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Yu, W.;  Jiang, Y.;  Lin, F.;  Liu, J.;  Zhou, J. Biofunctionalization of the Tissue Engineered Heart Valves. Encyclopedia. Available online: (accessed on 24 April 2024).
Yu W,  Jiang Y,  Lin F,  Liu J,  Zhou J. Biofunctionalization of the Tissue Engineered Heart Valves. Encyclopedia. Available at: Accessed April 24, 2024.
Yu, Wenpeng, Ying Jiang, Feng Lin, Jichun Liu, Jianliang Zhou. "Biofunctionalization of the Tissue Engineered Heart Valves" Encyclopedia, (accessed April 24, 2024).
Yu, W.,  Jiang, Y.,  Lin, F.,  Liu, J., & Zhou, J. (2022, September 27). Biofunctionalization of the Tissue Engineered Heart Valves. In Encyclopedia.
Yu, Wenpeng, et al. "Biofunctionalization of the Tissue Engineered Heart Valves." Encyclopedia. Web. 27 September, 2022.
Biofunctionalization of the Tissue Engineered Heart Valves

Valve replacement is the mainstay of treatment for end-stage valvular heart disease, but varying degrees of defects exist in clinically applied valve implants. A mechanical heart valve requires long-term anti-coagulation, but the formation of blood clots is still inevitable. A biological heart valve eventually decays following calcification due to glutaraldehyde cross-linking toxicity and a lack of regenerative capacity. The goal of tissue-engineered heart valves is to replace normal heart valves and overcome the shortcomings of heart valve replacement commonly used in clinical practice. Surface biofunctionalization has been widely used in various fields of research to achieve functionalization and optimize mechanical properties.

surface biofunctionalization tissue engineering valve implants

1. Introduction

Valvular replacement is the most important treatment for patients with end-stage valvular disease [1]. More than 200,000 heart valve replacement surgeries are performed worldwide every year, and the number is expected to increase to 850,000 per year by 2050 [2]. During surgery, a natural valve that has lost its function is replaced with an artificial valve, either a mechanical heart valve (MHV) or a biological heart valve (BHV). MHV is generally made of pyrolyzed carbon, various polymers, and metal alloys, whereas BHV is generally composed of three types: (1) Chemically stable animal-derived tissue, (2) valve transplantation from cadaveric or living donors in the heart, or (3) patients’ own valve transplantation from one location to another. Both MHV and BHV have their advantages and disadvantages [3][4][5]. Patients using mechanical valves require lifelong anticoagulation, which can lead to severe thromboembolism or bleeding complications. While the biorepairing of heart valves has achieved clinical success in the short to medium term, calcification leads to their eventual decay [6][7][8][9]. In addition, none of the heart valve replacements currently in use have shown the ability to grow or regenerate, which puts pediatric patients at risk of multiple surgeries. Therefore, creating a valve substitute with the ability to grow, repair, and regenerate using engineered tissue seems to be the best way to overcome many limitations at present.
The concept of tissue-engineered heart valves (TEHV) is described as the development of a heart valve with mechanical function and bioactivity under physiological conditions that facilitate the repair and reshaping of the scaffold [10]. TEHV generally addresses defects in implants by causing biomaterials to interact with autologous cells to achieve growth and biointegration. An ideal heart valve prosthesis should be biocompatible and durable with antithrombotic and anticalcification effects and a physiologically hemodynamic profile [11].

2. Biofunctionalization of the Tissue Engineered Heart Valves

2.1. Non-Glutaraldehyde Cross-Linking

Glutaraldehyde (GLUT) is an aliphatic dialdehyde that can be attached to an amine functional group on collagen by the Schiff alkali reaction [12]; it has been shown to be reversible with easy hydrolysis [12][13]. GLUT or the presence of some groups such as aldehyde groups are highly cytotoxic and do not facilitate cell adhesion and growth on the valve, further leading to valve calcification [14][15]. In addition, GLUT can cause a strong immune response in the body, which leads to valve degeneration through the activation of macrophages, phagocytes, and T lymphocytes, and the aggregation of platelets [16][17][18]. Due to the defects in GLUT cross-linking, the implanted BHV is susceptible to structural damage and loss of function, resulting in a reduction in its durability and the need for reoperation in approximately only 15 years [19][20].
An ideal biomaterial cross-linker should be cytotoxic and less expensive. It can improve the mechanical properties of the material and inhibit calcification. Many fixed ECM-derived scaffolds of cross-linking agents are available, which can be divided into (1) chemical cross-linking agents and (2) natural cross-linking agents. Chemical cross-linkers include carbodiimide [1-ethyl-3-(3-dimethylaminopropyl)-carbondiimide (EDC)], epoxy compounds, six methylene diisocyanates, glycerin, and alginate [21][22][23][24]. Natural cross-linkers mainly include genipin, nordihydroguaiaretic acid, tannic acid, and proanthocyanidins [25]. Besides the aforementioned cross-linking agents, researchers have developed many uncommon cross-linking agents, and their effect is also worth looking forward to. Guo et al. [26][27] and Xu et al. [28] explored the comprehensive properties of the prepared BHV by radical polymerization and cross-linking, respectively. The results showed that the free radical polymerization cross-linking treatment had similar ECM stability and biaxial mechanical properties to the GLUT treatment. Furthermore, the samples showed better cytocompatibility, endothelialization potential, and anti-calcification potential and lower immune response in vivo after the free radical polymerization cross-linking treatment (Figure 1). Curcumin, quercetin, and other polyphenols have calcification inhibition potential similar to that of proanthocyanidins in cross-linked collagen and elastin scaffolds [29][30]. Curcumin [31] and quercetin [32] were developed as cross-linking reagents for valve materials. The cross-linked samples were superior to GLUT in terms of mechanical properties, blood compatibility, and cell compatibility.
Figure 1. Schematic illustrations of the presumable cross-linking mechanism for RPC-PP. (A) Synthesis of PPMA. (B) Cross-linking of PPMA. PP, porcine pericardium; PPMA, porcine pericardium methacryloyl; RPC-PP, radical polymerization cross-linking-treated PP (adapted from Ref. [27]).
The focus of research on the bioprocessing of BHV involves the improvement of traditional GLUT cross-linking methods and the design of novel cross-linking methods. The special treatment employed by some researchers of BHVs cross-linked with ethanol, metal ions, -amino-oleic acid, and some other substances has effectively delayed the calcification of BHVs [33][34][35][36][37]. However, these methods still have many shortcomings. For example, epoxy cross-linked ECM-derived scaffolds are white, soft, and nonshrinking, with collagen remaining loose and natural [38]. Linear epoxy compounds exhibit low cross-linking and are also poorly stable due to their resistance to the degradability of collagen [38]. In addition, the epoxy compounds in the cross-linked extracellular matrix-derived scaffolds showed a degree of toxicity, leading to an immune response and eventual calcification failure [37][39][40]. The scaffold obtained by EDC cross-linking does not effectively inhibit calcification, which determines whether it can be used in the field of cardiovascular grafts [35]. The current substitution effect of cross-linkers has not been verified in the clinical stage. Therefore, although the development results of many cross-linkers are exciting, the ultimate success is yet to be achieved. Table 1 shows the basic research on non-glutaraldehyde cross-linking in the past 20 years.
Table 1. Application of different cross-linking agents in the study of tissue-engineered heart valves.

2.2. Modification Strategies after Decellularization

The decellularized porcine aortic valve is a promising alternative to the ideal tissue-engineered valve scaffold [50][51][52][53]. Pretreatment of the porcine aortic valve with fixatives and detergents can greatly stabilize xenografts, improve their persistence, and reduce immunogenic updates. However, biofunctionalized decellularized porcine valves, such as Synerggraft, have failed due to decreased mechanical properties and poor cell aggregation [54]. Therefore, surface biofunction has attracted widespread attention as an important means to improve the performance of decellularized valves.

2.2.1. Hydrogel Coating

Physical coatings can give the substrate an ideal morphology and corresponding biological function, which is simple, fast, and efficient compared with chemical modification. In recent years, hydrogels have been widely used in engineered tissue due to their good biocompatibility and adjustable mechanical properties, but their application has been limited due to poor mechanical durability. Therefore, hydrogel coatings based on decellularized scaffolds have been developed by many researchers. These coatings provide good biocompatibility and function as carriers for decellularized scaffolds, while decellularized scaffolds provide sufficient mechanical properties. A variety of hydrogels, including natural (e.g., collagen [35], fibrin [55][56], and hyaluronic acid [56][57]), synthetic (e.g., polyethylene glycol [58][59] and polyvinyl alcohol [60]), and composite hydrogels (e.g., type I collagen with chondroitin sulfate [61]), have been developed, which provide good biocompatibility and bioactivity for engineered tissue applications. Synthetic hydrogels are composed of synthetic polymers, which have the advantages of adjustable mechanical properties and structure and easy control of chemical composition compared with natural hydrogels. Taking enhanced endothelialization as an example, the researchers seemed to prefer to load vascular endothelial growth factor (VEGF) into hydrogels as a core factor and coat decellularized scaffolds using natural hydrogels such as hyaluronic acid [62], elastin [63], and alginate [64]. The types and functions of synthetic hydrogels are much more complex. They not only focus on solving the side effects of heart valve implants but also make more detailed adjustments to the mechanical properties and fatigue resistance of the hybrid scaffold. Luo et al. used methacrylic anhydride to modify the decellularized heart valves and applied a mixed hydrogel made of sulfa methacrylate and hyaluronic acid methacrylate to the surface to improve the anti-calcification performance of BHVs. This strategy could achieve both endothelialization and anti-calcification, thus helping improve the main drawbacks of the existing commercial BHV products [65]. In addition, Jahnavi et al. [66] developed a biological hybrid scaffold with a natural structure of non-cross-linked decellularized bovine pericardium coated with a layer of polycaprolactone-chitosan nanofibers, showing superior mechanical properties. These synthetic hydrogels solved individual problems to varying degrees, but for hydrogels, most of the studies did not take into account their own problems, that is, poor fatigue resistance, which leads to rapid damage during circulating hydrodynamic stress. Strengthening the mechanical properties of the overmolded hydrogel is a necessary condition for long-term protection. A dual-network hard hydrogel was developed in response to the anti-fatigue properties of single-mesh hydrogels. This gel penetrated and anchored the matrix of the decellularized porcine pericardium to form a strong and stable conformal coating, reduce immunogenicity, improve antithrombosis, and accelerate endothelialization (a schematic diagram is shown in Figure 2) [67]. In the last decade, researchers seem to have focused on the use of hydrogels in tissue-engineered heart valves, and as research continues to grow, various potential hydrogels have been proposed (Table 2). Hydrogel coatings are now gaining attention in this field, but most of these studies are currently in the initial research phase and have not reached the clinical stage. Hydrogel coatings still have a long way to go in this field, but the proposal of many research concepts has provided more ideas and perspectives for future researchers.
Figure 2. A schematic overview presenting the fabrication process, structure, and function of the decellularized porcine pericardium coated with polyacrylamide/hyaluronic acid dual-network hydrogel (adapted from Ref. [67]).
Table 2. Application of hydrogels in the study of tissue-engineered heart valves.

2.2.2. Cross-Linked with Nanocomposite

The advent of nanotechnology has made anti-tumor interventions possible. It also provides new ideas for TEHV. The nanoparticles have good biocompatibility. Furthermore, their surfaces have a variety of active groups, and researchers can modify them according to their purpose [71]. Common nanoparticles include lipids [72][73], polymers [74], inorganics [75][76], metals [77], and so forth. Nanoparticles are used in tissue-engineered heart valves mainly for gene transmission or the transmission of biologically active factors. This can effectively solve the limitation of cell seeding before TEHV implantation. A polyethylene glycol nanoparticle containing transforming growth factor-β1 was developed through a carbon diimide-modified fibrous valve scaffold that improved the ECM microenvironment of the tissue-engineered heart valves [78]. Based on this concept, researchers encapsulated VEGF in polycaprolactone (PCL) nanoparticles (Figure 3). Then, using the Michael addition reaction, PCL nanoparticles were introduced to the decellularized aortic valve, and a hybrid valve was prepared. The results showed that the mixed valve could effectively accelerate endothelialization [79]. A large number of nanoparticles used in tissue-engineered heart valves in recent years are biocompatible polymers, such as PEGs, PCL, and so forth. Recently, Hu et al. [80] were inspired by the natural biological systems and reported a new approach for cross-linking amino and carboxyl groups. The heart valves with erythrocyte membrane bionic drug-carrier nanoparticles were modified using amino and carboxyl groups remaining after GLUT cross-linking. This modified heart valve not only preserved the structural integrity, stability, and mechanical properties of GLUT-treated BHV but also significantly improved anticoagulation, anti-inflammatory, anti-calcification, and endothelialization properties.
Figure 3. Preparation scheme of VEGF-loaded nanoparticles and endothelialization of the hybrid valve (adapted from [79]).
An inorganic nanoparticle, mesoporous silica, has attracted much attention because of its advantages of good compatibility and adjustable particle size, pore size, and structure [81][82]. Pinese et al. [83] applied MSNs to tissue engineering and prepared siRNA/MSNPEI complexes for siRNA delivery. The results showed that siRNA/MSNPEI complexes were more efficient and less toxic than the traditional silencing methods. However, MSN has not been used in decellularized tissue engineering so far. Hence, this may be one of the key directions to be explored by researchers. Many metal nanoparticles, such as gold, silver, and titanium nanoparticles, have been widely examined in other fields. Their future performance in TEHV based on their basic properties is also worth examining. These nanoparticles can be used as a functional platform to achieve the transmission of a certain substance (Table 3 lists the basic research of nanocomplexes applied to tissue-engineered heart valves in the last 15 years). However, they seem to be more flexible in terms of modification and function and can even be used as a cross-linking agent to make the structure more stable.
Table 3. Application of different nanocomposites in the study of tissue-engineered heart valves.


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