Disease modeling and functional screening using engineered heart tissue
Introduction
The translation of promising drug candidates into clinical therapeutics is a time-consuming and costly process, with 9 out of 10 candidates failing to progress from Phase I trials to clinical approval [1, 2]. Furthermore, many targets identified using cell culture or small-animal models fail to translate in pre-clinical testing due to lack of efficacy. There is a need to improve our current methods of modeling human biology and disease, which may lead to the identification of better candidates for clinical translation. One approach is to use tissue engineering to develop 3D tissues and screening platforms that more closely mimic in vivo physiological and pathophysiological processes. Currently, tissue engineered products can be stratified into two primary applications: firstly, making new tissue for implantation and replacement/repair of lost or damaged organs, or secondly, creation of engineered constructs to mimic the native tissue as an in vitro model system. It is important to highlight that these two different applications may require very different tissue engineering strategies. Implantation requires integration with the host, sufficient tissue to replace the lost or damaged tissue, a safe and defined product and, additionally, may require factors to tailor the potentially hostile new environment and ensure long-term functionality [3]. However, when creating a tissue as an in vitro model system, the tissue needs to re-capitulate the functional and physiological properties of interest, and the tissue needs to be amenable to manipulation (e.g. genetic or pharmacological manipulation) to study the effects of biological factors. In addition, it may also be beneficial for these model systems to be scaled down to sizes amenable to screening to reduce the costs associated with producing the tissue. Whilst a model tissue will never be exactly the same as its in vivo counterpart, a good model only needs to be well suited to addressing the particular physiological or disease processes in question. As the famous statistician George E.P. Box once wrote, ‘essentially all models are wrong, but some are useful’ [4].
Recent advances in the re-capitulation of in vivo-like structure and function with in vitro organoids is providing more accurate models of human biology and disease. The term organoid was originally used to describe tumors, which ‘resemble an organ in structural appearance or qualities’ (Marriam-Webster Medical Dictionary). However, it is now also widely used to describe 3D engineered tissues or cultures that re-capitulate their in vivo counterparts, ‘ex vivo multicellular fragments that contain the major cell types of a particular organ and approximate its in vivo organization’ [5]. The development of multiple organ systems is becoming widespread with: liver [6], intestinal [7, 8], stomach [9], optic cup [10], cerebral [11, 12], lung [13], kidney [14], and heart [15••] organoids having been developed and used as model systems. The development of engineered heart tissue (EHT) has progressed steadily over 20 years, making it one of the most studied organoid models to date.
Tissue engineering was originally dominated by the ideology of seeding polymer constructs with cells. In the cardiac field, this approach was one of the first to be employed [16, 17] and has been widely used over time [18, 19, 20, 21, 22] (reviewed in [23]). Additionally, other methodologies such as micro-patterns/devices [24, 25, 26], cell sheets [27], and de-cellularised hearts [28] have also been used to create cardiomyocyte cultures for modeling or regenerative approaches. However, most studies have achieved in vivo-like cardiac organoids by embedding the cells in extracellular matrix hydrogels, first pioneered by the Eschenhagen group [29]. Multiple natural matrices have now been used to embed the cells, the most widespread being collagen I, Matrigel and/or fibrin [15••, 30••, 31••, 32, 33]. Embedding the cells in a bioactive hydrogel enables the cells to not only re-arrange to form organoid structures [15••], but also enables the cells themselves, rather than the substrate [18], to dictate the mechanical properties of the EHT [34], which is critical for optimal cardiomyocyte function [34, 35]. Additionally, mechanical loading directly imparts load onto the cells and cardiomyocytes in the EHT [34], and greatly improves the structure and function of EHT [36, 37]. The in vivo-like properties, and the recent ability to make human EHT using pluripotent stem cell-derived cardiac cells [31••, 38, 39, 40, 41••, 42] (Figure 1), have made EHTs an attractive platform for multiple modeling applications over the past few years, as summarized and discussed in this review. Please note that while the term EHT specifically refers to the fabrication method depicted in Figure 1, we have used the term EHT to describe all engineered culture formats in this review for simplicity.
Section snippets
The importance of cellular interactions
A number of studies have shown that non-cardiomyocyte populations are important for EHT formation. EHT composed of both cardiomyocytes and non-cardiomyocyte populations display enhanced cellular alignment and functional properties compared to pure cardiomyocyte EHT [18, 43, 44••, 45]. EHT made with pure or enriched cardiomyocyte populations fail to properly re-arrange and form elongated muscle bundles after seeding, which negatively impacts functional output [31••, 40, 46, 47]. As a result,
Genetic disease modeling
The ability to generate human models of cardiac disease using patient-matched induced pluripotent stem cells (iPSCs) and gene editing technologies has revolutionized cardiovascular research in recent years. One of the great promises of cardiac tissue engineering is that it would advance the study of iPSC-derived cardiomyocyte phenotypes due to the enhanced maturity, functionality and physiological relevance of 3D organoids compared with standard 2D monolayer cultures (see above). For example, a
Modeling diverse cardiac pathological stimuli using EHT
Heart failure is a chronic, progressive disease that results in compensatory mechanisms that trigger structural and functional remodeling in an attempt to maintain cardiac output. By altering environmental factors in the EHT environment, many of the key features of cardiac dysfunction can be recapitulated in an in vitro setting (summarized in Table 3). A seminal example of this was an increased afterload model pioneered by the Eschenhagen lab [58••, 59, 60]. By increasing the stiffness of the
Modeling regeneration and screening for regenerative therapeutics
Another application of EHT is to study aspects of human cardiac developmental and regenerative biology that are difficult to assess in vivo. For example, recent studies suggest that the mammalian heart has the ability to regenerate following injury during fetal/neonatal life [69, 70], but whether this ability also exists in humans is currently unclear. To assess whether immature human heart tissue has an innate capacity for regeneration following injury, we recently developed an in vitro model
EHT as a human model system for future biomedical research
Cardiomyocytes derived from human pluripotent stem cells have been widely characterized as embryonic or fetal in nature [74, 75, 76]. These model systems have been very useful in studying a wide variety of different genetic diseases, toxicology and environmental stimuli [77, 78, 79]. However, development of more mature cardiomyocytes will be beneficial for many of the most important biomedical applications including improving the predictability for drug toxicology assays [80, 81, 82] and
Conflict of interest statement
R.J.M., J.E.H. and E.R.P. are listed as inventors on patents relating to EHT technologies.
References and recommended reading
Papers of particular interest, published within the period of review, have been highlighted as:
• of special interest
•• of outstanding interest
Acknowledgements
E.R.P. and J.E.H. are supported by fellowships and grants from the National Health and Medical Research Council of Australia, the National Heart Foundation, Stem Cells Australia, The University of Queensland and the Victorian Government's Operational Infrastructure Support Program.
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These authors contributed equally.