Here we present a protocol to fabricate a kidney cortex extracellular matrix-derived hydrogel to retain the native kidney extracellular matrix (ECM) structural and biochemical composition. The fabrication process and its applications are described. Finally, a perspective on using this hydrogel to support kidney-specific cellular and tissue regeneration and bioengineering is discussed.
Extracellular matrix (ECM) provides important biophysical and biochemical cues to maintain tissue homeostasis. Current synthetic hydrogels offer robust mechanical support for in vitro cell culture but lack the necessary protein and ligand composition to elicit physiological behavior from cells. This manuscript describes a fabrication method for a kidney cortex ECM-derived hydrogel with proper mechanical robustness and supportive biochemical composition. The hydrogel is fabricated by mechanically homogenizing and solubilizing decellularized human kidney cortex ECM. The matrix preserves native kidney cortex ECM protein ratios while also enabling gelation to physiological mechanical stiffnesses. The hydrogel serves as a substrate upon which kidney cortex-derived cells can be maintained under physiological conditions. Furthermore, the hydrogel composition can be manipulated to model a diseased environment which enables the future study of kidney diseases.
Extracellular matrix (ECM) provides important biophysical and biochemical cues to maintain tissue homeostasis. The complex molecular composition regulates both structural and functional properties of tissue. Structural proteins provide cells with spatial awareness and allow for adhesion and migration1. Bound ligands interact with cell surface receptors to control cell behavior2. Kidney ECM contains a plethora of molecules whose composition and structure varies depending on anatomical location, developmental stage, and disease state3,4. Recapitulating the complexity of ECM is a key aspect in studying kidney-derived cells in vitro.
Previous attempts at replicating ECM microenvironments have focused on decellularizing whole tissue to create scaffolds capable of recellularization. Decellularization has been performed with chemical detergents such as sodium dodecyl sulfate (SDS) or non-ionic detergents, and it utilizes either whole organ perfusion or immersion and agitation methods5,6,7,8,9,10,11,12,13. The scaffolds presented here preserve the structural and biochemical cues found in native tissue ECM; furthermore, recellularization with donor-specific cells has clinical relevance in reconstructive surgery14,15,16,17,18,19. However, these scaffolds lack structural flexibility and are therefore incompatible with many current devices used for in vitro studies. To overcome this limitation, many groups have further processed decellularized ECM into hydrogels20,21,22,23,24. These hydrogels are compatible with injection molding and bioink and circumvent micrometer scale spatial constraints that decellularized scaffolds place on cells. Furthermore, molecular composition and ratios found in native ECM are preserved3,25. Here we demonstrate a method to fabricate a hydrogel derived from kidney cortex ECM (kECM).
The purpose of this protocol is to produce a hydrogel that replicates the microenvironment of the kidney cortical region. Kidney cortex tissue is decellularized in a 1% SDS solution under constant agitation to remove cellular matter. SDS is commonly used to decellularize tissue because of its ability to quickly remove immunological cellular material6,7,9,26. The kECM is then subject to mechanical homogenization and lyophilization5,6,9,11,26. Solubilization in a strong acid with pepsin results in a final hydrogel stock solution20,27. Native kECM proteins that are important for structural support and signal transduction are preserved3,25. The hydrogel can also be gelled to within one order of magnitude of native human kidney cortex28,29,30. This matrix provides a physiological environment that has been used to maintain the quiescence of kidney-specific cells compared to hydrogels from other matrix proteins. Furthermore, matrix composition can be manipulated, for example, through the addition of collagen-I, to model disease environments for the study of renal fibrosis and other kidney diseases31,32.
Human kidneys were isolated by LifeCenter Northwest following ethical guidelines set by the Association of Organ Procurement Organizations. This protocol follows animal care and cell culture guidelines outlined by the University of Washington.
1. Preparation of Human Kidney Tissue
2. Fabrication of Hydrogel Stock Solution
3. Hydrogel Gelation
The kECM hydrogel provides a matrix for kidney cell culture with similar chemical composition as the native kidney microenvironment. To fabricate the hydrogel, kidney cortex tissue is mechanically isolated from a whole kidney organ and diced (Figure 1). Decellularization with a chemical detergent (Figure 2A.1-A.3) followed by rinses with water to remove detergent particles (Figure 2A.4-A.6) yields isolated kidney cortex ECM. Histological evaluation confirms typical basal laminar proteins such as collagen-IV and laminin and structural proteins such as collagen-I are preserved, with vitronectin as the only noted exception (Figure 2B). Furthermore, protein composition, including preservation of isoforms, in the ECM remains consistent with observed values in native kidney ECM (Figure 3). The ECM (Figure 4A) is mechanically homogenized and lyophilized (Figure 4B) then solubilized to produce the final kECM hydrogel (Figure 4C). The kECM hydrogel appeared opaque with small amounts of visible tissue and was not as viscous as traditional collagen-I hydrogel. Rheological measurement of gelled kECM at a concentration of 15 mg/mL revealed a complex modulus (dynamic elastic modulus) of around 800 Pa over the linear range of strain values, significantly greater than that of 7.5 mg/mL collagen-I (p = 1.602E-14). Human kidney peritubular microvascular endothelial cells (HKMECs) cultured on collagen-I, kECM, and a 1:1 mixture gel showed differences in phenotype, specifically in CD31 expression around cell surfaces and junctions (Figure 5). HKMECs cultured on collagen-I displayed uniform CD31 expression while HKMECs cultured on the two gels containing kECM displayed reduced CD31 expression in uneven distributions. Matrix type did not appear to affect the high PV1 and low VWF expression in the HKMECs.
Figure 1: Isolation of kidney cortex tissue. Mechanical processing of a whole kidney organ to isolate the cortex tissue as a base material for the kECM hydrogel. Mechanical isolation begins with (A) the removal of the perirenal adipose tissue. Large pieces of adipose tissue can be torn away from the kidney with hemostat clamps. Remaining pieces of adipose tissue can be removed by running a scalpel against the renal capsule at an angle. (B) The renal capsule is best removed by making a shallow incision along the superior end of the kidney and (C) peeling the renal capsule away from the underlying tissue with hemostat clamps. (D) Bisecting the kidney along the coronal axis allows for the visualization of the cortex and medulla regions. (E) Isolation of the cortex tissue is best done by carving out pieces of the medulla tissue with a scalpel. The color of the cortical region is noticeably darker than that of the medullar region and can be used differentiate the two anatomically distinct tissues. Final processing of the cortex tissue involves (F) dicing the tissue into 0.5 cm3 pieces to aid in subsequent decellularization. Please click here to view a larger version of this figure.
Figure 2: Decellularization of cortex tissue. Visual and histological characterization of decellularized tissue. (A.1) Submerging diced cortex tissue in 1% SDS solution causes lysing of cells and removal of cellular material. After (A.2) 1 h and (A.3) 24 h, the tissue begins to lose color, indicating cellular matter is being removed. By (A.4) 120 h the tissue is blanched and only the ECM remains. Rinses with water at (A.5) 24 h and (A.6) 120 h show no visible changes to the tissue. (B) Immunofluorescence staining of untreated and decellularized cortex tissue reveals near complete removal of cellular matter and preservation of major structural proteins (collagen-IV = Col-IV; laminin = LAM; fibronectin = FN; heparin sulfate proteoglycans = HSPG; and vitronectin = VN). Scale = 100 µm. Please click here to view a larger version of this figure.
Figure 3: Mass spectroscopy of decellularized tissue. Analysis of decellularized cortex tissue by mass spectrometry to determine ECM protein composition. All ratios are measured as mass percent. (A) Structural and other proteins associated with the basal lamina were present with collagen-IV and -I being the most highly represented. (B.1) Collagen-IV A1 and A2 chains, ubiquitous in all basement membranes, were conserved. Collagen-IV A3 and A5 chains, present only in basement membranes of the glomerulus, were also detected. (B.2) Common isoforms of laminins and (B.3) collagen-I were also detected. This figure was reproduced with permission12. Please click here to view a larger version of this figure.
Figure 4: Fabrication of kECM hydrogel. Mechanical and chemical processing of decellularized cortex tissue yields a workable kECM hydrogel with sufficient mechanical properties following gelation with neutralizing reagents. (A) Decellularized cortex tissue is mechanically homogenized with a tissue homogenizer until no visible pieces of ECM remain. (B) A coarse powder was yielded after 3 days under lyophilization. (C) Solubilization in HCl and chemical digestion with pepsin in a scintillation vial resulted in a workable kECM hydrogel. The hydrogel was opaque and of a low viscosity. (D) Physical characterization of the kECM hydrogel following gelation with neutralizing reagents. Rheological experiments were performed with a 30 mm diameter parallel plate system. The sample edges were protected with mineral oil and the loading platform was set at 37 ˚C. The kECM hydrogel was allowed to gel for 1 h prior to testing. Viscoelastic properties of the gel were measured with a strain sweep between 0.01 to 20%. Three samples of both kECM and collagen-I were tested (n = 3). Please click here to view a larger version of this figure.
Figure 5: Cell growth characterization. Characterization of morphological differences in HKMECs grown on different matrices. Hydrogels were mixed with neutralizing reagents and set at 37 ˚C for 45 min in open-faced polydimethylsiloxane molds. HKMECs were seeded on the surface of the gels and kept in culture for 72 h before being fixed and stained. Immunofluorescent images of HKMECs cultured in (A and D) 7.5 mg/mL collagen-I gel; (B and E) 7.5 mg/mL kECM gel; and (C and F) 7.5 mg/mL 1:1 mixture gel. (A-C): red = CD31; green = VWF; blue = nuclei; scale bar = 50 µm. (D-F): red = F-actin; green = PV1; blue = nuclei; scale bar = 50 µm. This figure was reproduced with permission12. Please click here to view a larger version of this figure.
Matrices provide important mechanical and chemical cues that govern cell behavior. Synthetic hydrogels are able to support complex 3-dimensional patterning but fail to provide the diverse extracellular cues found in physiological matrix microenvironments. Hydrogels derived from native ECM are ideal materials for both in vivo and in vitro studies. Previous studies have used decellularized ECM hydrogels to coat synthetic biomaterials to prevent host immunological responses33,34, to differentiate stem cells35,36,37,38, as a substrate for 2D and soft lithography cell culture39,40,41,42, and in preparation of bioinks for 3-dimensional printing43,44,45,46. ECM hydrogels provide cells with proper signaling to initiate adhesion and control further proliferation and differentiation2,47.
The ratios and composition of major components of the ECM, such as collagens, laminins, elastin, fibronectin, and glycosaminoglycans, are highly dependent on the anatomical location and functionality of the tissue48,49,50. It is well established that using nonspecific or nonnative ECM-derived hydrogels will elicit improper responses from cells21,51,52,53,54. In the kidney, ECM composition varies widely between anatomical locations1,2. It is, therefore, important to differentiate between regions such as the cortex, medulla, or papilla before fabricating hydrogels for experimental use.
The kECM matrix fabricated here preserves native kidney cortex ECM protein ratios following decellularization while also enabling gelation to a physiologically relevant mechanical stiffness3,25,28,29,30. Serum albumin, a blood plasma protein, was detected in trace amounts within the decellularized cortex tissue, possibly due to binding to heparin that escaped decellularization and rinsing55,56. Although pepsin, a non-native chemical to kidney cortex ECM, is present in the stock kECM solution, it only accounts for 2.5% (w/v) of the final gelled product. Furthermore, pepsin becomes deactivated with the addition of the neutralizing reagent solution57.
The kECM hydrogel serves as a substrate upon which kidney cortex-specific cells can be maintained under physiological conditions. We demonstrated that this matrix can support HKMEC growth on a planar surface. These HKMECs maintained a quiescent physiological state as determined through functional assays, phenotypic expression, and genetic expression58. In contrast, these cells became activated when collagen-I, a matrix component correlated with kidney fibrosis, was added to the kECM hydrogel at a 1:1 ratio59. By comparison, when human umbilical vein endothelial cells were cultured on collagen-I, they were quiescent, and when mixed with kECM they became activated12. Accordingly, collagen-I is known to be an integral component of the basement membrane composition within the umbilical cord and is decreased under pathological states such as preeclampsia38,60. These results highlight the importance of providing cells with tissue-specific cues to maintain quiescence and also how manipulation of the ECM milieu can affect homeostasis.
Whereas all steps in the outlined procedure are important, several steps are critical in ensuring the viability of the fabricated hydrogel. The degree of homogenization of the decellularized cortex tissue will vary based on the technique or equipment used. It is important to find a technique that will best homogenize the tissue. During solubilization, the pH should be kept at 3-4 to ensure the pepsin is active. When mixing the hydrogel with neutralizing reagents, the gel must be mixed thoroughly and without the introduction of air bubbles. If a uniform mixture is difficult to obtain, check the pH of the gel solution to ensure it is neutral.
The representative results presented in this method demonstrate how a physiologically relevant matrix for the in vitro study of kidney cells can be achieved. Decellularized kidney cortex ECM provides an ideal base material to support kidney-derived cell growth as ECM protein ratios are conserved in the final hydrogel product3,25. The gelled product can also achieve physiologically relevant mechanical properties28,29,30. The kECM hydrogel allows for proper cell-matrix interactions and has been shown to elicit greater physiological behavior from kidney cells than collagen-I when cultured on a planar surface. Furthermore, the hydrogel can be seeded with kidney-specific cells prior to gelation to model a more physiologically relevant 3-dimensional environment. The composition of the kECM hydrogel can also be easily manipulated. For example, mixing the hydrogel with varying amounts of collagen-I prior to gelation could produce matrices that mimic progressive states of renal fibrosis31,32. The tunability of this ECM-derived hydrogel to mimic known diseased ECM compositions warrants further investigation and will enable the future study of kidney diseases.
The authors have nothing to disclose.
The authors would like to acknowledge the Lynn and Mike Garvey Imaging Laboratory at the Institute for Stem Cell and Regenerative Medicine and LifeCenter NorthWest. They would also like to acknowledge the financial support of National Institutes of Health grants, UH2/UH3 TR000504 (to J.H.) and DP2DK102258 (to Y.Z.), NIH T32 training grant DK0007467 (to R.J.N.), and an unrestricted gift from the Northwest Kidney Centers to the Kidney Research Institute.
Preparation of Kidney Tissue | |||
5000 mL Beaker | Sigma-Aldrich | Z740589 | |
Sodium Dodecyl Sulfate (SDS) | Sigma-Aldrich | 436143 | |
Sterile H2O | Autoclaved DI H2O | ||
Stir Bar (70 x 10 mm) | Fisher Science | 14-512-128 | |
500 mL Vacuum Filter | VWR | 97066-202 | |
Stir Plate | Sigma-Aldrich | CLS6795420D | |
1000 mL Beaker | Sigma-Aldrich | CLS10031L | |
Forceps | Sigma-Aldrich | F4642 | Any similar forceps may be used |
Scissor-Handle Hemostat Clamp | Sigma-Aldrich | Z168866 | |
Dissecting Scissors | Sigma-Aldrich | Z265977 | |
Scalpel Handle, No. 4 | VWR | 25859-000 | Any similar scalpel handle may be used |
Scalpel Blade, No. 20 | VWR | 25860-020 | Any similar scalpel blade may be used |
Stir Bar (38.1 x 9.5 mm) | Fisher Science | 14-513-52 | |
Absorbent Underpad | VWR | 82020-845 | |
Petri Dish (150 x 25 mm) | Corning | 430597 | |
Autoclavable Biohazard Bag | VWR | 14220-026 | |
Sterile Cell Strainer (40 um) | Fisher Science | 22-363-547 | |
Cell Culture Grade Water | HyClone | SH30529.03 | |
30 mL Freestanding Tube | VWR | 89012-778 | |
Fabrication of ECM Gel | |||
Tissue Homogenizer Machine | Polytron | PCU-20110 | |
Freeze Dryer | Labconco | 7670520 | |
20 mL Glass Scintillation Vials and Cap | Sigma-Aldrich | V7130 | |
Stir Bar (15.9 x 8 mm) | Fisher Science | 14-513-62 | |
Pepsin from Porcine Gastric Mucosa | Sigma-Aldrich | P7012 | |
0.01 N HCl | Sigma-Aldrich | 320331 | Dilute to 0.01 N HCl with cell culuture water |
Kidney ECM Gelation | |||
1 N NaOH (Sterile) | Sigma-Aldrich | 415413 | Dilute to 1 N in cell culture grade water |
Medium 199 | Sigma-Aldrich | M4530 | |
15 mL Conical Tube | ThermoFisher | 339651 | |
Cell Culture Media | ThermoFisher | 11330.032 | Dulbecco's Modified Eagle Medium: Nutrient Mixture F-12 (DMEM/F12) |
Fetal Bovine Serum (FBS) | Gibco | 10082147 | |
Antibiotic-Antimycotic 100X | Life Technologies | 15240-062 | |
Insulin, Transferrin, Selenium, Sodium Pyruvate Solution (ITS-A) 100X | Life Technologies | 51300-044 | |
1 mL Syringe | Sigma-Aldrich | Z192325 | |
Microspatula | Sigma-Aldrich | Z193208 |