Department of Plastic and Reconstructive Surgery, Shanghai Ninth People's Hospital, Shanghai Jiao Tong University School of Medicine, Shanghai 200011, China.
Correspondence Address: Dr. Xu-Song Luo, Department of Plastic and Reconstructive Surgery, Shanghai Ninth People's Hospital, Shanghai Jiao Tong University School of Medicine, No. 639, Zhizaoju Road, Shanghai 200011, China. E-mail: email@example.com
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The design and application of hyaluronic acid (HA)-based scaffolds to control cell response and construct ideal tissue engineering products have been of great interest in the past few decades. This review provides an overview of the biological properties of HA to better understand how to engineer a cell-scaffold composite that is qualified in tissue engineering; important tissue engineering applications of HA including cartilage tissue engineering; and lastly, the problems of the current research on HA. All the data described above were collected and analyzed from PubMed, EMBASE and Medline.
Hyaluronic acid, biomaterials, tissue engineering and regenerative medicine, stem cells
Hyaluronic acid or hyaluronan (HA) was the first isolated from bovine vitreous humor by Meyer and Palmer in 1934. It was named because of its transparent appearance in water and the probable presence of hexuronic acid as one of the components. HA is a linear polysaccharide without branches and is one of the most important components of extracellular matrix. Researches demonstrated that HA plays an important role in regulating cell differentiation, migration, angiogenesis and inflammation responses[2-5]. HA has become a hotspot in the fields of scaffold materials in tissue engineering because of its ubiquitously distribution in vertebrate tissues, good biocompatibility and non-toxic degradation products. The versatility of HA is closely related to its unique properties, andHA with its different states or molecular weights can exhibitdiverse features. Therefore, to understand the application of HA, the basic physical, chemical and biological properties of HA must first be understood.
A review of the literature was performed by searching the keywords “hyaluronic acid” AND “tissue engineering” OR “tissue regeneration” OR “stem cells” in PubMed, EMBASE and Medline. The most important or typical papers discussing cartilage and bone tissue engineering using HA-based scaffolds were viewed and selectively cited. Skin and soft tissue engineering with HA-based scaffold were reviewed as well.
HA is an unbranched non-sulfated glycosaminoglycan composed of repeating disaccharides [β-1,4-D-glucuronic acid (known as uronic acid) and β-1,3-N-acetyl-D-glucosamide] [Figure 1]. Since HA is rich in carboxyl and hydroxyl groups, it can form a hydrogel under mild conditions like chemical modification, crosslinking or photo-crosslinking. The mechanical strength, physical and chemical properties of the materials depend on the degree of the modification and crosslinking[1,7]. The physical properties of HA include its compressive stress, compressive modulus, storage and loss modulus, porosity, swelling rate, degradation rate and density.
HA has a molecular weight between 103 and 104 kDa, which can reach a length of 25 μm when fully extended[9,10]. The high hydrophilicity of HA is the physical basis for its wide presence in the human body. The molecular chains of HA are intertwined in solution and it occurs even when the concentration is very low. This phenomenon can be observed in HA solution as low as 1 mg/mL, which is one of the reasons to the unique rheological characteristics of HA [Figure 2]. In human bodies, especially soft tissues, HA often exists in the form of high molecular weights which is the essential reason for its high viscosity even in diluted solutions. Moreover, the mutual macromolecular crowding in human body contributes to the higher viscosity. With macromereconcentrations from 2 to 20 wt%, networks exhibited volumetric swelling ratios ranging from ~42 to 8, compressive moduli ranging from ~2 to over 100 kPa, and degradation times ranging from less than 1 day up to almost 38 days in the presence of 100 U/mL of hyaluronidase. Although higher molecular weight or crosslinking degree can result in improved compressive modulus that is essential in the tissue engineering of cartilage or bone, the viability of seed cells would be compromised. In most instances, HA exhibited a highly porous morphology so that cells can permeate into the scaffold easily. Under most circumstances, the HA macromere is degraded by hyaluronidase. However, it can also be degraded by reducing substances or at acidic pH values after modification.
The characteristics of HA including its consistency, biocompatibility, hydrophilicity, limited immunogenicity and unique viscoelasticity have made it an excellent moisturizer in cosmetic dermatology and skin-care products as well as a potential biomaterial in tissue engineering. However, HA without modification tends to be absorbed rapidly in human body, which makes it unqualified in tissue engineering. To overcome this defect, chemical modification is indispensable. Many biomaterials do not have a lot of chemically modified sites, while HA can be chemically modified with its hydroxyl, carboxyl and N-acetylaminoends. The chemical modification of HA can be roughly divided into two types: esterification and crosslinking. The purpose of esterification is to link HA with certain hydrophobic groups, reducing the poly anion properties of HA. Under certain conditions, the carboxyl group of HA can undergo esterification reaction to produce HYAFF, an esterified derivative of HA. In this reaction, many different alcohols, such as fatty alcohols and aryl fatty alcohols can be bound to HA moleculesin order to improve the chemical properties of HA and its stability as a tissue engineering scaffold, as well as to extend its maintenance in the human body. The purpose of HA cross-linking is to convert it from solid state to hydrogel state under mild conditions and to prolong its maintaining time in the human body. Besides, the mechanical strength of crosslinked HA can be remarkably improved compared to the non-crosslinked one, which makes it more suitable for tissue engineering applications.
The cross-linking reaction of HA can be divided into complete or incomplete one. The complete cross-linking reaction causes the HA molecules to be covalently attached to the continuous polymer network so that HA is no longer soluble in the water. While the incomplete reaction prompts part of the covalent binding reactions of HA molecules, resulting in partial solubility after the reaction. 1-ethyl-3-(3-dimethylaminopropyl) carbodiimide, divinyl sulfone, glutaraldehyde, butanediol-diglycidyl ether are the most common crosslinking agents [Figure 3].
HA is synthesized by HA synthesis (HAS) on the cell membrane. And it is the only glycosaminoglycan that is not synthesized in the Golgisome. There are three different HAS in mammals, HAS1, HAS2 and HAS3. The three enzymes are located on different chromosomes, producing HA with different molecular weights. The expression of HAS isoenzymes varies under different status of morphogenesis and pathology. For example, HA in infants is of abundant quantity, however, in the process of growing up it is gradually replaced by collagen fibers and proteolycins which accounts for the fact that mature tissue can withstand greater mechanical force.
It is almost certain that most kinds of vertebrate cells synthesize HA at some point in their natural history. When ﬁbroblasts, mesothelial or certain other kinds of cell are plated out in tissue culture, they surround themselves in a few hours with a transparent gel-like HA which can protect themselves against damage by immune cells, impedes virus infection and may be important in mitosis.
At present, different origins derived stem cells are the most universally used seed cells in tissue engineering. HA can interact with many stem cell surface receptors, inducing intracellular signal transduction through the connection with these receptors and activating corresponding proteins in a direct or indirect pattern.
Through signal transduction receptors, HA can affect the most essential cell activities including proliferation, survival, movement and differentiation. One of the most important receptors is CD44, which provides an agent for maintaining and anchoring the proteoglycan polymer to the cytoplasmic membrane. CD44 plays an important role in tissue formation by mediating the remodeling of extracellular matrix, intercellular interactions, and cell-matrix interactions. In addition, the close connection with the cytoskeleton allows CD44 to induce intracellular signal transduction, thereby experiencing changes in the extracellular matrix environment and triggering cellular responses. Besides, CD44 receptors are of widespread concern because they are essential to maintain cartilage phenotype and HA catabolism. HA-containing materials can also interact with proteins or cells through the receptor for hyaluron-mediated motility or intercellular adhesion molecule-1.
There are also some reports that HA-based scaffolds can directly induce or promote stem cell differentiation. In vitro experiments conducted by Meng et al. demonstrated that HA-based scaffold can induce stem cells into cartilage in basal medium without the addition of growth factors. The increased expression of an important HA receptor like CD44, also suggested the interaction of cells with HA. In addition, Choi et al. reported that HA oligomers in the skin substitute models could promote the survival of basal stem cells. Their experiments demonstrated that a recognized skin stem cell marker p63 expression was elevated in the skin substitute model added HA oligomer (400-2000 Da), therefore, HA may also help to maintain stemness. Huang et al. also reported that mesenchymal stem cells grown on chitosan-HA membranes performed better in maintaining stemness markers (Oct4, Sox2 and Nanog) than cells cultured on common dishes.On the contrary, if CD44 was blocked by the antibody, then the cells would lose their ability to maintain the spherical form while the stemness gene expression would also decline. It indicated that HA may assist in maintaining stemness through CD44.
Tissue transplantation is one of the most frequent and most important treatments in plastic and reconstructive surgery. However, autologous transplantation is often limited by the insufficiency and trauma of donor site, while allogeneic transplantation is faced with immune rejection, donor scarcity, transplant infection and other risks. The emergence of tissue engineering is a promising technique to overcome these problems above.
Tissues or even organs can be regenerated by the coordination of seed cells, scaffold and growth factors. The histocompatibility, chemical modification and biodegradability of HA make it an ideal scaffold for tissue engineering. The properties of hydrogel can mimic the water content of human tissue and contribute to the exchange of oxygen, nutrition and metabolic waste[27,28]. In addition, the fluid morphology makes it possible to inject the scaffold through a tiny needle hole, which can greatly reduce the trauma and infection rate of the operation. Therefore, it has been one of the hotspots in tissue engineering materials and used in a variety of fields. The ideal tissue engineering scaffold should have good cell adhesion to support the growth of seed cells, however, HA tends to have weak cell adhesion. Therefore, modifications like heparin decorated, Arg-Gly-Asp (RGD) sequence linking are indispensable[29-31].
In tissue engineering construction, a scaffold has to maintain its structure for several months or longer before extracellular matrix is deposited. Since the diffusion of nutrients and essential gases to cells is typically limited to a depth of 150-250 μm from a capillary (3-10 cells thick), tissue constructs must permit in-growth of a blood capillary network to nourish and sustain the viability of cells within. HA can be chemically modified to promote angiogenesis without changing its original biocompatibility or weak immunogenicity. HA can be degraded into oligomers (HA oligomers, HAO) (4-25 dose units) by hyaluronidase in vivo. These HAOs have a high biological activity and are capable of affecting cell behavior including angiogenesis through monovalent bond to the host cells[3,34]. Silva et al. demonstrated that gellan gum-HA hydrogel can be degraded by hyaluronidase and release various amounts and sizes of HA oligomers that are capable of promoting the proliferation of human umbilical vein endothelial cells. Besides, in the mice hind limb ischemia model, HA-cell composite can significantly promote angiogenesis. A series of in vitro and in vivo experiments have shown that long-chain (native high molecular weight) HA at physiological concentrations has the ability to resist inflammation and inhibit angiogenesis. Long-chain HA can bind to CD44, and inhibit cell proliferation, cell cycle in the key signal transduction, thereby inhibiting angiogenesis. While HAO will compete with long-chain HA for binding to CD44 and prompt mitosis and angiogenesis. The CD44-HA oligosaccharide interactions that primarily cause these pro-mitotic effects have also been shown to stimulate matrix metalloproteinase-2 and -9 production and thereby increase cell invasion through extracellular matrix barriers to facilitate vessel sprouting and outgrowth. Since the pro-angiogenic HA oligomers cannot by themselves be crosslinked to yield solid biomaterials, and can also potentially incite inflammatory/activated cell responses, they must be presented on other scaffolding biomaterials, either synthetic or natural[37,38]. Another method is to mix with the more bioinert long-chain HA in such a manner as to fulfill the physical and mechanical requirements of the biomaterial, elicit the desired biologic responses, and yet deter excessive and long-term inflammation.
In the application of HA-based materials, cartilage tissue engineering is the most extensive due to the fact that HA is quite a suitable scaffold for the growth of chondrocyte. The extracellular matrix of chondrocytes is rich in glucosamine and HA while the latter one plays an important role in regulating the function of chondrocyte. Moreover, since HA can also be used as a scaffold in bone regeneration, it is a suitable material for osteochondral tissue engineering[41,42]. HA, as a scaffold, has several possible mechanisms to promote cartilage formation. First, HA can induce stem cells, cartilage progenitor cells to differentiate into chondrocytes. Some papers indicate that HA involves in the maintenance of chondrocyte phenotype, which is utmost important for the reason that chondrocyte can lose its phenotype during in vitro culture. Furthermore, HA is favorable to the deposition of extracellular matrix which is essential in cartilage tissue engineering[44-48]. Besides, HA-containing hydrogel material has a lower oxygen concentration, while the hypoxic environment is conducive to the growth of chondrocytes. Another possible mechanism is that HA interacts with cells through the cell surface of the CD44 receptor, regulating cell migration, proliferation, differentiation, and other close contact with the cytoskeleton to CD44-activated cells within the signal transduction. HA binds to proteoglycans by the aid of core proteins. These proteoglycan monomers can connect with CD44 receptors on chondrocytes, while the released ones in the extracellular matrix can enhance matrix permeability, therefore improve the stress resistances. Lammi et al. reported that HA deposition would occur in the areas of cartilage injury and it would attract exogenous mesenchymal stem cells to the injured area. HA can also act as a cell carrier, wrapping stem cells and chondrocytes in the injected area so that the cells can proliferate and differentiate in situ[45,51]. Chung and Burdick demonstrated in both in vivo and in vitro experiments that methacrylated HA is capable of providing a microenvironment that facilitates differentiation of mesenchymal stem cells into cartilage, and the effect can be enhanced in the presence of certain cytokines such as transforming growth factor-β3.
Methacrylated HA is gaining increasingly attention because it can gelatinize through an easy photo-crosslinking, moreover, seed cells can be encapsulated into HA in this way which enables the cell to live in a 3D environment[52,53]. Conventional cartilage tissue engineering materials requirea much larger incision than injectable ones, and photo-crosslinking HA can transform from liquid to hydrogel through ultraviolet irradiation after injected into the ideal site and fill the defect space with various shapes. Chung and Burdick used methacrylated HA with human multipotent stromal cells (MSCs) to regenerate cartilage, and they demonstrated that both in vitro and in vivo cultures of MSC-laden HA hydrogels permitted chondrogenesis, measured by the early gene expression and production of cartilage specific matrix proteins. This kind of in situ cross-linking ways including photo-crosslinking and thermosensitive crosslinking will be a possible future trend.
Besides served as a scaffold, HA can also be used a biologically active molecule to modify bio-inert artificial materials such as polyethylene glycol (PEG), small intestinal submucosa, etc.. The HA-based cell-scaffold composite can provide a framework for the regenerated matrix. Skaalure et al. demonstrated that biodegradable PEG hydrogel modified by high concentration of HA can evidently improve the deposition of extracellular matrix and proliferation of chondrocytes.
HA is most generally used in the cross-linked, modifiedform or as composite with other materials such as platelet-rich plasma, fibrin, chitosan, tricalcium phosphate, collagen, alginate, etc. This is because the cross-linked HA has better mechanical properties than the linear one, while the composite material can combine the advantages of different materials, corresponding with the requirements of tissue engineering scaffold materials. Chen et al. demonstrated that HA and platelet-rich plasma can restore the down-regulation of cartilage gene expression induced by interleukin-1β and tumor necrosis factor-α, including SOX-9, collagen type II and aggrecan.
HA also has a wide range of research and application in bone tissue engineering, it can be used as a scaffold or molecular carrier to promote bone tissue regeneration[40,59]. The existing papers show that its application has been explored in the field of skull, alveolar and so on. As in cartilage tissue engineering, HA is also usually required for modification in bone tissue engineering. Since the mechanical properties of HA are weaker than that of human natural bones, the use of HA alone as a scaffold material is not sufficient to support the cell-scaffold composite and requires other materials to be compounded. For example, Subramaniam et al. demonstrated that HA can be compounded with hydroxyapatite (one of the components of the bone matrix) and modified with calcium sulfate, which encapsulates collagenase. The composite above can serve as a substitute for alveolar bone to produce satisfactory outcomes.
HA can regulate cell differentiation and bone formation by binding to CD44, CD168 on seed cells, such as mesenchymal cells. Zhu et al. demonstrated that N-cadherin modified HA can promote the differentiation of human mesenchymal cells into bone, leading to more bone matrix deposition. N-cadherin is an important factor in mediating cell-cell interactions during the cluster of mesenchymal cells in bone formation. In the experiment, they also modified HA with RGD peptide because only the calcium cadherin was sufficient to provide sufficient cell adhesion.
As a molecular carrier, HA has a wide range of applications on the in vivo experiments. Of all the researches, carrying bone morphogenetic protein 2 (BMP-2) to promote bone formation, fracture healing is the most commonly used method. BMP-2 is a potent bone-forming molecule that has been approved by the Food and Drug Administration for intervertebral fusion, open tibial fractures, and alveolar bone expansion. Bhakta et al. confirmed that the thiolated-HA exhibited a low burst followed by a sustained release of BMP-2 while collagen sponge rapidly released BMP-2 with a high burst phase that was followed by a low sustained phase. Analysis of bone formation by micro-computed tomography revealed that low burst followed by sustained release of BMP-2 from a HA hydrogel induced up to 456% more bone compared to a BMP-2 dose-matched collagen sponge that has a high burst and sustained release. Bhakta et al. also reported that heparin-modified HA also had a similar controlled release effect.
Tissue engineering skin equivalents (substitutes) is one of the most successful and most widely used products in tissue engineering so far. It is usually manufactured by seeding keratinocytes and fibroblasts into non-human (e.g. type I bovine collagen) matrix. However, this tissue engineering skin can only last for approximate 8 weeks due to its high shrinkage of the extracellular matrix, which is not sufficient to form a normal human extracellular matrix consisting of fat, fibrin, glycosaminoglycans and polysaccharides. Stark et al. seeded keratinocytes on esterified HA fibers, producing the dermal equivalents that could last for a longer period and was more similar to normal skin tissue.
In addition to tissue engineering of skin substitute, HA has also been used to increase the retention rate of fat grafts. Alghoul et al. used HA as a cell carrier, mixing with autologous fat of the same volume and transplanted into the back of a nude mouse. They found that HA can improve the survival rate of early fat transplantation and prolong the fat maintenance time.
Tissue engineering is one of the most promising methods in wound healing, while HA is one of the most suitable natural materials in hydrogel scaffolds. HA has similar water content as human tissue, has good tissue compatibility, and it plays an important role in promoting the proliferation and differentiation of seed cells. In addition, high molecular weight HA has a certain anti-inflammatory effect, and low molecular weight HA oligomers have been shown to promote angiogenesis. At present, HA as a scaffold material, connecting molecules, carrier of drugs and other small molecules has been widely used in tissue engineering. Since the microenvironment formed by HA is particularly suitable for the growth of chondrocytes, the application of HA in cartilage tissue engineering is the most popular. Researchers have also devoted themselves to the regeneration of bone tissues, myocardial tissues, skin and soft tissues with the utilization of HA. Natural HA has a short reservation time in vivo due to the rapid degradation by hyaluronidase, therefore appropriate cross-linking and modification of the active group is essential. HA after cross-linking and modification has been widely used alone or compounded with other materials in the tissue engineering. Since HA itself doesn’t have a satisfying cell adhesion, modification with RGD sequence or heparincan be considered as anecessary improvement.
The current problem is that there are a variety of cross-linking and modification methods of HA. Moreover, the raw materials from different origins owning divergent molecular weight (ranging from hundreds to millions), thus exhibiting different biological properties, which brings about quite a lot of difficulties to the research and application of HA. Since the high cross-linking (high molecular weight) and low cross-linking (low molecular weight) HA make such a great difference in the biological properties that how to combine the anti-enzymatic ability of high molecular weight HA with the high biological activity of low molecular weight HA remains to be explored.
Data collection and analysis: Z. Zhu, Y.M. Wang
Manuscript preparation: Z. Zhu, X.S. Luo
Manuscript’s review: J. Yang
Concept design, manuscript preparation and data interpretation: X.S. LuoFinancial support and sponsorship
None.Conflicts of interest
There are no conflicts of interest.Patient consent
Not applicable.Ethics approval
© The Author(s) 2017.
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Zhu Z, Wang YM, Yang J, Luo XS. Hyaluronic acid: a versatile biomaterial in tissue engineering. Plast Aesthet Res 2017;4:219-227. http://dx.doi.org/10.20517/2347-9264.2017.71
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