Hyaluronic Acid and Derivatives for Tissue Engineering.

¹Fluorotronics, Inc, Departments of Life Sciences, Chemistry and Nanobiotechnology, 2453 Cades Way, Bldg C, San Diego, CA 92081, USA

²Centre Medical des Guittieres, Departments of Aesthetic and Anti-Aging Medicine, Rue des Guittieres, Saint-Philbert de Grand lieu 44310, France

Corresponding Author:

Dr. B Menaa
Fluorotronics, Inc, Departments of Life Sciences
Chemistry and Nanobiotechnology, 2453 Cades Way
Bldg C, San Diego, CA 92081, USA
E-mail: bouzid.menaa@gmail.com, dr.fmenaa@gmail.com

Received date: July 14, 2011; Accepted date: November 14, 2011; Published date: November 16, 2011

Citation: Menaa F, Menaa A, Menaa B (2011) Hyaluronic Acid and Derivatives for Tissue Engineering. J Biotechnol Biomaterial S3:001. doi:10.4172/2155-952X. S3-001

Copyright: © 2011 Menaa F, et al. This is an open-access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.

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Abstract

Among the protein-based hydrogel-forming polymers, various salts of hyaluronic acid (HA), aka hyaluronan or sodium hyaluronate, are used to prepare tissue-engineering. HA is a natural occurring glycosaminoglycan, a polysaccharide of high molecular weight which displays interesting viscoelastic properties. Among other organisms, HA is omnipresent in the human body, occurring in almost all biological fluids and tissues, although the highest amounts of HA are found in the extracellular matrix of soft connective tissues. HA is synthesized in a unique manner by a family of hyaluronan synthases and degraded by hyaluronidases and, exerts pleiotropic biological functions such as tissue repair and tissue regeneration. The excellent biocompatibility and biodegradability of HAderived hydrogels make them ideal materials for tissue engineering. Nevertheless, because of their hydrophilic nature, further modification with adhesion-mediating peptides is required to allow sufficient cell attachment. Hence, several methods of chemical cross-linking using different linkers have been investigated to improve the mechanical properties of those materials for long-term applications in the biomedical field. This manuscript provide an overview of HA and derivatives used as biomaterial scaffold for theranostic medicine.

Keywords

Hyaluronic acid; Hydrogel-forming polymers; Tissue engineering; Scaffolds; Theranostics; Nanobiotechnology

Introduction

Over the past three decades, tissue engineering (TE) and regenerative medicine have emerged in order to find alternative therapies to organ transplants, a life-threatening medical procedure. Indeed, tissue loss and organ failure alternatives represent one of the greatest challenges in human health-care avoiding (i) severe drawbacks due to the huge demand for organs, (ii) scarce number of donors and, (iii) life-term medication (e.g. immunosuppressive drugs).

TE is an interdisciplinary field which applies the principles of engineering and life sciences towards developing biological substitutes which restore, maintain, or improve tissue function [1]. One of the major approaches in TE is to deliver cells and/or bioactive substances (e.g. growth factors) to patients using three-dimensional scaffolds [2] (Figure 1). Cells and growth factors are chosen based on the type of tissue to be restored, and the scaffolds should function as temporary artificial extracellular matrices (ECM) which accommodate the cells and guides their growth in three dimensions to form new tissue [3].

Figure 1: Principles of tissue engineering. A scaffold containing cells and bioactive substances can be used as a biocompatible and biodegradable bioreactor and implant with the purpose of restoring or improving the tissue defects.

Polymers are ideal candidates as scaffold materials for TE since they can be tailored to have desired properties (e.g. mechanical features, geometrical shapes, biocompatibility, minimal toxicity) and, be degraded in the same rate as new tissue is formed [4,5]. They are represented either by synthetic or natural molecules. For instance, synthetic polymers such as poly(-N-isopropylacrylamid) (PNIPAM) [6], poly(vinyl alcohol) (PVA) [7,8] and poly(ethylene glycol) (PEG) [9], have been widely explored because of their relatively simple modification to prepare gels with desired mechanical and physical properties. Natural polymers such as collagen type-I [10], fibrin [11], alginate [12], chitosan [13], chondroitin sulfate [14] and HA [15] have been used to prepare hydrogel scaffolds. Hydrogels of naturally derived polymers have the advantage of biodegradability and resemble to the natural ECM. Nevertheless, some of them have also their limitations. Thereby, collagen hydrogels can be immunogenic [10] while fibrin hydrogels can yield insoluble fibrin peptides aggregates and can be associated with a certain degree of shrinkage when used as matrices for cell encapsulation [11].

HA is a glycosaminoglycan (GAG), a polysaccharide that contains no protein backbone and which is receiving special attention in a wide range of biomedical and TE applications [15]. Indeed, this main component of ECM is naturally involved in tissue repair, and displays unique physical-chemical properties (e.g. viscoelasticity, biodegrability, biocompatibility), making it an ideal material for TE [16-17]. Over the years, HA has been isolated from rooster combs or, through microbial fermentation. Today the production and purification of HA has turned into an industry. Highly pure HA is available in a wide range of molecular weights at relatively low costs. However, due to the short turnover rate and limited mechanical properties of native HA solutions, chemical modifications are required to obtain suitable stable biomaterials (e.g. hydrogels for in vivo tissue repair). Thereby, methods of chemical crosslinking using different linkers have been investigated [18-20].

In this manuscript, we provide an overview of the properties and applications of HA and derivatives for both therapy and diagnosis.

Physiological and Physical-Chemical Properties of Hyaluronic Acid (HA)

Structure and physical-chemical properties

HA was first isolated, in 1934, from the bovine vitreous humor where it was recognized as a muco-polysaccharide of high molecular weight (range of 10²-10⁴ kDa) [21]. The structure of this natural polymer is highly conserved between mammalian species and, is defined as a versatile, linear straight-chain, non-sulfated GAG, composed of 2000-25000 repeating alternative sequence of disaccharide units (β1,3 glucuronic acid (GlcA) and β1,4 N-acetylglucosamine (GlcNAc)) (Figure 2), with an extended length of 2-25 mm [22-24]. Its pseudorandom coil configuration in aqueous solvents occupies a large volume of solvent. It is thus considered as a space-filling molecule, loosening tissues, creating spaces for cell motility, decreasing cell-cell contacts, and impeding intercellular communication [25].

Figure 2: Spatial structure of hyaluronic acid (HA). HA is composed of alternating D-glucuronic acid and D-N-acetylglucosamine moieties, linked together via alternating β-1,4 and β-1,3 glycosidic bonds. The number of repeating disaccharide units (n) can be up to 25000, and each unit has a molecular weight of 401g/mol. The arrows schematize the functional groups that can be used for performing chemical modifications (e.g. addition of a linker).

Interestingly, HA displays viscoelastic properties [23,26], based on a mixture of intrinsic factors related to its structure (polymeric and polyelectrolyte) characteristics [16] such as (i) high molecular weight, (ii) electrostatic repulsions of the carboxylate ions (COO-), (iii) intramolecular hydrogen bonds and, (iv) double helical conformation.

Distribution and biological functions

HA is predominantly present in the ECM of some tissues (e.g. skin, umbilical cord, embryonic and malignant tissues) and body fluids (e.g. synovial fluid, vitreous humor) of all vertebrates as well as in some bacteria [22,27-30]. HA is also highly expressed in the glycocalyx, a pericellular coat of most cells, and is particularly prominent on the apical surface of endothelial cells [31].

Since its discovery, the biological functions of HA have been thoroughly investigated [23,25]. For instance, HA is involved in the (i) healing wound, tissue repair and regeneration [23,32-34], (ii) organization of the ECM [23,35], (iii) lubrication of the joints [23,28], (iv) regulation of the cell adhesion and motility through receptors that interact with the cytoskeleton [23,36,37], (v) angiogenesis by mediating cell proliferation, cell migration and cell differentiation [23,38,39]. Some of those functions (e.g. angiogenesis, tissue homeostasis, tissue remodeling) are exerted by binding to a family of cellular proteoglycan receptors, the hyaladhedrins (e.g. RHAMM aka CD168, CD44) [24,40].

Interestingly, the relevant role of HA in promoting cancer is actively investigated. Indeed, HA-HA receptor interaction is known to generate intracellular signaling, which, in turn, promotes tumor growth, metastasis, angiogenesis, trafficking of tumor-associated macrophages, and chemoresistance [41-47]. In fact, a HA-hyaluronidase (HAHAase) complex system would be involved in tumor angiogenesis. Indeed, HA synthase (Has) expression required HYAL-1, a HAase, to promote tumor growth and progression [48-49]. Concordantly, the use of 4-methylumbelliferone (4-MU), an HA synthesis (Has) inhibitor, displayed antitumor activity in cancer cells [50]. Besides, HYAL-1 is able to degrade HA into proangiogenic fragments that support tumor progression, invasion, and angiogenesis in some cancer models [51-52]. Therefore, HYAL-1 expression is potentially an independent predictor of metastasis [53-56] and, HYAL-1 can be considered as a valuable target for cancer therapy. Thereby, the use of sulfated HA (sHA), generated by O-sulfation of HA, was shown to inhibit HAases [57] and tumor growth [58]. Eventually, a recent safety assessment report showed that HA does not play a causal role in cancer metastasis and, that the widespread clinical use of HA has been shown free of significant adverse reactions [59].

Nevertheless, further mechanistic insights into the tumorassociated HA-HAase system and a preclinical proof-of-concepts of the safety and efficacy of inhibitors against HAases, are still required. Moreover, in our opinion, the risks of developing cancer using HAbased scaffolds in TE shall be rigorously evaluated in a time-dependent manner as HA biodegradation can generate pro-angiogenic fragments.

Metabolism

Circulating HA is mostly derived from lymph. Lymph nodes may nevertheless extract as much as 80-90% from peripheral lymph before it can reach the bloodstream [29]. HA can be taken up by cells [60] through receptors such as CD44 [61-63] and the receptor for HA-mediated motility (RHAMM) [64]. Nevertheless, HA is not immediately degraded by the cells since intact HA chains have been detected in cytoplasm, in nucleus, and even within the nucleolus [65-67]. Furthermore, it has been suggested that stromal cells (aka connective tissue cells such fibroblasts and endothelial cells) primarily synthesize HA, through specific synthases, before supplying it to the epithelial cells [68]. The general pattern of distribution suggested that HA is absorbed from plasma and tissue fluids by elements of the reticuloendothelial (RES) system [69].

Despite the increasing importance of HA in biology, little is still known about the degradation of HA in tissues. The catabolism scheme of endogenous HA did report an uptake of the lymphatic system followed by blood transportation to the liver where it is fully degraded [70]. Uptake and metabolism are thus primarily effected in liver and lymph node by endothelial cells lining the sinusoids of each [29]. A significant plasmatic flux of radio-labeled HA was also taken up in bone marrow and in lymph nodes [29,69]. In lymph nodes and in spleen, macrophage-like cells intertwined with the endothelial cells to take up HA [29].

HA can be then degraded by glycosylphosphatidylinositol (GPI)- anchored HAases, class of enzymes that cleave specifically HA glycosidic bonds [71], by oxidation due to reactive oxygen species (ROS) [72], heat [73], hydrolysis [74], among others [75]. The daily metabolic turnover of HA ended up to approximately one third of the total body content (e.g. 15g of HA for a 70 kg individual) [76,77]. Between different tissues, rates of turnover varied widely. In the bloodstream, the t_1/2 for HA was rapid (i.e. 2-5 min) while in a tissue as relatively inert as cartilage, HA turnover occurs in 1-3 weeks [78]. Interestingly, normal turnover in the bloodstream has been estimated in the range of 0.3- 1.0 μg/min/kg body weight, and turnover in peripheral tissues may be effected by degradation in situ, or by transfer into lymph by diffusion or hydrodynamic forces [29].

Increasing evidence points to the existence of a mini-organelle, a hyaluronasome, a possible multi-protein membrane-associated complex, that has both HA synthetic and catabolic activities and, which possesses sensitive sensor mechanisms that can respond to various metabolic states [79,80]. Thereby, it has been suggested that high molecular HA is tethered to the plasma cell surface by HA receptors, combined possibly with an interaction with Hyal-2, a GPI-linked hyaluronidase anchored to the plasma membrane [80].

Hyaluronic Acid Hydrogel-Forming Polymer

Definition

Hydrogels are cross-linked hydrophilic polymer networks swollen in water (Figure 3), and can be classified as “reversible” or “permanent” depending respectively on the physical (e.g. molecular entanglements, hydrogen bonding, ionic forces or hydrophobic interactions) or chemical (e.g. covalent cross-linking) nature of the cross-linkage [81].

Figure 3: Schematic illustration of hydrogel thick film in a quartz cell.

Hydrogels are used in TE and drug delivery applications due to their biocompatibility, porosity and hydrophilic character [82,83]. In addition, many hydrogels are biodegradable and can be processed to resemble the natural ECM with physical and chemical properties that promotes cell proliferation and cell differentiation [84,85].

Injectable gels containing cells and/or therapeutic agents (e.g. growth factors) are of particular interest as they can be administered through minimally invasive procedures [86,87].

Chemical modifications

HA hydrogels can be formed by covalent cross-linking or derivatization by addition of hydrophobic groups. These possible routes slow degradation rates, increase mechanical stability of HA solutions and introduce new functionalities (e.g. in vivo cross-linking and/or conjugation with therapeutic agents).

Chemical modification of HA is generally achieved by targeting the carboxylic acid group (-COOH) present on the glucuronic acid moieties, or the hydroxyl groups (-OH) found on both sugar rings (Figure 2). A suitable modification technique should preferably be performed under mild conditions (e.g. pH, temperature) and enable low-degree functionalization to maintain properties of native HA (e.g. solubility, stability, immune-neutrality, biological recognition).

Thereby, HA functionalization has been successfully demonstrated through carbodiimide chemistry, while this strategy required a large amount of reagents [88,89]. Indeed, at pH 4.75, HA carboxyl groups reacts with 1-ethyl-3-[3-(dimethylamino)propyl]carbodiimide (EDC) to produce an intermediate, O-acylurea, useful for further introduction of various hydrazides [88,89]. Moreover, similarly to a strategy originally employed in the preparation of HA-esters using alkyl and benzylhalides [90], active N-hydroxysulfo-succinimide (sulfo-NHS)- esters of HA carboxyl groups could be prepared in dimethyl sulfoxide (DMSO) for subsequent amidation [91]. DMSO enabled solubilization of HA by changing the carboxylate counter (-COO-) ion to t-butyl ammonium (TBA) [91].

Gel preparation

HA gels can be prepared by covalent cross-linking of native HA bisepoxides [92], divinylsulfone [93], formaldehyde [94], biscarbodiimides [95] and dihydrazides together with EDC [96], which target HA hydroxyl groups. However, these strategies were not suitable for in vivo gel formation as the reactions could (i) cause HA instability due to the alkaline or acidic conditions used, (ii) use potentially toxic reagents, and (iii) lead to unspecific reactions with the surrounding tissue as the carboxylic acids and hydroxyl groups are present in all biological tissues.

Thus, cross-linking of functionalized HA has been used for suitable preparation of HA hydrogels capable of in vivo gel formation. For instance, the use of homo-bifunctional cross-linkers have been explored using thiolated HA and diacrylated PEG [97,98], as well as using methacrylated HA together with dithiothreitol (DTT) [99]. The cross-linking reactions in these systems took place under physiological conditions and the gels were formed within 30 minutes approximately after mixing HA-derivatives with cross-linkers [100].

In dilute systems, high molecular weight bifunctional cross-linkers were a better option than the low molecular ones which could (i) easily form molecular loops than cross-linkages, due to a favorable likehood and, (ii) be cytotoxic due to their diffusion away from the injection site before reacting [101].

Furthermore, increase of the degree of functionalization (e.g. crosslinking of two polymer derivatives having complementary reactive functionalities) can avoid potential intra-molecular cross-linking, enabling efficient hydrogel formation without causing significant changes of polymer biological properties (Figure 4). Thereby, injectable two-component HA-based hydrogels have been successfully prepared through the cross-linking of aldehyde and hydrazide-modified derivatives of HA [102].

Figure 4: Possible network formation in hydrogel. Deficient network formation is usually observed using bi-functional low molecular weight cross-linkers (top reaction), whereas cross-linking of multifunctional polymers having complementary reactive functionalities enables efficient network formation (bottom reaction).

Some HA-based Scaffolds Applications in Bio-Medicine and Pharmacy

Use of HA-based scaffolds in regenerative medicine

When a tissue is largely damaged, tissue transplantation (e.g. bone) or prosthetic implants usually are considered as major medical solutions [103]. However, those therapeutic options are not without limitations and risks for the patient. Indeed, tissue transplantation may (i) be limited by tissue supply, (ii) cause discomfort to the patients, (iii) increase the risk of disease transmission and, (iv) cause host reactions [104]. Besides, prosthetic implants are not physiologically functional and, are too often accompanied by infection and structural failure [105].

As an alternative therapeutic option to tissue transplantation and prosthetic implantation, TE showed very promising results mainly for acute and relatively small lesions (e.g. cartilage reconstruction) and, it is expected that TE will have tremendous clinical applications if it can be applied to chronic lesions (e.g. large chondral lesions in patients with degenerative osteoarthritis) [106].

TE consists in inducing or accelerating the tissue forming process by in situ delivering of progenitor/stem cells, and/or growth factors using degradable biomaterial scaffolds (e.g. HA based-scaffolds designed according to the tissue defect) [107]. Importantly, the sitedirected injection of a growth factor without a scaffold was helpless [108], because the later was required to locally concentrate the growth factor [109].

Bone represents one of the most frequently transplanted tissues in spite of its capacity to self-regenerate [110]. Nevertheless, bone transplantation is limited and presents the risks previously evoked [104,105]. Then, bone TE often involved injectable polymer-based scaffolds (e.g. HA hydrogels), osteoprogenitor or osteo-stem cells (e.g. mesenchymal stem cells (MSCs)) which were able to get differentiated in bone-building cells (aka osteoblasts) in presence of growth factors (e.g. bone morphogenic proteins (BMPs), a group of proteins belonging to the transforming growth factor-b TGF-b) superfamily) [111-113]. Thereby, HA-based polymers were used as cell carriers for tissueengineered repair of bone and cartilage [114,115]. Interestingly, a new minimally invasive tissue-engineering approach, named Hyalograft®, consisting in the implantation of expanded autologous chondrocytes grown on a three-dimensional hyaluronan-based scaffold, was described as a safe, rapid, easy-handle, and viable therapeutic option for treatment of acute cartilage lesions over currently available autologous chondrocyte implantation techniques [116]. Besides, co-encapsulation of TGF-β3 containing nanofilm-coated alginate microspheres, along with human MSCs in HA hydrogels, has recently shown promising results in animal models towards the development of implantable constructs for cartilage reconstruction (aka chondrogenesis) [117]. Eventually, to establish medical use of TE technology for ligament and tendon injuries, a scaffold with sufficient ability for cell growth, cell differentiation, and mechanical properties, has been developed [118]. This scaffold made from chitosan and 0.1% HA exhibited adequate biodegradability, biocompatibility, joint stabilization, low toxicity and low inflammation in animal experiments [118].

Use of HA-based scaffolds as drug delivery systems

HA hydrogels, among others, are widely used as dermal and transdermal drug delivery systems. These innovative carrier systems were designed for the controlled release of drugs through the skin into the systemic circulation, in order to maintain consistent efficacy and reduce the dose and potential side-effects of the drug(s) [119].

For instance, a local delivery of DNA through a hydrogel scaffold would increase the applicability of gene therapy in tissue regeneration and cancer therapy [120]. Thereby, a novel process, termed caged nanoparticle encapsulation (aka CnE), has been developed for loading concentrated and unaggregated non-viral gene delivery nanoparticles into various HA hydrogels [120].

Furthermore, HA-bioconjugates have been developed to enhance selective entry of cytotoxic drugs into HA receptor-expressing cancerous cells (e.g. CD44 and RHAMM in ovarian cancer cells) [121-122]. Indeed, it was shown that (PEG)-conjugated HA nanoparticles (HA-NPs) were largely taken up by cancer cells over-expressing the HAreceptor CD44 comparatively to normal fibroblast cells, improving the tumor targetability in vivo [122]. Concordantly, a new HA-paclitaxel bioconjugate, Oncofid-P®, was more effective than the use of free paclitaxel for intraperitoneal treatment of ovarian cancer in mice [123].

However, HA and its degradation products, accumulated into the stroma of various human tumors, can modulate intracellular signaling pathways and, positively affect angiogenesis of malignant cells and multidrug resistance [124].

Use of HA-based scaffolds in anti-aging and esthetic medicine

HA reached prominence in cosmetic practice where it represents the injectable dermal filler of choice for most anti-aging, esthetic and plastic specialists [125].

For instance, HA is used for the correction of soft tissue defects (e.g. skin regeneration, wrinkle-treatment, wound healing) [125,126]. Thereby, HA material provided an effective, non invasive, non surgical alternative for correction of the contour defects of the face due to its enormous ability to bind water and easiness of implantation [127]. In the US, eight HA dermal fillers were approved for commercialization by the Food and Drug Administration (FDA) although severe adverse effects have been reported [128].

Conclusion

HA is a naturally occurring polysaccharide which is present in extracellular matrices of soft connective tissues and body fluids. With regards to its mechanism of synthesis, its size and its physical-chemical properties, HA is unique among other glycosaminoglycans. HA is able to interact with other macromolecules (e.g. proteins) and, participates in regulating the cell behavior during numerous morphogenic, restorative, and pathological processes in the body. The role of HA in diseases, such as in various forms of cancers, arthritis and osteoporosis, is leading to new impetus in research and development. The preparation of the safest and efficient HA-based biomaterials for theranostic medicine for any type of lesions, regardless their surface, remains an exciting challenge.

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