Decellularized Hydrogels in Bone Tissue Engineering: A Topical Review

Abstract

Nowadays, autograft and allograft techniques represent the main solution to improve bone repair. Unfortunately, autograft technique is expensive, invasive and subject to infections and hematoma, frequently affecting both donor sites and surgical sites. A recent advance in tissue engineering is the fabrication of cell-laden hydrogels with custom-made geometry, depending on the clinical case. The use of ECM (Extra-Cellular Matrix)-derived Hydrogels from bone tissue is the new opportunity to obtain good results in bone regeneration.

Several micro-engineering techniques and approaches are available to fabricate different cell gradients and zonal structures in hydrogels design, in combination with the advancement in biomaterials selection. In this review, we analyse the stereolithografy, the Bio-patterning, the 3D bioprinting and 3D assembly, the Laser-Induced Forward Transfer Bioprinting (LIFT), the Micro-extrusion bioprinting, the promising Electrospinning technology, the Microfluidics and the Micromolding. Several mechanical properties are taken into account for bone regeneration scaffolds. However, each typology of scaffold presents some advantages and some concerns. The research on biomaterials is the most promising for bone tissue engineering: the new biomimetic materials will allow us to obtain optimal results in the next clinical application of basic research.

Introduction

Nowadays, autograft and allograft techniques represent the main solutions to facilitate bone repair. Unfortunately, autograft is expensive, invasive, and subject to infections and hematoma, frequently affecting both donor sites and surgical sites ^1-4. Besides, there are several issues related to allografts, such as the possibility to cause an immune reaction followed by a rejection; moreover, the patient can be infected if the graft is contaminated ^5-8.

In the last decade, tissue engineering has focused on the development of a scaffold that emulates ECM composition and physic-biochemical properties ^9-11.

The main challenges in the implementation of scaffolds in the human body are: (i) preserving the strength and stability of the interface during the degradation period and the replacement phase by the natural host tissue, (ii) matching the resorption rates to the repair rates of body tissues developed both for hard tissue implants and tissue engineering scaffolds, (iii) being highly porous to allow for nutrients, oxygen and waste transport, as well as neovascularization/angiogenesis and bone ingrowth ^12-14.

Starting from the 1990s with the introduction of the hydrogels concept, great interest was focused on the discovery of new biomaterials and novel techniques to produce hydrogels for hard and soft tissue regenerative applications ¹⁵. Hydrogel in material science is defined as a polymer or peptide-based gel with a major component represented by water and with a hydrophilic behaviour. The presence of microscopic pores interconnected in the hydrogel allow to adsorb a higher amount of water in comparison with other types of material, thus guaranteeing the migration of cells, nutrients and oxygen to the construct ¹⁶. In addition, the easy modulation of their physic-chemical and mechanical properties other than cell entrapment and drug delivery potentially makes this substrate ideal for tissue engineering applications. The structural characteristics such as the biodegradability, the water content, the interconnectivity and the biocompatibility make this material the most suitable one for reproducing the ECM platform ^17,18.

Polymers used to synthesize hydrogel networks can be divided into natural and synthetic polymers. The natural polymers' group includes polysaccharides such as chitosan, alginate, hyaluronic acid, agarose, chondroitin sulphate and gelling gum and proteins such as collagen, fibronectin, fibrin and silk.

The hybrid hydrogels are an attempt to combine the good biocompatibility and biochemical properties of natural polymers with the better mechanical performances of synthetic polymers ^3,19,20.

A recent advance in tissue engineering is the fabrication of cell-laden hydrogels with custom-made geometry that is adaptable to the clinical case thanks to the progress made in manufacturing technology ^21-25. (Figure 1)

Figure 1.

Graphical abstract of bone tissue engineering with stem cells combined with hydrogel form biomaterial.

However, a fully functional, mechanically competent, tissue-engineered bone graft showing clinical success in humans has not been developed yet.

Bone Extra-Cellular Matrix: techniques and mechanical properties

Different microengineering techniques and approaches are available to fabricate different cell gradients and zonal structures in hydrogels design in combination, with the latest advancements in biomaterials selection.

Stereolithografy is based on a laser source and a three-dimensional-controlled stage. The materials generally used to obtain solid freeform structure are photopolymerizable and non-polymerizable polymers. Two different layering approaches can be adopted: the bottom-up and the top-down approaches. The incorporation of cells in the manufacturing process is difficult and these are usually seeded after construct fabrication ^26,27.

Bio-patterning is based on micromirrors digital technology generating a reflective photomask, which is the guide to synthesize and polymerize the 3D structure of the scaffold at the same time.

A spatial resolution less of 10 micron allows the encapsulation of cells in the constructs and can be obtained by combining photopatterning and electro-patterning in the design of a microscale hydrogel ^28-30.

3D bioprinting applies a layering deposition mechanism of bio-inks and cells. The instrument is composed of a bio-ink reservoir and a 3D controllable platform. Such printers, which are defined as inkjet, can print through thermal or acoustic approaches, thus setting the amount of bio-ink to be deposited in a certain area and layering the defined prototype. The crosslinking of hydrogel materials can occur through the incorporation, for example, of tyrosinase or through sonication. Cell viability and proliferation have shown to be high when this manufacturing process is used. The drawbacks are the lower thickness obtained as compared with other technologies, the lower resolution at micro and nano-scale length scale as well as the decrease in the mechanical strength and in the ability to withstand degradation and load-bearing defects ^31-33.

Laser-Induced Forward Transfer Bioprinting (LIFT) is based on laser pulses that generate high-pressure bubbles leading the bio-ink through a ribbon into the collector. Several factors affect the final product, such as the viscosity, wettability and free energy surface of the material, the distance between the ribbon and the bio-ink as well as the laser energy. With such technology, the number of ribbons used is related to the number of materials used as bio-inks ^34-36.

Micro-extrusion bioprinting is one of the cheapest technologies mentioned in this review. The bio-ink is extruded in a micrometric length scale along the three axes. Two approaches are used depending on the material viscosity, such as the mechanical extrusion for lower viscosities and the pneumatic one for higher viscosities. The resolution performance is better in the mechanical system than in the pneumatic one. In this manufacturing process, the temperature can be regulated, thus limiting side effects in case of cells loading; however, the force generated to extrude the material can lower the cell viability ^37-39.

Electrospinning technology allows the creation of fibers that can adopt a porous or core-shell morphology depending on the type of material being spun as well as the evaporation rates and miscibility of the solvents involved. This technology allows for a higher mechanical performance of the matrix; however, the three-dimensional structure is hard to manage especially compared with the precision of modern 3D-printing technology, therefore it is difficult use of this manufacturing process at an industrial level ^40,41.

Microfluidics is used to produce small and 2D geometries at a centimetre length scale, but it is difficult to use in complex 3D shaping. A passive pump generates a flow induced intake while the evaporation of the prepolymer is induced before the photo-crosslinking step, thus producing layered hydrogels with different cell gradient concentrations ^42,43.

Micro-molding technique utilizes 3D medical-imaging of bone plateau, two-part reverse mold design and fabrication and hydrogel molding. If materials with higher resolution and free energy surface are used, such as fluoro-based materials, the nano-carrier can be incorporated in the scaffold for drug delivery applications. In micro-molding it is difficult to tailor synthetic construction and cell implementation at different gradients ⁴⁴.

3D assembly allows to aggregate small single units and to interlock cells, thus obtaining an increase in flexural modulus and withstanding large deformation under compressive strain as well as the enhancement in cell viability and differentiation ⁴⁵.

In the scaffold designed for bone tissue regeneration, the mechanical coherence of the structure implanted is an important parameter to determine the final success. Indeed, a fundamental role is played by hydrogel as extracellular matrix simulation. It was demonstrated how stem cells behaviour is dictated by the mechanical performances of the ECM. The most important factors are the elastic modulus of the material and the stiffness. Indeed, it was shown how stem cells possess an enhanced proliferation and multipotency maintenance when cultured on hydrogel with an elastic modulus, similar to bone marrow ^46-48.

Bone defects can be identified in load-bearing and no-loaded defects. In this context, the porosity of the material can play an important role, especially if we consider the size of pores. Interconnectivity is also fundamental for cell migration and proliferation as well as the engraftment of the implant through neovascularization mechanism and nutrients perfusion; such characteristic can lower the mechanical performances ³.

Mechanical characterization of hydrogel in tissue engineering

Several mechanical properties are taken into account for bone regeneration scaffolds. Tensile, compression and flexural properties are first considered, as well as swelling/deswelling behaviour and indentation. Other important factors to be analysed are the pore size, the interconnectivity defined as pore morphology and the degree of connections between pores.

Most of the techniques available are invasive and destructive for cell-laden scaffolds in in-vitro simulated conditions. For this reason, other techniques, such as long focal microscopy and optical-coherence tomography- based spherical indentation, have been evaluated ¹⁵.

In the field of Materials Sciences, the instrument that is used the most to test materials is called Universal Instron machine. By adapting the machine tools ^49-51 it is possible to carry out different mechanical tests; more in details, the apparatus can perform both compression and tensile tests by changing the hardware interface ^52,53. In the compression test, the material is put between two plates. Afterwards, the pressure applied in connection with the distance allows, by means of a numerical model, to analyse the mechanical properties. Anyway, through tensile and compression tests, load-displacement data are obtained, which are then converted into stress-strain data by a geometrical relationship. Flexural modulus and failure strength are also calculated. A variation of parameters can be adopted when hydrogel materials are tested; more in details, a time-depending variation of fixed loading conditions can be useful ^54,55.

Among the mechanical characteristics considered in tissue engineering applications, elastic modulus is given by the relation between tensile stress and strain while flexural modulus is given by the relation between bending stress and strain during deformation of the material. Furthermore, tensile strength is the maximum stress immediately before the failure value and the maximum strain is represented by the ductility of the material ^56-60.

The tangent modulus is graphically represented during the compression test by the slope of the stress-strain curve at each strain point; this value provides information about the stiffness of the scaffold.

The Weibull modulus, also known as the shape factor, is correlated to the strength variability of the material selected. The fracture energy is directly proportional to the relation between the stress and the Young's modulus ^58-61.

Another useful mechanical characterization of hydrogels can be obtained by means of the Bulge test. This test is performed by inflating the hydrogel through a window and by recording it through a CCD camera, thus analysing the displacement as a function of the pressure. Afterwards, a finite element method allows to deduce, based on the data acquired, the mechanical properties ^62,63.

The extensometer method foresees the block of the sample between two clamps and the application of a tensile force, thus the elongation at a certain force is plotted and stress-strain data are acquired. These last methods are used to calculate the viscoelastic properties, the flexural modulus, as well as the tensile and yield strength of the material taken into account ^64,65.

The indentation test in another important test in hydrogel characterization. In this case, the hydrogel is put under compression in a specific localized small area, thus a force-displacement curve is reported with the resulting elastic modulus of the material. In addition, by applying the indenter at a constant depth on the hydrogel surface for a fixed period of time, it is possible to acquire stress relaxation data. Other recent indentation techniques for hydrogels are nanoindentation or atomic force microscopes (AFMs) ^66,67. Novel non-destructive techniques are being used, such as the long-focal-microscopy-based spherical microindentation system, which allows for a central indentation by using a sphere with a specific weight and therefore it allows to analyse the displacement in the central deformation area as well as the mechanical and viscoelastic properties of the material ^68,69. In addition to this last method, optical-coherence-tomography-based spherical microindentation evaluates the mechanical properties of hydrogel materials through the Hertz contact theory applied on the depth indentation area of a sphere into the material. The micrometer resolution of this three-dimensional imaging technique is based on the interferometric backscattering of a light beam in the material. This technique can also determine the geometry and thickness of the hydrogel analysed ^70,71.

In literature, different natural and synthetic materials and different technologies have been reported for the preparation of hydrogels, which can be applied as functional biomaterials but also as carriers of cells by microencapsulation. However, the frequent lack of adequate characterization of the hydrogels and of their components, as well as the incomplete description of the technology, lead to the conclusion that many results of in vitro and in vivo studies are not reliable as they cannot be reproduced ⁷².

Therefore, researchers should first characterize properly hydrogel-based materials in order to improve their reliability and usefulness in transplantation.

Conclusions and future insights

Biomaterials are the most important field of research, particularly in bone tissue applications. The use of safe biomaterials is important to ensure a good control of tissue reply after scaffold transplantation, thus avoiding inflammatory and oxidative reactions, which might cause local and systemic pathological conditions ^73-76. Nowadays, tissue engineering and regenerative medicine are very much based on mesenchymal stem cells: the sources easily obtainable are the most preferred by surgeons. Indeed, in the last years the main concern related to the use of mesenchymal stem cells (MSCs) has been the complicated method used to obtain them from the source, which is based on invasive procedures ^77-79. A good approach to effective bone tissue engineering is to combine MSCs and the proper biomaterials in a cell-based construct to induce bone tissue formation ^80-85.

Of course, many surgeons already use in dental and maxillofacial applications platelets-rich matrices, such as PRF and PRP: they are pretty useful and allow to obtain a good bone growth with excellent vascularization, thanks to neo-angiogenetic properties of such blood derived materials ^86-88.

The main advantages in using the new hydrogel-based biomaterials are that they are easy to use, especially in complex surgeries and to replace also extensive bone losses ⁸⁸.

Future insights could be related to the use of hydrogels in medicine: their considerable ability to be shape-friendly makes hydrogels ideal for guided bone regeneration of complex defects. Hydrogels are also future scaffolds for localized therapies, in order to treat and regenerate at the same time. It is important to underline that also 3D-printing machines are increasingly improving their ability to print different hydrogels to ensure printed tissues to be transplanted in degenerated organs or damaged tissues. In the future we could use both hydrogels and new materials, such as magnesium alloys, to ensure the mechanical and biological skills that will be crucial to achieve a complex regeneration of both hard and soft tissues.