the increase of salts improved the elasticity of the rubber (from 1x PBS to 2x PBS). The higher glutaraldehyde concentration produces stiffer gels that set earlier compared to low concentration ones. However, they are more difficult to dispense, mix homogenously, and they form brittle gels. To deliver the appropriate amount of BSA rubber into the molds, every part of the assembly must be kept cold because higher temperatures accelerate the glutaraldehyde and BSA reaction. The ideal rubber (30% BSA 3% glutaraldehyde in 2x PBS or 1x PBS) behaves as a viscoelastic material that can withstand loading without permanently deforming. This becomes very important when handling and casting material around the BSA rubber structure.
Trypsin is a serine protease that hydrolyzes proteins. Trypsin is a widely used enzyme that has high cleavage specificity. It cleaves the peptide chains mainly at the carboxyl side of the amino acids lysine and arginine22. BSA is readily soluble at low concentrations in water, and the trypsin readily digested the BSA rubber leaving the collagen intact and relatively untouched. The material will not have any contact with cells. The construct was tested for the presence of free glutaraldehyde and there were no traces of this fixative. This demonstrates the efficacy of the BSA rubber as a sacrificial material for biofabrication. In this protocol, collagen was used as the scaffold material, but any other material that is resistant to trypsin digestion could be used.
Future work will be focused on reconstituting the vascular components within the hydrogels by seeding the scaffold with endothelial and fibroblast cells. One of the challenges is to create a uniform distribution of cells throughout the inside of the channels that mimic the native 3D distribution. To address this issue, a strategy is being developed that allows the sealing or plugging of the channels and the injection of the cell suspension. The material tested is pluronic F127, which is a thermoreversible gel, liquid at 4 °C and a solid above 30 °C23,24. A high concentration of pluronic was successful in creating the necessary temporal seal. After the cell suspension is within the channels of the scaffold, the entity is rotated for a specific amount of time until the cells adhere to all sides of the 3D structure. The inside channel will have adequate media for maintaining cell survival. Pluronic maintains its gel form and is readily soluble in an aqueous environment. Once the cells adhere, the hydrogel will be flooded with media, and can be cultured in stationary or flow conditions, depending on the purpose of the study. This methodology will be further assessed and will become the follow up to this publication. The biofabrication technique described herein is currently being used to develop a scaffold replica of a human renal artery. The same approach could be done with other types of tissues, such as cardiac, to expand the applicability of this technique to a wide range of clinical applications.
The biofabrication technique developed here is a step forward in the generation of in vitro scaffolds that can recapitulate intrinsic geometrical features quickly and reliably. A natural material, such as collagen, was selected because it offers optimal chemical and physical cues to cells over synthetic materials. These natural materials can be used for therapeutic research, as in vitro models of development, malformation, and disease tissue, as well as for replacement of damaged tissue.
The authors have nothing to disclose.
This work was supported by NIH-NIDCR IRO1DE019355 (MJ Yost, PI), and NSF-EPSCoR (EPS-0903795).
Collagen type I | Collagen extracted from calf hide | ||
Hydrocloric Acid (HCl) | Sigma-Aldrich | 7647-01-0 | |
Phosphate Buffer Solution (PBS Tablets) | MP Biomedical | U5378 | 1 tablet per 100 mL makes 1XPBS |
Albumium from bovine serum (BSA) | Sigma-Aldrich | A9647 | |
Glutaraldehyde | Sigma -Aldrich | G5882 | Toxic |
Lard | Fields | 3090 | |
Stainless Steel Molds | Milled using Microlution Machine | ||
Air Brush Kit | Central Pneumatic | 47791 | |
Mixing Tip for double syringe | Medmix | ML2.5-16-LLM | Mixer, DN2,5X16, 4:1 brown, med |
Small O ring for double syringe | Medmix | PPB-X05-04-02SM | Piston B, 5mL, 4:1, PE natural |
Double Syringe cap | Medmix | VLX002-SM | Cap, 4:1/10:1, PE brown, med |
Big O ring for double syringe | Medmix | PPA-X05-04-02SM | Piston A, 5 mL, 4:1 |
Double Syringe | Medmix | SDL X05-04-50M | Double syringe, 5 mL, 4:1 |
Double Syringe Dispenser | Medmix | DL05-0400M | Dispenser, 5 mL, 4:1, med , plain |
Laminim | 3.6 mg/mL- extracted USC lab | ||
20 mL Syringe Luer Lock Tip | BD | 302830 | |
Luer Lock Caps | Fisher | JGTCBLLX | |
HEPES | Sigma -Aldrich | H4034 | |
Gibco Minimum Essential Media 10X (MEM) | Life Technologies | 1143-030 | |
Trypsin | Life Technologies | 27250-018 | |
UV Crosslinker | Spectroline UV | XLE1000 | |
Sodium Cloride (NaCl) | Fisher | S271-10 | To prepare Mosconas |
Potassium chloride (KCl) | Sigma -Aldrich | P5405-250 | To prepare Mosconas |
Sodium Bicarbonate (NaHCO3) | Fisher | BP328-500 | To prepare Mosconas |
Glucose | Sigma -Aldrich | G-8270 | To prepare Mosconas |
Sodium Phosphate didasic (NaH2PO4) | Sigma-Aldrich | S-7907 | To prepare Mosconas |
Sterile Filter for syringes | Corning | 431224 |