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Ischemic heart disease is a leading cause of morbidity and mortality worldwide, affecting at least 20.5 million people in the United States alone1,2,3. Without adequate perfusion, prolonged hypoxia results in cardiomyocyte (CM) death and myocardial dysfunction. Myocardial ischemia is primarily treated with revascularization via percutaneous intervention, thrombolytic therapy, or coronary artery bypass grafting. However, revascularization is a double-edged sword and can cause additional injury via the release of reactive oxygen species4,5. While reperfusion strategies have been immensely successful, approaches to limit CM loss during ischemic insults or after reperfusion have been more elusive. Though many attempts to salvage infarcted tissue prove effective in animal models of ischemia-reperfusion, these same therapies have largely been unable to achieve significant benefit in human trials, raising a need for human models to evaluate CM-sparing or replenishing therapeutics6,7,8,9,10,11,12.
Human platforms used to model cardiac injury include primary tissues and human induced pluripotent stem cell (hiPSC)-derived systems13,14. Because primary tissues are constrained by sample availability, hiPSC systems have emerged as the dominant human platform for cardiac disease modeling, with the distinct advantages of being genetically tractable and scalable15,16,17,18,19. Traditional 2D hiPSC-derived cardiomyocyte (hiPSC-CM) cultures are limited by the immaturity of the resulting CMs, the absence of complex tissue architecture, and an inability to reproduce the full cellular diversity found in the human heart15,20. To address these shortcomings, engineered 3D heart tissues (EHTs) have become increasingly adopted20,21,22,23,24,25,26. EHT approaches include mixing pre-differentiated cardiac cells into spheroids24 or seeding differentiated cardiac cells into scaffolds or molds21,22,27. Although EHTs can better model heterotypic cellular interactions and have relatively more maturity than 2D cultures, the requirements for custom scaffolds or bioreactors to create and maintain EHTs currently limit their scalability21,27,28.
Self-assembling cardiac organoids (hCOs), or cardioids, are a new and powerful in vitro human model system20,25,26,29. hCOs have several advantages. First, they can include multiple cell types, including endothelial cells, fibroblasts, and epicardial cells, without the need for multiple specialized differentiation protocols26,29,30. Second, most of their differentiation occurs in 3D suspension culture, obviating the requirements for specialized molds or tissue matrix25,26,29,30. Finally, hCOs have a stereotypical spherical morphology with a central cavity, enabling morphological analyses. Thus, hCOs have scalability similar to 2D culture systems while retaining some of the tissue complexity of EHTs. hCOs have been used for drug toxicity testing, patient-specific disease modeling, and to model aspects of cardiac development20,26,30,31,32,33,34,35,36,37,38,39. While promising, hCOs have several limitations compared to EHTs, including an inability to directly measure force output. Further, there is no native immune cell population in the described hCO models, though it is possible to populate hCOs with macrophages. Nevertheless, hCOs are an emerging and rapidly evolving human model system20,26,30,31,32,33,34,35,36,37,38,39.
To date, modeling cardiac injury with hCOs has been limited. A cryoinjury model has been described, but injuries are highly variable, and the need to individually injure hCOs limits scalability29. This manuscript describes a user-friendly protocol for generating and injuring self-assembling hCOs with hypoxia-reoxygenation (H/R) injury. Compared to other protocols for generating hCOs, this protocol uses a simplified differentiation medium and incorporates the 2D-3D mesoderm differentiation strategy described by Hofbauer et al.29. The protocol for H/R injury can be performed any time after hCOs begin beating, which typically occurs around differentiation day 8 (D8) to D11. H/R duration can be titrated between 6 h and 24 h to achieve the desired level of injury, ranging from minimal to near complete CM loss. Additionally, hCOs stereotypically develop a collagenous core with Vimentin+ cells after H/R injury that also scales in severity with H/R duration. This high-throughput, scalable hCO model of H/R injury potentially addresses the need for human models to develop and test new therapeutic avenues for promoting CM recovery or regeneration after injury.