Endothelial progenitors derived from induced pluripotent stem cells (iPSC-EPs) have the potential to revolutionize cardiovascular disease treatments and to enable the creation of more faithful cardiovascular disease models. Herein, the encapsulation of iPSC-EPs in three-dimensional (3D) collagen microenvironments and a quantitative analysis of these cells’ vasculogenic potential are described.
Induced pluripotent stem cells (iPSCs) are a patient-specific, proliferative cell source that can differentiate into any somatic cell type. Bipotent endothelial progenitors (EPs), which can differentiate into the cell types necessary to assemble mature, functional vasculature, have been derived from both embryonic and induced pluripotent stem cells. However, these cells have not been rigorously evaluated in three-dimensional environments, and a quantitative measure of their vasculogenic potential remains elusive. Here, the generation and isolation of iPSC-EPs via fluorescent-activated cell sorting are first outlined, followed by a description of the encapsulation and culture of iPSC-EPs in collagen hydrogels. This extracellular matrix (ECM)-mimicking microenvironment encourages a robust vasculogenic response; vascular networks form after a week of culture. The creation of a computational pipeline that utilizes open-source software to quantify this vasculogenic response is delineated. This pipeline is specifically designed to preserve the 3D architecture of the capillary plexus to robustly identify the number of branches, branching points, and the total network length with minimal user input.
Human umbilical vein endothelial cells (HUVECs) and other primary endothelial cell types have been utilized for two decades to model blood vessel sprouting and development in vitro1. Such vascular platforms promise to illuminate molecular and tissue-level mechanisms of cardiovascular disease and may present physiological insight into the development of primitive vascular networks2,3. Though the field of vascular modeling has witnessed significant advances, a “gold standard” assay that can quantitatively model and assess physiological vascular development remains elusive. Most published protocols do not adequately recapitulate the vascular niche to encourage the formation of mature, functional blood vessels or do not have a method to quantitatively compare the vasculogenic potential of the assessed cell types in three dimensions (3D).
Many current vascular models are limited in their ability to mimic the physiological vascular niche. One of the most commonly employed in vitro platforms is the gelatinous protein mixture-based tube formation assay. Briefly, HUVECs are seeded as single cells on a thin layer of gel that consists of proteins harvested from murine sarcoma extracellular matrix (ECM); within one to two days, the HUVECs self-assemble into primitive tubes4. However, this process occurs in two-dimensions (2D) and the endothelial cells (ECs) utilized in this assay do not form enclosed, hollow lumens, thereby limiting the physiological significance of these studies. More recently, ECs and supporting cells (e.g., mesenchymal stem cells (MSCs) and pericytes) have been co-cultured in 3D microenvironments that simulate the fibrous architecture of the native ECM, such as collagen or fibrin hydrogels5. To model vascular development in this microenvironment, polymeric beads coated with ECs are typically employed6. The addition of exogenous growth factors and/or growth factors secreted by other cells interstitially embedded in the hydrogel can induce the ECs, coating the polymeric beads, to sprout and form single lumen; the number and diameter of sprouts and vessels can then be computed. However, these sprouts are singular and do not form an enclosed, connected network as is seen in physiological conditions and thus is more reminiscent of a tumor vasculature model. Microfluidic devices have also been utilized to mimic the vascular niche and to promote the formation of vasculature in EC-laden hydrogels7,8. Typically, an angiogenic growth factor-gradient is applied to the circulating cell culture medium to induce EC migration and sprouting. ECs that constitute the lumen of developed vessels are sensitive to the shear stress induced by the application of fluid flow through the microfluidic device; thus, these microfluidic devices capture key physiological parameters that are not accessible in the static models. However, these devices require costly microfabrication abilities.
Most importantly, all three vascular models (2D, 3D, microfluidic) overwhelmingly utilize primary ECs as well as primary supporting cell types. Primary cells cannot be developed into an effective cardiovascular therapy because the cells would engender an immune response upon implantation; furthermore, HUVECs and similar primary cell types are not patient-specific and do not capture vascular abnormalities that occur in patients with a genetic disposition or pre-existing health conditions, e.g., diabetes mellitus. Induced pluripotent stem cells (iPSCs) have emerged in the past decade as a patient-specific, proliferative cell source that can be differentiated into all somatic cells in the human body9. In particular, protocols have been published that outline the generation and isolation of iPSC-derived endothelial progenitors (iPSC-EPs)10,11; iPSC-EPs are bipotent and can, therefore, be further differentiated into endothelial cells and smooth muscle cells/pericytes, the building blocks of mature, functional vasculature. Only one study has convincingly detailed the development of a primary capillary plexus from iPSC-EPs in a 3D microenvironment12; though this study is critical to an understanding of iPSC-EP assembly and differentiation in natural and synthetic hydrogels, it did not quantitatively compare the network topologies of the resulting vasculature. Another recent study has used the polymeric bead model to compare the sprouting of HUVECs and iPSC-derived ECs5. Therefore, there is a clear need to further elucidate the physical and chemical signaling mechanisms that regulate iPSC-EP vasculogenesis in 3D microenvironments and to determine if these cells are suitable for ischemic therapy and cardiovascular disease modeling.
In the past decade, different open-source computational pipelines and skeletonization algorithms have been developed to quantify and compare vascular network length and connectivity. For example, Charwat et al. developed a Photoshop-based pipeline to extract a filtered, binarized image of vascular networks derived from a co-culture of adipose-derived stem cells and outgrowth ECs in a fibrin matrix13,14. Perhaps the most widely used topology comparison tool is AngioTool, a program published online by the National Cancer Institute15; despite the program’s widespread adoption and well-documented fidelity, the program is limited to analyzing vessel-like structures in two dimensions and other programs, including AngioSys and Wimasis, share the same dimensionality limitation16. Powerful software suites such as Imaris, Lucis, and Metamorph have been developed to analyze the network topology of engineered microvasculature; however, these suites are cost-prohibitive for most academic labs and limit access to the source code, which may hinder the ability of the end-user to customize the algorithm to their specific application. 3D Slicer, an open-source magnetic resonance imaging/computed tomography package, contains a Vascular Modeling Toolkit that can effectively analyze the topology of 3D vascular networks17; however, the analysis is dependent on the user manually placing the end-points of the network, which may become tedious when analyzing a large dataset and can be influenced by the user’s subconscious biases. In this manuscript, a computational pipeline that can quantify 3D vascular networks is described in detail. To overcome the above-outlined limitations, this open source computational pipeline utilizes ImageJ to pre-process acquired confocal images to load the 3D volume into a skeleton analyzer. The skeleton analyzer uses a parallel medial axis thinning algorithm, and was originally developed by Kerschnitzki et al. to analyze the length and connectivity of osteocyte networks18; this algorithm can be effectively applied to characterize the length and connectivity of engineered microvasculature.
Altogether, this protocol outlines the creation of microvascular networks in 3D microenvironments and provides an open-source and user-bias free computational pipeline to readily compare the vasculogenic potential of iPSC-EPs.
1. Preparation of culture media and coating solutions
2. Thawing, maintenance, and passaging of iPSCs
3. Generation of iPSC-derived endothelial progenitors (Figure 1).
4. FACS of endothelial progenitors
5. Encapsulation and long-term culture of iPSC-EP-laden collagen hydrogels
6. Fixing, immunostaining, and visualization of EP-based vascular networks
7. Using the computational pipeline to analyze and compare vascular network topologies
After differentiation (Figure 1), FACS and encapsulation of iPSC-EPs in collagen hydrogels, the cells will typically remain rounded for 24 h before beginning to migrate and form initial lumens. After about 6 days of culture, a primitive capillary plexus will be visible in the hydrogel when viewed with brightfield microscopy (Figure 2). After imaging the fixed, stained cell-laden hydrogels on a confocal microscope (Movie 1, Supplemental Movie 1), the pre-processed images are converted to a skeleton which enables an analysis of the overall length and connectivity of the network. These quantitative measures can then be used to determine which set of conditions are optimal for producing robust vascular networks.
This protocol allows for the development of a robust, three-dimensional capillary plexus that is responsive to local physical and chemical cues. In previous work, this network formation has been shown to be sensitive to matrix density, matrix stiffness, matrix metalloprotease inhibition, and the type and concentration of various angiogenic mitogens20,23.
Figure 1: Generation of iPSC-EPs from pluripotent stem cells. (A) WiCell 19-9-11 iPSCs, which stained positive for Oct4, were cultured in E8 medium supplemented with 10 μM Y-27632 ROCK inhibitor for 48 h. (B) The iPSCs were then induced with 6 μM of CHIR99021 in LaSR Basal medium for 48 h, at which point the cells were positive for Brachyury, a mesoderm marker. (C) The cells were further cultured in LaSR Basal media until they expressed CD34, a marker for endothelial progenitors. (D) Roughly 15%–25% of the differentiated cells expressed CD34. All scale bars represent lengths of 200 μm. Please click here to view a larger version of this figure.
Figure 2: Generation and analysis of iPSC-EP vascular networks in collagen hydrogels. (A) A cross-section of the 3D microenvironment used in this assay to promote vascular network formation from iPSC-EPs. A floating collagen hydrogel is seeded with iPSC-EPs and exposed to EGM-2 supplemented with 50 ng/mL VEGF and a temporal dose of Y-27632. (B) The resulting capillary plexus is highly branched and interconnected, as visualized via staining with F-actin (cyan). The binarized image, shown on the left, is generated by pre-processing with ImageJ. This z-stack is then analyzed via a previously developed algorithm, which skeletonizes the network (shown in a collection of thin red lines) and then analyzes the network topology for branches (yellow), end points (blue), isolated vessels (black), and connected vessels (red). The scale bar represents a length of 100 m. (C) Morphological changes of iPSC-EPs-laden collagen hydrogels: 24 h after seeding, the iPSC-EPs remain spherical and within 96 h gradually take on a more elongated phenotype. Further culture results in assembly of lumen-containing VE-Cadherin network, as shown in the inset at the 144-h time point. The scale bars represent lengths of 400 μm; green = VE-Cadherin, red = F-actin, and blue = DAPI. Please click here to view a larger version of this figure.
Movie 1: Z-stack of VASCULATURE GENERATED FRom iPSC-EPs. Vascular networks were fixed, stained with F-actin, and visualized by acquiring z-stacks on a confocal microscope. Slices were acquired at 17 μm intervals. Please click here to view this video. (Right-click to download.)
Supplemental Movie 1: 3D rendering of vessels. Vascular networks were fixed, stained with F-actin (red) and VE-cadherin (green), and visualized by acquiring z-stacks on a confocal microscope. Please click here to download this file.
This protocol involves the long-term culture of cells in three types of cell culture media: E8, LaSR Basal, and EGM-2. Therefore, great care should be taken to appropriately sterilize all materials. Additionally, lab coats and ethanol-cleaned gloves should always be worn when working in the laboratory’s laminar flow hood. It is recommended to frequently test for mycoplasma contamination; if a large amount of debris is observed during iPSC culture or a sudden drop in differentiation efficiency is noted, mycoplasma contamination is a likely cause. iPSC-EPs generated with this protocol tend to deposit a significant amount of ECM, which lengthens the dissociation time and causes the single cell suspension to separate into small clumps. Do not use Trypsin-EDTA (0.25%), as the solution may disrupt CD34 epitopes on iPSC-EPs. However, treatment with collagenase/dispase solution may remove deposited ECM and ease dissociation with a standard cell detachment solution. After extensive dissociation, some small clumps of cells and ECM may remain; remove these clumps with a P100 pipette tip, as they are likely to clog the cell strainers or interfere with the FACS.
Pluripotent stem cells are sensitive to dissociation and will undergo apoptosis in a single-cell suspension unless a ROCK inhibitor (commonly Y-27632) is added to the medium24. iPSC-EPs are also sensitive to dissociation; including Y-27632 at 10 μM for the first 24 h of culture is imperative to increase cell survival and proliferation. Therefore, it is critical that a ROCK inhibitor is included in both the hydrogel and surrounding medium immediately following FACS. The seeding density of iPSC-EPs also significantly impacts vessel development and total network size. Generally, a concentration of 500,000 cells/mL to 3 million cells/mL is an appropriate range of seeding densities. A further increase in seeding density often leads to hydrogel compaction and cell death.
The density of ECM structural proteins has been found to have a significant impact on the development of engineered microvasculature25,26. Generally, increasing the density of an ECM-based hydrogel (often collagen or fibrin) limits vascular network length and connectivity. Therefore, it is critical that careful attention is paid to the collagen matrix density; concentrations below 2 mg/mL promotes the premature proteolytic degradation of collagen hydrogels, which results in an irreparable loss of the hydrogel’s structural integrity. In contrast, concentrations above 4 mg/mL induce the formation of short, wide lumen that exhibit poor connectivity; hydrogel deformability and a change in pore size are primarily responsible for this abrogation20.
Acellular and cell-laden collagen hydrogels do not bind to the ultra-low attachment plates; the hydrogels tend to remain suspended in the media and will occasionally float to the top of the well. If tissue culture-treated plates are employed in this protocol, the embedded progenitors will migrate to the bottom of the well and will form a near confluent monolayer at the bottom of the plate. The resulting decrease in cell seeding density inhibits the assembly of these progenitors into 3D networks. Additionally, if hydrogels are cast into the wells of a tissue culture treated plate, they will weakly bind the inner surface of the well; this binding applies strain to the hydrogel. Since this platform was developed to isolate the importance of physical and chemical cues, it is critical that no extraneous forces are imparted to the cells27. The floating hydrogels may be difficult to feed because most of the cell culture media lies below the hydrogel; to overcome this, tilt the plate and use a P100 pipette to remove media from the side of the wall.
When imaging the vascular networks on a confocal microscope, it is critical to follow all washing steps to ensure that excess fluorophore does not result in a low signal to noise ratio. Excess fluorescence may confuse default thresholding algorithms and make the z-stack difficult to binarize. To overcome this issue, use phalloidin, a fungal toxin that selectively labels F-actin and displays limited off-target binding. In general, use primary antibodies that have been pre-conjugated to a secondary antibody to limit the concentration of free fluorophore that diffuses through the gel. When generating the z-stacks a slice depth of 10-20 microns is recommended to balance the time needed for acquiring a z-stack against the need for a high-resolution image.
Here a quantitative assay to assess the vasculogenic potential of iPSC-EPs in 3D microenvironments is described. This assay utilizes open source software and is unaffected by user biases. Still, it represents an oversimplified model of the physiological vascular niche. While iPSC-EPs can differentiate into the cells needed for mature, functional vasculature, this assay neglects the contributions of other cell types (e.g., fibroblasts and macrophages) that participate in vasculogenic processes. Furthermore, this system is static and does not expose the developing vessels to flow. Finally, while collagen I is one of the dominant proteins in the ECM28 and maintains its fibrillar architecture in vitro, it is lot-dependent and is limited to weak physical crosslinking when neutralized at high temperatures. Despite these limitations, this assay represents a significant step forward in the quest to engineer functional vasculature for cardiovascular disease therapy and modeling.
The authors have nothing to disclose.
This work was supported by the American Heart Association (grant number 15SDG25740035, awarded to J.Z.), the National Institute of Biomedical Imaging and Bioengineering (NIBIB) of the National Institutes of Health (grant number EB007507, awarded to C.C.), and the Alliance for Regenerative Rehabilitation Research & Training (AR3T, grant number 1 P2C HD086843-01, awarded to J.Z.). We would like to acknowledge Prof. Jeanne Stachowiak (The University of Texas at Austin) for her technical advice on confocal microscopy. We are also grateful for discussions with Samuel Mihelic (The University of Texas at Austin), Dr. Alicia Allen (The University of Texas at Austin), Dr. Julie Rytlewski (Adaptive Biotech), and Dr. Leon Bellan (Vanderbilt University) for their insight on the computational analysis of 3D networks. Finally, we thank Dr. Xiaoping Bao (University of California, Berkeley) for his advice on differentiating iPSCs into iPSC-EPs.
µ-Slide Angiogenesis | Ibidi | N/A | A flat, glass bottom tissue-culture plate with side walls enables facile confocal imaging |
96 well, round bottom, ultra low attachment microplate, sterile | Corning | 7007 | Prevents the binding of cell-laden collagen hydrogels to the cell culture dish |
Accutase | STEMCELL Technologies | 7920 | Gentle cell detachment solution; does not degrade extracellular epitopes vital for FACS |
Advanced DMEM/F12 | Thermo Scientific | 12634010 | The base media for iPSC-EP differentiation. |
Barnstead GenPure xCAD Plus | Thermo Fisher Scientific | 50136165 | Water purification system; others can be readily substituted |
Bovine Serum Albumin solution,7.5% in DPBS, sterile-filtered, BioXtra, suitable for cell culture | Fisher Scientific | A8412 | To preserve cell viability when FACs sorting |
CD34-PE, human (clone: AC136) | Miltenyi Biotec | 130-098-140 | Antibody used for FACs isolation of iPSC-EPs |
CHIR99021 | LC Laboratories | C-6556 | Induces the formation of mesoderm from pluripotent stem cells |
Collagen I Rat Tail High Protein 100 mg | VWR | 354249 | Main component of the 3D microenvironment |
Conical centrifuge tubes (15/50 mL) | Fisher Scientific | 14-959-49D/A | Used to store and mix relatively large volumes of reagents and cell culture media |
DAPI (4',6-Diamidino-2-Phenylindole, Dihydrochloride) | Thermo Fisher Scientific | D1306 | To counterstain and visualize cell nuclei |
DMEM/F12 | Thermo Fisher Scientific | 11320-082 | For dilution of Matrigel and thawing of pluripotent stem cells |
Dulbecco's phosphate-buffered saline (DPBS) | ThermoFisher | 14190-250 | To wash monolayer cultures |
EDTA | Sigma-Aldrich | E8008 | For passaging of pluripotent stem cell colonies and to prevent cell aggregation when FACs sorting |
Endothelial Cell Growth Medium 2 | PromoCell | C-22011 | Promotes endothelial cell viability and proliferation |
Essential 8 Medium | Thermo Fisher Scientific | A1517001 | For maintenance of pluripotent stem cells |
Glycine,BioUltra, for molecular biology, >=99.0% (NT) | Sigma-Aldrich | 50046 | Neutralizes remaining detergent |
L-Ascorbic acid 2-phosphate sesquimagnesium salt hydrate,>=95% | Sigma-Aldrich | A8960 | Component of iPSC-EP differentiation medium |
MATLAB | MathWorks | 1.8.0_152 | Multi-paradigm numerical computing environment (free available at most academic institutions) |
Matrigel Matrix GFR PhenolRF Mouse 10 mL (gelatinous protein mixture) | Fisher Scientific | 356231 | Diluted in DMEM/F12 to coat plates for iPSC-EP differentiation |
Medium-199 10X | Thermo Fisher Scientific | 1825015 | Used to balance final hydrogel osmolarity and pH |
Microcentrifuge tubes (1.7 mL) | VWR | 87003-294 | Stores small volumes of reagents |
Phosphate-buffered saline (PBS) | Sigma-Aldrich | P3813 | The main ingredient of the immunostaining solutions |
Penicillin-Streptomycin (10,000 U/mL) | Thermo Fisher Scientific | 15140122 | Antibiotic used after sorting to remove possible contamination from FACS instrument |
Recombinant Human VEGF 165 Protein | R&D Systems | 293-VE | Mitogen that stimulates endothelial cell proliferation and tubulogenesis |
Rhodamine phalloidin | Themo Fisher Scientific | R415 | To identify F-actin deposition and therfore outline the borders of the vascular networks |
Triton X-100 (nonionic surfactant) | Sigma-Aldrich | X-100 | Detergent used to gently permeabilize cells |
Tween-20 (emulsifying reagent) | Fisher Scientific | BP337 | Increases the binding specificity of the added antibodies |
VE-Cadherin (F-8) | Santa Cruz Biotechnology | sc-9989 | To identify 3D endothelial lumen in collagen hydrogels |
Vitronectin | ThermoFisher | A14700 | For maintenance of pluripotent stem cells |
Y-27632 | Selleck Chemicals | S1049 | Preserves pluripotent stem cell and iPSC-EP viability when dissociated and re-seeded |