Experimental and computational models for tissue-engineered heart valves: a narrative review.

Valvular heart disease is currently a common problem which causes high morbidity and mortality worldwide. Prosthetic valve replacements are widely needed to correct narrowing or backflow through the valvular orifice. Compared to mechanical valves and biological valves, tissue-engineered heart valves can be an ideal substitute because they have a low risk of thromboembolism and calcification, and the potential for remodelling, regeneration, and growth. In order to test the performance of these heart valves, various animal models and other models are needed to optimise the structure and function of tissue-engineered heart valves, which may provide a potential mechanism responsible for substantial enhancement in tissue-engineered heart valves. Choosing the appropriate model for evaluating the performance of the tissue-engineered valve is important, as different models have their own advantages and disadvantages. In this review, we summarise the current state-of-the-art animal models, bioreactors, and computational simulation models with the aim of creating more strategies for better development of tissue-engineered heart valves. This review provides an overview of major factors that influence the selection and design of a model for tissue-engineered heart valve. Continued efforts in improving and testing models for valve regeneration remain crucial in basic science and translational researches. Future research should focus on finding the right animal model and developing better in vitro testing systems for tissue-engineered heart valve.

Introduction

Valvular heart disease affects an increasing number of patients in both developed and developing countries. Since the use of mechanical or bioprosthetic valves, the number of valve replacement procedures performed each year has been constantly increasing and is expected to reach 850,000 implantations worldwide by 2050.[1, 2] As a particularly vulnerable patient population, children with congenital heart malformations often require multiple reoperations because current repair materials lack inherent growth, and this is associated with an exponentially increased risk of surgical complications.[3] In addition, mechanical valves are prone to inflammation, infection and thrombosis, while bioprosthetic valves experience calcification which has both stiffening and thickening effects on the valve cusps, eventually leading to insufficient valve closure and leakage. Consequently, many of the patients implanted with these prosthetic heart valves are exposed to a lifelong risk of valve prosthesis-related morbidity and mortality.[4]

The design of tissue-engineered heart valves (TEHVs) with self-repair, remodelling and regeneration capacity allows the replacement of whole or part of diseased tissues or organs with biomimetic replicates to address the limitations of current mechanical and bioprosthetic valves, and may become a promising therapeutic alternative for patients with valvular disease, particularly paediatric and elderly patients.[5]

To make better use of TEHVs in clinical patients, the regulatory framework governing the safety and efficacy of medical devices can be considered in three distinct phases of product study: preclinical studies, clinical studies, and post-market monitoring. Among them, pre-clinical studies comprise in-vitro (i.e., engineering and material characterisation) and in-vivo components (i.e., animal models). Animal testing of cardiovascular devices can provide invaluable information on their safety, but there are still many uncertainties in the anatomical and physiological structure of the animal model. In addition the evaluation of large animals is difficult, and requires a lot of financial and human investment, consequently it is very important to select an appropriate model for performance evaluation in the construction stage.[6]

The formation of engineered tissue is influenced by inflammation, cell migration, proliferation, the evolution of cell phenotypes, extracellular matrix (ECM) production, polymer or biological material degradation, and tissue remodelling, while the structure and performance of the valve stent also needs to be fully considered if implanted through transcatheter aortic valve implantation, so an appropriate and low-cost model is urgently needed to investigate possible problems with the valve. In this review, we summarise several commonly-used models such as animal models, bioreactors and computational modelling to understand the influence of biomechanical properties in TEHVs.

Search Strategy

The articles about animal models, bioreactors and computational modelling for TEHVs were using the following conditions: ((heart valve tissue engineering) OR (heart valve) OR (tissue engineering)) AND ((animal model) OR (model)) were describing animal models. Then, the articles about bioreactors were retrieved by the search terms: ((heart valve tissue engineering) OR (heart valve) OR (valve cells)) AND ((bioreactor) OR (model)). In addition, the computational modelling used in heart valve was performed using the following conditions: ((heart valve tissue engineering) OR (heart valve)) AND ((computational modelling) OR (silico model)). All these searches were retrieved on PubMed and Web of Science databases prior to June, 2021. The results were further screened by title and abstract. Finally, 128 articles were included in this review.

Strategies for Tissue Engineered Heart Valves

Four essential elements needed for the synthesis of functional TEHVs are scaffolds from natural or synthetic biomaterials, cells encapsulated within scaffolds, signalling molecules to regulate cell responses, and models to test the implantability of TEHVs.[7] There are three types of scaffold available: (1) Decellularised ECM: obtained by physical agitation, chemical surfactant removal, and enzymatic digestion to remove antigenic materials and allogeneic cells from the graft,[8] so that the decellularised scaffold can be seeded with cells derived from the intended recipient.[9] (2) Natural biodegradable materials: derived from natural matrix materials and displaying robust biocompatibility, including collagen, hyaluronate, gelatine, glycosaminoglycan, chitosan, alginate, fibrin, silk, dextran, and Matrigel.[10] (3) Synthetic biodegradable materials: including poly(glycolic acid) (PGA), polylactic acid, polylactic-co-glycolic acid, poly(L-lactic acid), poly-ε-caprolactone, polyethylene glycol, polyvinyl alcohol, polypropylene fumarate, polyacrylic acid, and others.[11] Various tissue-engineering approaches have been used: (1) In vitro: autologous or allogenic cells are isolated and seeded onto a bioresorbable scaffold and then cultured in a bioreactor system until the new composite scaffold has sufficient mechanical elasticity and strength for implantation.[12] (2) In vivo: this strategy relies on fibrotic encapsulation of valvular moulds implanted subcutaneously with autologous ECM.[13-15] (3) In situ: decellularised homograft or xenograft materials are implanted to grow cells and remodel the ECM[15-17] ().

Figure 1

Schematic illustration showing tissue engineered heart valves strategies. (a) In situ, tissue engineered heart valve approaches are derived from decellularised homograft or xenograft scaffolds and can be reshaped by various cells and tissue sources. (b) Bioresorbable polymeric scaffolds can be manufactured by the method of electrostatic spinning and implanted in vivo without cell growth. (c) Bioresorbable polymeric scaffolds are pre-seeded with autologous cells. (d) In vivo, a non-degradable valve scaffold is implanted subcutaneously in an animal to induce the formation of fibrous tissue. (e) In vitro, autologous or allogeneic cells are cultured on a bioresorbable synthetic scaffold in a bioreactor system with a culture medium (M). Created with smart.server.com and ChemDraw.

Animal Models

The rapid development of TEHVs and in situ tissue-engineering triggered the studies on animals. Although animal models are essential to determine the clinical potential of TEHVs, because they are complete organisms that can mimic human physiology to some extent, there are still no ideal animal models or international consensus on standards. To further verify the safety and efficacy of TEHVs, several appropriate pre-clinical animal models, including large and small animals whose hearts are similar to that of humans, were translated into the preclinic. Briefly, small animals are used for in vivo assessments such as subcutaneous implantation,[13, 18-21] while large animal models are used to test functionality and re-cellularisation in situ [22-30] ().

Table 1

Animal models used in TEHV studies.

Species	TEHV manufacture	Surgical method	Functionality assessment and postmortem analysis	Reference
Small animal model
Mouse	Sulfonic polymer hybrid extracellular matrix	Subdermal	Histological and immunohistochemical analysis	18
Rat	Glut-fixed porcine aortic valve	Subdermal	Histological and quantitative analysis	19
	Electrospinning polycaprolactone scaffold	Subdermal	Scanning electron microscopic and histological analysis	20
	Allogeneic aortic conduit grafts	End-to-side anastomosis with infrarenal aorta	Histological and immunohistochemical analysis, quantitative real-time polymerase chain reaction	21
Rabbit	Poly urethane scaffold	Subdermal	Macroscopic and histological analysis	13
Large animal model
Adult sheep	Poly(glycolic acid) scaffold	Pulmonary valve replacement via transcatheter-based jugular	Intracardiac echocardiography, cardiac magnetic resonance imaging, computed tomography, histological and immunohistochemical analysis	22
	Polyvinylidene fluoride scaffold	Left anterolateral thoracotomy	Inspected for thrombotic deposits, light microscopic analysis, electron microscopic analysis or processed for extracellular matrix assay	23
Juvenile sheep (13–17 kg)	Tissue-engineered porcine pulmonary valved conduit	Off-pump cardiopulmonary bypass/left anterolateral thoracotomy	Transthoracic ultrasound echocardiography, mortality, operating time	24
Foetal ovine	PCL scaffold	Transcatheter pulmonary valve replacement	Ultrasound (pulmonary valve annulus), foetal outcome	25
Yorkshire pigs (80 kg)	AZ31 magnesium alloy biodegradable stent frame scaffold-based polycarbonate urethane urea TEHV	Cardiopulmonary bypass in the pulmonary position	Echocardiography, biaxial mechanical testing, scanning electron microscopy	26
Porcine	Decellularised porcine pulmonary heart valves	Median sternotomy or limited lateral thoracotomy, then injection of TEHV	Echocardiographic examination, invasive pressure, angiographic measurements	27
Vietnamese pigs	Decellularised porcine aortic valves conduit	Xypho-jugular incision, followed by median longitudinal sternotomy	Echocardiography, macroscopic inspection, metabolic labelling	28
Canine	Decellularised porcine pulmonary heart valves	Left anterolateral thoracotomy	Echocardiography, histology (haematoxylin and eosin, Masson) and immunohistochemistry, transmission electron microscopy	29
Non-human primate (Chacma Baboon)	Poly(glycolic acid) scaffold	A mini-sternotomy using an antegrade transapical approach	Transesophageal echocardiography, epicardial echocardiography, Pulmonary artery pressure measurement, biochemical analysis	30

Note: TEHV: tissue-engineered heart valve.

Small animal models

The history of using small animals as models to explore valvular heart disease can be traced back to the 1950s.[31] Small animal models have been popular and widely used since the surgical approach and assessing methods were accepted by researchers, for their easy approach and economic advantages.

In the area of TEHV studies, the most frequently-used small animal subdermal models include mice, rats and rabbits. Below, we introduce their characteristics and applications in translational research into TEHVs.

Mouse

Due to their small size, assessment of TEHVs in mice is much more difficult than in other animal models. This animal model is typically used to evaluate the development of cardiac tissue and differentiation of valves, but ways of appraising the functionality of TEHVs in mice is challenging. Subdermal implantation models are the most commonly-used models at present. Mice have unique advantages including convenience in gene editing, availability of a great variety of immunodeficient strains, and multiple types of antibodies. Kim et al.[32] implanted porcine and bovine pericardium, aortic valve and aortic wall into the subcutaneous tissue of wild-type and α-gal knockout mice. Enzyme-linked immunosorbent assay analyses were used to measure anti-α-gal antibody titres before and after implantation. Histopathology and quantification of calcification revealed that immunoreaction to α-gal may cause more severe calcification in α-gal knock-out mice.[32] Bioprosthetic heart valves (BHVs) have also been subcutaneously implanted in mouse models. Guo and his colleagues[18] used sulphonic monomers to crosslink with decellularised ECM to obtain hybrid ECM. Then a mouse subdermal model was used to evaluate immune responses and calcification. The results indicated that BHVs crosslinked with sulphonic polymer hybrid ECM exhibited better biocompatibility compared with those crosslinked with glutaraldehyde.[18] These studies reveal a potential mechanism of BHV calcification and provide novel perspectives in TEHV design. Although, mice models have unique advantages above, the single subdermal approach and difference of cardiovascular physiology still limit the use of mice. Otherwise, we discover that the back area of mice is so small that if multi-type grafts are subcutaneously implanted in mouse models, the grafts may affect each other, which reduces the veracity of the result.

Rat

The cheap cost is the advantage of this species. In addition, the convenience of anaesthesia and management, and the availability of various strains make rats a common choice in translational medical research. However, the small size brings challenges to surgeons in the development of animal experiments. Another problem is that the haemodynamics and physiology of the rat are not similar to those of the human.

Rat subdermal models have been proven to be an ideal model for assessment of immunoreaction and biological compatibility after implantation.[33] Lovekamp and colleagues[19] implanted tissue-engineered valve samples in juvenile rats through a small dorsal incision and subdermal pocket to evaluate calcification in vivo. Histological analysis and quantitative results showed extensive areas of calcification in tissue samples.[19] Jana et al.[20] employed a tri-layered nanofibrous substrate manufactured through electrospinning to imitate the structure of a heart valve. Then the TEHV sample was implanted subcutaneously into a rat model for 2 months. The results showed that cells infiltrated into the structure and glycosaminoglycans and elastin were observed, demonstrating good regeneration.[20]

In addition, other experimental methods have been developed such as implantation into the systemic circulation. Assmann and his colleagues[34] implanted decellularised aortic conduits by fibronectin surface coating into the systemic circulation of Wistar rats for 8 weeks. Compared with controls, decellularised scaffold coated with bioactive proteins accelerated autologous re-cellularisation.[34] Nevertheless, due to the small size, the graft was not able to open and close to simulate the function of valves in human haemodynamics as in large animal models.

Rabbit

The rabbit is the largest of small animal models, so that larger grafts can be implanted for study. Ye and colleagues[29] used scanning electron microscopy to characterise the surface of rabbit heart valves. Based on the results, they developed a microstructural model of a heart valve to investigate the best geometric parameters of the rough surface of the valves to improve the replacement of heart valves.[29] In addition, like rats, rabbit subdermal models have been used in TEHV studies. Hayashida et al.[13] manufactured an autologous heart valve using a poly-urethane scaffold and implanted it in a rabbit subdermal model for 4 weeks, after which the graft was harvested for macroscopic and histologic analyses to evaluate its mechanical properties and microstructure. The results proved the good biocompatibility of the polymer scaffold.

Large animal models

The best large animal models traditionally used in the assessment of TEHVs include non-human primates (NHPs), sheep or goats, pigs, and dogs. TEHVs are usually implanted in situ into these animal models. In these studies, the safety, functionality, biocompatibility, and durability of TEHVs were assessed. The choice of appropriate animal models for TEHV research is very important and can significantly influence the cost and outcome of the research. For instance, if the long-term durability of TEHVs is the aim, sheep may be a preferred model since pigs may grow faster, which results in the insufficiency of the implantation. Nevertheless, in addition to somatotype, gender and age should also be taken into account. However, there is no specific selection criterion so far. Here we succinctly summarise the large animal models used in studies of TEHVs.

Sheep

The ovine model is the gold standard animal model in translational research into TEHV replacement that satisfies the requirements of the U.S. Food and Drug Administration.[35] The similarity of the size of the heart valves and the animal’s cardiovascular physiology to those of the human make the sheep an ideal model for use in TEHV studies. These species also have the advantages of a long neck, which means that the carotid artery and jugular vein—the most common surgical approach for transcatheter replacement of TEHVs—are easily accessible. In addition, sheep are fast-maturing animals and adult individuals do not grow so that they can be used in assessment of long-term functionality and durability of the grafts. TEHVs manufactured from polymer or decellularised scaffolds have been used in adult sheep models. Emmert and colleagues[22] used computer modelling to design PGA polymer scaffold TEHVs, and implanted them into the pulmonary valves of sheep using minimally-invasive percutaneous transjugular access, then used intracardiac echocardiography, computed tomography (CT), and magnetic resonance imaging to evaluate the functionality of the graft. After sacrifice, immunohistochemistry and other methods were used to assess the remodelling of the valve.[22] The outcome suggested that TEHVs based on computer modelling can effectively overcome valve insufficiency due to the contraction of leaflets and adverse tissue remodelling.[36] Shinoka et al.[37] constructed TEHVs from PGA biodegradable scaffold seeded with fibroblasts and endothelial cells and implanted them into pulmonary valves of sheep. After 8 weeks, transplanted autologous cells generated ECM on the scaffold, and showed good regenerative ability.[37]

In addition to the above, there are also other options in terms of the age of the animals and the surgical approach. Wu et al.[24] used lamb models to compare the outcomes of off-pump cardiopulmonary bypass (CPB) and left anterolateral thoracotomy in TEHV replacement. Flanagan et al.[23] used left anterolateral thoracotomy and normothermic CPB to replace pulmonary valves. Zakko et al.[25] used transcatheter valve replacement technology to successfully perform pulmonary valve replacement surgery on foetal ovine. Overall, these studies show that the ovine model is a very appropriate model to evaluate short-term complications and the long-term durability of implanted TEHVs.

Pig

This species is widely used as a surgical model and also for translational researches.[38, 39] Due to its resemblance to humans in terms of cardiovascular anatomy and physiology, pigs can be used in assessment of heart valves. However, the sensitivity of the species’ hearts presents difficulties with anaesthesia, and the tendency of pigs to easily contract infection makes them need specific sterile methods and more nursing care.[40] In addition, CPB used in porcine surgery may lead to chronic arterial occlusion and cardiac death.[41] Further, their large size and rapid growth rate can also lead to insufficiency of the graft, which affects the long-term assessment, so that miniature pigs have become popular for translational medical research in recent years.

Pig models have been used to assess the functionality and durability of implanted TEHVs. In one innovative study, Coyan and colleagues[26] employed AZ31 biodegradable magnesium alloy as a frame scaffold, then applied a polycarbonate urethane urea coating to the surface. The Yorkshire pigs then underwent open TEHV implantation during CPB in the pulmonary position. Echocardiography, biaxial mechanical testing, and scanning electron microscopy all showed that the grafts retained their mechanical strength and ultrastructure, without platelet activation or thrombosis.[26] Decellularised porcine pulmonary valves have also been used in piglet models. Schlegal et al.[27] successfully implanted decellularised TEHVs in juvenile pigs under fluoroscopic guidance. The results of angiography and epicardial echocardiography revealed no trans- or paravalvular leakage, and the haemodynamic parameters were stable.[27] Diminutive pigs such as Vietnamese pigs have been considered to be a suitable model for assessment of novel TEHVs in the right ventricular outflow tract,[42] and an intra-operative protocol has been developed.[43] Gallo and colleagues[44] implanted decellularised aortic valves in Vietnamese pigs for 15 months, and the results of haemodynamic analysis and regeneration were satisfactory, demonstrating the potential of the grafts. Pigs are also the models of choice for transcatheter aortic valve replacement, in the same way as sheep.[45] The surgical access for transcatheter aortic valve replacement in pigs and sheep may be via the femoral or jugular vein.[46-48] However, the jury is still out regarding which species allows more accurate evaluation of the functionality of the graft. At present, anatomic studies have shown that sheep have long necks and thus if the catheter is long, the sheep may be a better model.[49] Moreover, the size of a sheep is smaller and more similar to a human compared to a pig. However, there is a remarkable analytical difficulty associated with this model at the protein level because of the lack of appropriate antibodies.

Dog

Since the first studies on dogs by William Harvey in the 17th century, the use of canine models in the field of cardiovascular research has been developed. Because of their moderate size — between 10 and 30 kg — and their docile character, dogs have become appropriate animal models to work with. Compared with other large animals, their thinner skin makes implantation of catheters easier, and allows convenient imaging. In addition, the advantage of dogs in TEHV studies is the lower risk of postoperative infection.[28] However, obtaining and maintenance of dog models are notably more expensive than small animal models, which should be taken into consideration when long-term studies are designed. Although Institutional Animal Care and Use Committee guidelines vary from agency to agency, the use of dogs as animal models is often difficult to obtain approval compared with other large animal models. In addition, the number of animals that can be used is limited, even though the use of dogs is reasonable and appropriately approved. These issues should be considered by reviewing specific institutional policies before designing studies.[50]

Due to the restrictions above, developing studies for the assessment of TEHVs implanted in dogs is extraordinarily hard. Iwai and colleagues[51] tested the functionality of decellularised porcine pulmonary valves in dogs for 6 months. Left anterolateral thoracotomy and normothermic CPB were performed for the implantation. Echocardiography demonstrated that the functionality of the grafts was good, without thickening of the leaflets, regurgitation or thrombosis. Spontaneous re-endothelialisation of the leaflet surface was observed through haematoxylin and eosin staining, confirming regeneration of the structure.[51] Nevertheless, the size of dogs and their hearts impose restrictions on further use.

Non-human primates

Due to their similarity to humans in terms of genome, cardiovascular anatomy and physiology, NHPs are considered to be attractive animal models for preclinical research to simulate many diseases such as enteric viral infection,[52] human immunodeficiency virus vaccine,[53] multiple sclerosis,[54] and myocardial infarction. Yang et al.[52] used NHP models to analyse the effect of induced pluripotent stem cell-derived cardiomyocytes in two-dimensional monolayer and three-dimensional engineered heart tissue. Moreover, NHPs, represented mostly by rhesus monkeys and baboons, have the advantage of an immunological response similar to humans, which makes NHPs a better choice for studies of the biocompatibility of TEHVs in xenograft implantation.[55]

Baboons have been used as an ideal animal model for assessment of the functionality of TEHVs. During one study in 2013 by Weber et al.[30] decellularised PGA scaffold TEHVs were implanted into the pulmonary valve of baboons by minimally-invasive surgery under fluoroscopic guidance, then non-invasive imaging technologies were used to assess the position and in vivo functionality. The results revealed that the morphology and functionality of the graft were retained for more than 8 weeks. Macroscopic outcomes revealed the initial contraction of leaflets, and no formation of thrombus. Transmission electron microscopy showed re-cellularisation on the surface of the scaffolds. Quantitative DNA analysis showed that cell density was similar to that of natural valves in primates.[30] The success of the off-the-shelf decellularised TEHVs in preclinical models provided encouraging evidence that decellularised TEHVs may be a potential clinical alternative. Nevertheless, the ethical considerations and higher cost of purchase and management limit the use of NHPs in studies of TEHVs. On all accounts, small animal models are widely used for their easy approach and economic advantages. The general subdermal approach is used for assessment in chronic immunological response and calcification of TEHV. An ideal immunological response to TEHV subdermal implantation has three periods. In the hyperacute process, protein absorption occurs on the surface of TEHV. Then acute and chronic inflammations occur in turn. In the acute phase, invaded monocytes differentiate into macrophages, an ideal non-immunogenic TEHV will not induce invasion of massive neutrophils. The pro-inflammation M1 subtype is observed in the initial week, then in the chronic period, the macrophages shift towards the anti-inflammation M2 subtype. Eventually, mesenchymal progenitor cells migrate from surrounding tissue, differentiate into valvular interstitial cells, and produce new matrix.[56] In conclusion, inflammatory cells infiltration in the acute inflammation period may not mean poor biocompatibility, because the remodelling generally occurs after inchoate inflammation. Nevertheless, pro-inflammation cells found on the graft after months to years mean adverse chronic response, which leads to calcification and failure of TEHVs.

For translational medical research, large animal models are used to confirm the results in small animal models and evaluate the long-term functionality, biocompatibility, and durability. The commonly used large animal models in TEHV studies include sheep, pigs, dogs, and NHP. To determine which model is optimal requires several decisions including the cost, animal welfare, similarity to human cardiac anatomy and physiology, and surgical approach. Here we summarise the advantages and disadvantages of various animal models in .

Table 2

Advantages and disadvantages of animal models and bioreactors used in tissue-engineered heart valve studies.

Species & bioreactors	Advantages	Disadvantages
Small animal model
Mouse	Low cost of maintenance, ease of gene-editing and surgical manipulation, multiple types of antibodies	Not-suitable for in situ studies for small size and mismatched anatomy and physiology
Rat	Low cost of maintenance, ease of surgical approach, access for implantation into the systemic circulation	Not-suitable for in situ studies
Rabbit	Low cost of upkeep, larger size for larger graft implantation	Especially suitable for ectopic studies (subcutaneous implantation)
Large animal model
Sheep	The golden standard for translational studies, the similarity of body size to human, easy access for transcatheter replacement of tissue-engineered heart valves, suitable growing speed for growing model	Higher cost of purchase and upkeep, special facilities required for housing
Pig	Resemblance to humans in terms of cardiovascular anatomy and physiology, access to transgenic models	Higher cost of purchase and upkeep, special facilities required for housing, higher risk of post-operation infection, the possibility of chronic arterial occlusion and cardiac death after CPB, unsuitable growing speed compared with sheep
Dog	Docile character, thin skin for implantation of catheters and convenient imaging, lower risk of post-operative infection	Higher cost of purchase and upkeep, special facilities required for housing, difficulty in getting approval
Non-human primate	The best model for translational clinical research for anatomical, physiological, genetic, and immune similarity	The highest cost of purchase and upkeep, special facilities required for housing and social needs of primates, special equipment, and training required for surgical approach
Bioreactors
Pulse-flow bioreactors	The anatomy is more similar to the physiology	Generate complex and ill-defined mechanical conditioning, which cannot be readily controlled
Single mechanical stimulus bioreactor	The type and size of the mechanical stimulation can be finely adjusted	Only single stimulation can be made, a good cultural environment is needed and high cost
Multi-mechanical stimulus bioreactor	Know the synergistic effect of different combinations of mechanical stimuli on cells and tissues	May exist mutual interference that led to inconsistent results
Computer-regulated bioreactor	Predictable, easy to understand hydrodynamic parameters	Only mechanical simulations, not chemical and biological ones

Bioreactors

Heart valves in our bodies encounter a variety of complex mechanical forces. During each cardiac cycle, native valves are continuously subjected to highly-complex tension, flexure, pressure, and shear stress forces as a result of blood flow, for example, aortic valve leaflets experience peak fluid-induced shear stresses of approximately 64–71 dyn/cm2 during systole.[57] To better understand each component’s contribution to cellular behaviour and implementation, these mechanical forces must be separated. In an engineered heart valve tissue context, mechanical stimuli, particularly those that incorporate fluid-induced shear stress, have been shown to enhance progenitor cell differentiation pathways,[58] regulate ECM remodelling,[59] impact the behaviour of valvular endothelial cells behaviour[60] or endothelial mesenchymal transformation,[61] and induce morphological remodelling in cells cytoskeleton.[57]

Pulse-flow bioreactors

In order to simulate complicated cardiovascular systems and the clinical application conditions for functional TEHVs, the pulsatile-flow testing apparatus was designed with blood pumps, vessels and valves to measure the transvalvular pressure, the regurgitation fraction, and the effective orifice area at a certain heart rate and flow rate to evaluate the risk of transcatheter heart valve substitution.[62, 63]

The major advantages are that it does not involve humans or animals with no ethical issues, and it saves a lot of money compared to in vivo experiments.[64] Otherwise, pulse-flow bioreactors can also elucidate the mechanism of the cellular responses[65] and the interactions between cells and scaffold materials under different mechanical and biochemical conditions, as indicated by a large number of publications from their advent to the present day.[66, 67] But they often generate complex and ill-defined mechanical conditioning, which cannot be readily controlled.

Thus, a more controlled mechanical conditioning has been studied that can mimic physiological haemodynamic conditions, including the cyclic stretching, flexure, laminar flow, oscillatory shear stress, and pressure that native valves are exposed to and to sufficiently reproduce these environments in an in vitro setting to grow engineered heart valves[68, 69] (). A good example of bioreactor with subtle control is Ibidi pump system, a typical commercial bioreactor, which can exert and accurately regulate a variety of shear forces on cells or valvular tissues, including laminar oscillatory flow, as well as large-scale use. Therefore, it is widely used in mechanical stimulation related researches.[70-72]

Figure 2

Schematic representation of cyclic stretching, laminar flow, pulsatile flow, oscillatory shear stress, and pressure in a bioreactor.

Stretch bioreactor

Mechanical stretch is one of the physical cues from an organismal level to a subcellular level, which is associated with many physiological and pathological processes such as beating heart or bone remodelling processes. It is worth noting that mechanical stretch, as an important novel pretreatment method in tissue engineering, has been widely used. For example, cyclic stretch preconditioning improves engineered muscle contraction.[73] In addition, proper mechanical stimulation may promote the regeneration of cell-based ligaments and improve the success rate of transplantation.[74] Ku et al.[75] used a Flexcell bioreactor to stretch valve cells and mesenchymal stem cells and showed that 14% stretching upregulated expression of the type I collagen gene and increased collagen synthesis. Syedain and Tranquillo[76] also developed a controlled cyclic stretch bioreactor for TEHVs that resulted in improving tensile and compositional properties. To sum up, the mechanical stretch may promote tissue regeneration by influencing cell biological characteristics.

Flexure bioreactor

In vivo, cyclic flexure plays a vital role on heart valve deformation, the flexure bioreactor is necessary to evaluate candidate TEHV scaffolds and constructs. Engelmayr et al.[77] stimulated ovine vascular smooth muscle cells by using a bioreactor with unidirectional cyclic three-point flexure at a physiological frequency and amplitude. The result showed that, compared to static groups, flexure had independent effects on TEHV cell and ECM development and even on the mechanical properties of TEHV scaffolds.[77] Another study has showed that the mechanical properties of PGA/poly(L-lactic acid) fibre scaffolds have changed under dynamic flexure.[78] In a word, the flexure bioreactor can investigate the underlying mechanisms of which flexure influences tissue development and produce quantitative and qualitative changes in the mechanical properties of TEHV scaffolds.

Laminar flow bioreactor

In vascular tissue engineering, unidirectional laminar shear stress has favourable effects on endothelial progenitor cells,[79-81] inducing an antithrombotic and anti-atherosclerotic phenotype and, promoting endothelial cell survival.[82] Furthermore, cyclic flexure and laminar flow can synergistically promote tissue formation, underlying a rational design of in vitro preconditioning programs for tissue engineering.[77]

Oscillatory shear stress bioreactor

Gonzalez et al.[83] seeded human bone-marrow-derived mesenchymal stem cells onto synthetic, biodegradable scaffolds and cultured them under physiologically-relevant oscillatory shear stresses for 2 weeks. The result showed that the expression of endothelial cell markers augmented and the level of the activated α-smooth muscle phenotype was reduced. Studies also showed that oscillatory shear stress determined the direction of endothelial progenitor cell differentiation, such as facilitating the transition of endothelial progenitor cells into mesenchymal cells by increasing expression of the Kir2.1 ion channel[84] and reactive oxygen species/protein kinase Cζ/p53 pathway have played an important role in it.[85] In conclusion, oscillatory shear stresses alone are significant to the development of TEHV.

Pressure bioreactor

In a TEHV framework, fluid-induced shear stresses can induce stem cell differentiation. Using a bioreactor as a tool for seeding with cyclic waveforms tuned to various negative and positive chamber pressures showed that subjecting the system to positive pressure improved infiltration of human mesenchymal stem cells into the aortic valve leaflet, while retaining gene expression within the mesenchymal stem cell– valve interstitial cell phenotype lineage.[86]

Multi-mechanical stimulus bioreactor

To identify mechanical stimuli physiologically relevant to cells and biomaterials[78] in the dynamic flexure and laminar flow experinced by TEHVs,[87] Engelmayr et al.[88, 89] designed a flex-stretch-flow bioreactor and seeded bone marrow-derived mesenchymal stem cells onto PGA and poly(L-lactic acid) scaffolds. They found that, after 4 days of static culture and 3 weeks of dynamic incubation, cyclic flexure and laminar flow synergistically accelerated bone marrow-derived mesenchymal stem cell-mediated tissue formation. Compared to the effect of static conditions, the aortic valve leaflets produced more collagen exposing to oscillatory and laminar flow environment, glycosaminoglycans and elastin, which suggested that fluid flow is important for the remodelling of valve ECM.[90]

In contrast to laminar flow and pulsatile flow bioreactors designed to stimulate engineered tissues before, Engelmayr et al.[91] designed the flexure, stretch, and flow bioreactor which allows to control fluid flow and specimen deformation independently. This novel feature is essential to the differentiation between the effects of flow and strain-mediated stimuli. Elsewhere, flexure, stretch, and flow bioreactors have also verified that coupled mechanical stimuli significantly promote ECM production; in particular, the combination of steady flow with cyclic flexure.[58] A pressure-controlled bioreactor and a laminar-flow bioreactor were used to analyse the effects of pressure and shear stress independently, to understand the individual and synergistic effects of the two forces by measuring endothelin-1 and nitric oxide release from human umbilical vein endothelial cells.[92] Using a bioreactor with non-physiologic conditioning parameters for TEHVs has led to inconsistent results, such as hypoxia and high cyclic pressures which may increase cellular migration and infiltration into the valve leaflet tissue and interstitial cellular repopulation.[93]

Computer-regulated bioreactor

Bioreactors and computers can be combined to create computational fluid dynamics technology which enables a better understanding of hydrodynamic parameters that influence cell function and remodelling of tissue engineering constructs.[94] Williams et al.[95, 96] employed a computational approach to establish a range of oscillatory shear stresses that may optimize in vitro valvular tissue growth and demonstrated that the fluid-oscillating effect in combination with a physiologically-relevant shear stress magnitude contributes to the de novo formation of stem cell-derived heart valve tissues. A pulsatile bioreactor has been designed to be controlled by a closed-loop feedback computer system that can change automatically to simulate both physiologic and non-physiologic haemodynamic conditions. The result showed that the valve tissues change as the modulations of pulsatile pressure and/or flow waveforms are changed.[67]

Alongside the rapid development of TEHVs, bioreactors have also been improved to better mimic physiological haemodynamics;[97, 98] the value of bioreactor conditioning lies in developing not only the mechanical properties but also the biological properties of a valve including the capacity for remodelling, repair, and growth.[99] These biological properties enable improvements in durability, growth, and blood compatibility that TEHVs promise to deliver to the clinic. However, disadvantages also exist, for example, extra time and cost are associated with the bioreactor-conditioning of a TEHV. The contamination risk is also significant, which means that a good aseptic technique is critical and antibiotics should be added to the culture medium when possible.[63]

Computational Modelling

Computational modelling, particularly when integrated with experimental studies, can substantially accelerate our comprehension of inter-species differences in TEHV adaptation,[22] differential remodelling and functionality,[100] and the interaction between immune systems-mediated and mechanical stress-driven regenerative processes. Computational modelling of valve mechanics[101] and corresponding tissue remodelling provides a powerful approach to predict the consequences of changes in valve design to help inform the rational selection of scaffold parameters to fabricate TEHVs[102] (). Computational modelling helps designing TEHVs and consistently predicts valve in vivo tissue remodelling and long-term functionality in a large animal model. These findings indicate that integrating computational simulation into tissue engineering approaches can lead to predictable clinical outcomes and the promotion of clinical effectiveness[22, 103-119] ().

Figure 3

Schematic representation showing that the computational modelling mimics the physiology (a), biomechanical properties (b) and geometry (c) of heart valves in silico (d) to clarify the role of these parameters in the development of TEHVs to enable better use of in vivo models (f). TEHV: tissue-engineered heart valve. Created with Biorender.com and smart.server.com and ChemDraw.

Table 3

Advantages and disadvantages of animal models and bioreactors used in tissue-engineered heart valve studies.

Model	Application	Objective	Year	Reference
Computational modelling	Tissue-engineered heart valve	Guiding tissue-engineered heart valve design for long-term in vivo performance in a translational sheep model	2018	22
	Tissue-engineered vascular graft	Identifying optimal design parameters to save development time and costs while improving clinical outcomes	2019	103
	Bioprosthetic heart valve	Investigating the impacts of bovine and porcine pericardium tissues with different thicknesses and tissue mechanical properties in bioprosthetic heart valve applications	201920172016	104-106
	Tissue-engineered heart valve	Integrating computational simulation into tissue-engineering approaches can lead to more successful and predictable clinical outcomes	2018	107-109
Biomechanical model	Aortic stenosis	Providing the results of the numerical simulation of the valve function	2020	110
Finite element models	Congenital bicuspid aortic valve	Quantifying aortic valve and root biomechanical alterations associated with bicuspid geometry	2010	111
	Calcific aortic valve disease	Studying the calcification progression in aortic valves	2017	112
	Bioprosthetic heart valve	Comparing tensile properties of xenopericardium to choose tissue more appropriate for bioprosthetic heart valve tissue	2020	113
Three-dimensional bioprinting	Heart valve	Using computational fluid dynamics, digital image processing, artificial intelligence, and continuum mechanics during their optimisation and implementation to mimic the original and understand valvular problems	20192018	114, 115
Geometric model	Functional tri-leaflet aortic valves	Establishing a list of geometric guidelines to ensure safe operation of the valve during the cardiac cycle	2006	116
Numeric model	Aortic root	Studying the correlation between intraoperative effective height and diastolic coaptation	2013	117
Neural network material model	Simulation of the aortic heart valve	Providing an efficient computational analysis framework with increased physical and functional realism for the simulation of native and replacement tri-leaflet heart valves	20212020	118, 119

The short-term functionality of TEHVs was demonstrated to be excellent in many pre-clinical studies, but leaflet retraction often leads to valvular insufficiency in medium-term follow-up. Many factors that contribute to leaflet retraction such as cellular traction,[120] remodelling of the collagen network,[121, 122] and contraction of the matrix components. Computational models are necessary to increase our understanding of the underlying mechanisms, and predict the risk for the development of valvular insufficiency.[123]

Emmert et al.[22] adopted computational modelling of valve mechanics and corresponding tissue remodelling to provide a powerful approach to predict the consequences of changes in valve design on the overall outcome.[124] For example, the mechanical behaviour of TEHVs can influence α-smooth muscle actin expression that leads to leaflet retraction and cardiovascular tissue remodelling.[125] The use of computational modelling predicted that a more physiological valve geometry[126] in combination with a relatively large coaptation area would considerably increase the radial stretch of TEHVs and hence potentially reduce the development of retraction.[127] Loerakker et al.[123] also used a computational approach to predict the remodelling process in TEHVs subjected under dynamic pulmonary and aortic pressure conditions, and improve assessment of the risk of valvular insufficiency. In addition, they also investigated the importance of intrinsic cell contractility on the valvular matrix remodelling process in the end. Additionally, the model predicted that valvular insufficiency is unlikely because the blood pressure is high enough to prevent the development of leaflet retraction.[123] Another study with a computational modelling design indicated that TEHV geometry can significantly influence the host cell response by determining the infiltration and presence of macrophages and α-smooth muscle actin-positive cells, which play a crucial role in orchestrating TEHV remodelling.[128]

Considering the rapid advancement of studies relevant to computational simulations for the design of BHV in recent years, appropriate models also can be selected to examine the role of different aspects of tissue-engineered valvular function, for example, using structural mechanics, computational fluid dynamics, and coupled fluid-structure interaction models can analyse the geometry of the valvular apparatus, accurate time-evolving biomaterial models, and accurate boundary conditions over the cardiac cycle, thus providing information regarding optimal geometries of the TEHVs that would be valuable for clinical diagnosis and treatment.[105]

Although computational methods have proven to have high potential, the application and advancement of computational models in cardiovascular tissue engineering applications have presented some challenges. For example, the increased incorporation of features of biological growth and remodelling in computational models usually lead to increased model complexity. To obtain a model that can replicate the physiological problem more closely, the development of numerical methods to a number of models is essential for the optimisation for scaffold properties and for the prediction of TEHV function and adaptation.[21]

Conclusion & Perspectives

Although TEHVs have a good application prospect, the mechanical and biological characteristics that can meet the standard for in vivo application have not been fully studied, so appropriate experimental models are needed for simulation in order to reach the standard of clinical application as soon as possible.[107]

In this review, we summarise the animal models, bioreactors and computational models, to better simulate the biomechanical characteristics of heart valves. An animal model is a complex and complete organism, which simulates the haemodynamic state of the human body as much as possible, as well as the situation related to pathophysiology and immunology. Bioreactors are designed for the assessment of the dynamic mechanical stimulation of tissue-engineered materials and implants. These devices typically generate a complex biomechanical environment resembling in physiological conditions, and have been showed to promote both the development of mechanical strength, and the modulation of cellular function within the tissue-engineered construct. Further, the pulsatile-flow testing assesses haemodynamics and clarifies associated risks. Computational models also play an important role in the development of TEHVs, because it can be used to infer the reliable function of BHV by analysing the influence of design, tissue mechanics and haemodynamics by numerical simulation, while at the same time, it also helps us to understand the potential mechanism and provide guidance and insight for optimising the design of future artificial valves.

Current experimental and computational models for TEHVs have not yet succeeded to fully replicate the structure, function and mechanical environment of native heart valves. Understanding of the molecular mechanisms involved and development of markers to evaluate TEHV is crucial. For the translation from bench to bed, a set of key targets for characterizing in vivo remodelling and regeneration upon TEHV implantation still needs to be explored. Prior to implantation in humans, long-term preclinical studies are required to assess the remodelling of TEHV towards native tissues. More importantly, correspondences or contradictions between preclinical models and human data should be revealed, to accurately predict clinical outcome of TEHV. There is currently no standard model for the evaluation of TEHVs. Some important aspects that need to be considered in choosing a correct model for TEHVs include the research objectives, cost, animal welfare, species, size, and site of implantation. Continued efforts in improving and testing models for valve regeneration remain crucial in basic science and translational research. Future research should focus on finding the right animal model and developing better in vitro testing systems for TEHVs. Optimization of experimental and computational models will have great promotion of clinical translation of TEHVs.