This method enables decellularization of a complex solid organ using a simple protocol based on osmotic shock and perfusion of ionic detergent with minimal organ matrix disruption. It comprises a novel decellularization technique for human hearts inside a pressurized pouch with real-time monitoring of flow dynamics and cellular debris outflow.
The ultimate solution for patients with end-stage heart failure is organ transplant. But donor hearts are limited, immunosuppression is required, and ultimately rejection can occur. Creating a functional, autologous bio-artificial heart could solve these challenges. Biofabrication of a heart comprised of scaffold and cells is one option. A natural scaffold with tissue-specific composition as well as micro- and macro-architecture can be obtained by decellularizing hearts from humans or large animals such as pigs. Decellularization involves washing out cellular debris while preserving 3D extracellular matrix and vasculature and allowing "cellularization" at a later timepoint. Capitalizing on our novel finding that perfusion decellularization of complex organs is possible, we developed a more "physiological" method to decellularize non-transplantable human hearts by placing them inside a pressurized pouch, in an inverted orientation, under controlled pressure. The purpose of using a pressurized pouch is to create pressure gradients across the aortic valve to keep it closed and improve myocardial perfusion. Simultaneous assessment of flow dynamics and cellular debris removal during decellularization allowed us to monitor both fluid inflow and debris outflow, thereby generating a scaffold that can be used either for simple cardiac repair (e.g. as a patch or valve scaffold) or as a whole-organ scaffold.
Heart failure leads to high mortality in patients. The ultimate treatment option for end-stage heart failure is allo-transplantation. However, there is a long wait-list for transplantation due to the shortage of donor organs, and patients face post-transplantation hurdles that range from life-long immunosuppression to chronic organ rejection1,2. Bioengineering functional hearts by repopulating decellularized human-sized hearts with a patient's own cells could circumvent these hurdles3.
A major step in "engineering" a heart is the creation of a scaffold with appropriate vascular and parenchymal structure, composition and function to guide the alignment and organization of delivered cells. In the presence of the appropriate framework, cells seeded on the scaffold should recognize the environment and perform the expected function as part of that organ. In our opinion, decellularized organ extracellular matrix (dECM) comprises the necessary characteristics of the ideal scaffold.
By utilizing intrinsic vasculature, complex whole-organ decellularization can be achieved via antegrade or retrograde perfusion4 to remove cellular components while preserving the delicate 3D extracellular matrix and vasculature2,5,6,7. A functional vasculature is important in bioengineering whole organs just as it is in vivo, for nutrient distribution and waste removal8. Coronary perfusion decellularization has been proven to be effective in creating decellularized hearts from rats4, or pigs4,7,9,10,11,12,13, and humans5,7,14,15,16. Yet, integrity of the valves, atria and other "thin" regions can suffer.
Human-size decellularized heart scaffolds can be obtained from pigs using pressure control7,9,10,11,12 or infusion flow rate control13,17 and from human donors using pressure control5,7,14,15. Decellularization of human donor hearts occurs over 4-8 days under pressure controlled at 80-100 mmHg in upright orientation5,15,16 or over 16 days under pressure controlled at 60 mmHg14. Under antegrade, pressure-controlled decellularization, the aortic valve competency plays a crucial role in maintaining coronary perfusion efficiency and stable pressure at the aortic root. Our previous work revealed that the orientation of the heart influences its coronary perfusion efficiency during the decellularization procedure and therefore the scaffold integrity in the end9.
As a continuation of our previous work9, we introduce a novel concept wherein a pericardium-like pouch is added to improve whole-heart decellularization. We describe the decellularization of human hearts placed inside pressurized pouches, inversely oriented, and under pressure controlled at 120 mmHg at the aortic root. This protocol includes monitoring the flow profile and collection of outflow media throughout the decellularization procedure to evaluate coronary perfusion efficiency and cell debris removal. Biochemical assays are then performed to test the effectiveness of the method.
All experiments adhered to the ethics committee guidelines from the Texas Heart Institute.
1. Organ Preparation
NOTE: In collaboration with LifeGift, a nonprofit organ procurement organization in Texas (http://www.lifegift.org), donated human hearts not suitable for transplant were used for research with approved consent.
2. System Setup and Organ Decellularization Procedure
3. Evaluation of Decellularized Hearts
NOTE: After decellularization, representative hearts will be used for coronary angiogram imaging and biochemical assays.
After a 7-day decellularization with antegrade aortic perfusion under constant pressure of 120 mmHg, the human heart turned translucent (Figure 6B). The heart was grossly dissected into 19 sections for biochemical (DNA, GAG and SDS) analysis (Figure 6C) to evaluate the final decellularized product.
Throughout the decellularization process, infusion flow rate of different solutions varied as the pressure was kept constant. The flow rate into the Ao (Figure 7A) gradually decreased from 96.68±23.54 to 80.59±12.41 mL/min (16.64%) as the perfusion solution changed from hypertonic to hypotonic. In contrast, flow rate increased from 71.68±10.63 to 110.61±14.40 mL/min (54.31%) when perfusion solution changed from hypotonic to SDS. During the SDS perfusion, infusion flow rate fluctuated between 110±14.40 and 176.31±44.03 mL/min. The outflow rate from PA (Figure 7B) initially showed a similar trend (Figure 7A). However, the outflow rate during 1% SDS perfusion decreased from 35.77±9.07 to 27.08±4.09 mL/min. Coronary perfusion efficiency was used to evaluate aortic valve patency and similar trends. Efficiency decreased over time as different reagents perfused through the vasculature (Figure 7C). During the first hour of the 1X PBS wash, perfusion efficiency was restored to the original pre-hypotonic solution value (28.39±3.61% at 1-h PBS vs. 31.02±7.16% at 1-h hypotonic). The mean coronary perfusion efficiencies were 46.08±9.89%, 28.08±7.12%, 25.70±5.30%, and 28.39±3.61% with the hypertonic solution, the hypotonic solution, 1% SDS, and 1X PBS, respectively (Figure 7D).
Since the outflow perfusate from PA and LV were simultaneously collected, their debris content could be compared (Figure 8A) by spectroscopy absorbance measured at 280 nm (Figure 8B). The turbidity of the effluent from PA and LV decreased over time during perfusion of each solution; however, turbidity from the PA showed a more abrupt color change as compared to that observed from LV during the initial perfusion period. After switching from a hypertonic to a hypotonic solution, the turbidity of PA outflow changed from 1.15±0.03 to 1.40±0.07 (21.73% increase) and of LV changed from 1.13±0.05 to 1.24±0.07 (9.73% increase). During the first hour of 1% SDS perfusion, turbidity changed from 1.17±0.04 to 2.77±0.15 (136.75% increase) for PA and 1.11±0.04 to 1.75±0.26 (56.65% increase) for the LV effluent. The correlation between outflow turbidity and cell debris washout was evaluated using the bicinchoninic acid (BCA) protein assay when protein concentration was quantified in the outflow samples. The results obtained from the decellularization of 6 human hearts revealed a linear correlation between protein concentration and effluent turbidity with R2 = 0.95 (Figure 8C).
After completion of whole-heart decellularization, the coronary angiogram confirmed the preservation of intact coronary vasculature (Figure 9). Nonlinear optical imaging of myocardium layers from thick areas (i.e., RV, LV, and septum) in decellularized human heart confirmed cell removal, as no cell presence was observed in TPF channels (Figure 10). Cells (i.e., cardiomyocytes or cardiac fibroblasts) with their autofluorescence can be easily identified in TPF channel by their oval and elongated shape morphologies. To ensure effectiveness of the decellularization process and cellular debris removal, the decellularized human hearts were further grossed into 19 regions (Figure 6C) to quantify the levels of DNA, sulfated GAGs, and SDS remaining in those regions. DNA in all regions was less than 10% of cadaveric heart. DNA in right atrium (8.39%-10.38% relative to cadaveric) and left atrium (5.11%-7.60%) was highest (Figure 11A).
Figure 1: Cadaveric human heart from an organ procurement agency. Anterior and posterior views of cadaveric human heart. Inferior vena cava and a portion of right atrium are missing, as observed in dashed region. Please click here to view a larger version of this figure.
Figure 2: Inspection for septal and/or valve anatomical anomalies. (A) Inspect if patent foramen ovale (PFO) is present (communication between right and left atrium). (B) A 5-0 polypropylene suture is applied in a continuous fashion to close PFO. (C) Right atrium is closed with a running suture of 5-0 polypropylene. (D) The main pulmonary artery is dissected away from the ascending aorta by blunt dissection. FO: foramen ovale; PA: pulmonary artery; Ao: aorta. Please click here to view a larger version of this figure.
Figure 3: Components of the infusion bioreactor. The decellularization system is composed of (A) rubber cap with 4 ports; (B) outflow line to be connected to the pulmonary artery (PA); (C, F) connectors with luer lock for PA and aorta (Ao), (D) insertion line for the left ventricle (LV), (E) infusion line to be connected to the aorta, (G) polyester pouch, and (H) Perfusion container. Please click here to view a larger version of this figure.
Figure 4: Human heart cannulation and infusion bioreactor assembly. (A) Anterior view of the heart showing pulmonary artery (PA) and aorta (Ao) individually cannulated. (B) Posterior view of the heart showing cannula directed to left ventricle (LV) through pulmonary vein (PV). (C) Human heart inside the Infusion bioreactor after assembly. Please click here to view a larger version of this figure.
Figure 5: System setup of inverted oriented decellularization with pressure head. (A) The complete decellularization system is composed of: a computer, a proportional-integral-derivative (PID) controller, pumps, a bioreactor, and reservoirs for collecting the effluent from pulmonary artery (PA) and left ventricle (LV). Ao: aorta. Arrows indicate flow direction. (B) The schematic of the setup of human heart inside perfusion bioreactor and the associated flow paths of perfusate/effluent during decellularization. Please click here to view a larger version of this figure.
Figure 6: Schematic representation of the decellularization procedure and post-decellularization examination of a human heart. (A) Diagram of the decellularization procedure. (B) Anterior and posterior examination of a decellularized human heart. (C) Gross dissection of a human heart into four cross-sections (section A to section D) for biochemical assay analysis. The coloring in the human hearts is caused by residual lipofucin deposition. The coloring normally presents in inner ventricular surface or the boundary between epicardium and myocardium. LA: left atrium; RA: right atrium; LV: left ventricle; RV: right ventricle; Ant: anterior; Post: posterior; Hyper: hypertonic; Hypo: hypotonic; SDS: sodium dodecyl sulfate; PBS: phosphate buffered saline. Please click here to view a larger version of this figure.
Figure 7: Time-lapse flow dynamics during decellularization. (A) Infusion flow rate of decellularization solutions into aorta during procedure. (B) Flow rate of effluent from PA during decellularization. (C) Coronary perfusion efficiency during decellularization. (D) Mean coronary perfusion efficiency during perfusion of different solutions/reagents. N = 6. Data represent mean±SEM. PA: pulmonary artery; Hyper: hypertonic; Hypo: hypotonic; SDS: sodium dodecyl sulfate; PBS: phosphate buffered saline; SEM: standard error of mean. Please click here to view a larger version of this figure.
Figure 8: Time-lapse cell debris washout during decellularization. (A) Outflow media collection from PA and non-PA (Left ventricle). (B) Result of turbidity measurement at 280 nm. (C) Linear correlation exists between protein concentration and turbidity. n = 6 human hearts. Control was clean decellularization solution. Data represent mean±SEM. PA: pulmonary artery; Hyper: hypertonic; Hypo: hypotonic; SDS: sodium dodecyl sulfate; SEM: standard error of mean. Please click here to view a larger version of this figure.
Figure 9: Coronary angiogram of decellularized human heart confirms thevascular patency after decellularization. Please click here to view a larger version of this figure.
Figure 10: Images obtained using nonlinear optical microscopy from cadaveric and decellularized myocardium show no presense of cells (i.e., cardiomyocytes or cardiac fibroblasts) with oval or elongated shape morphologies in the decellularized LV, RV and septum. LV: left ventricle; RV: right ventricle; TPF: two photon fluorescence; SHG: second harmonic generation. Some cardiac cells are indicated by arrows. Please click here to view a larger version of this figure.
Figure 11: Biochemical assay results. (A) Remaining DNA relative to cadaveric heart in decellularized tissues. (B) Remaining GAG relative to cadaveric heart in decellularized tissues. (C) Remaining SDS in decellularized tissues. n = 6 human hearts. Data represent mean±SEM. LA: left atrium; RA: right atrium; LV: left ventricle; RV: right ventricle; Ant: anterior; Post: posterior; SDS: sodium dodecyl sulfate; SEM: standard error of mean. Please click here to view a larger version of this figure.
Method | Pro | Con |
Conventional upright Langendorff perfusion | · Easy to access the heart to repair during decellularization | · Excessive strain on the aorta owing to heart weight |
· High infusion flow rate during SDS perfusion under constant pressure control | ||
· Low coronary perfusion efficiency during SDS perfusion | ||
· The portion of aorta/pulmonary artery above cannula ligation line could get dehydrated and easily contaminated | ||
Inverted Langendorff perfusion inside a pressurized pouch | · Minimize strain exerted on the aorta owing to heart weight | · Hard to access the heart if repairing is needed. |
· Low infusion flow rate during SDS perfusion under constant pressure control | ||
· Improved coronary perfusion efficiency during SDS perfusion | ||
· No tissues will be dried out since the whole heart is submerged/hydrated. |
Table 1: A summary of pros and cons of whole-heart decellularization using conventional upright perfusion vs. inverted Langendorff perfusion inside a pressurized pouch.
To our knowledge, this is the first study to report inverted decellularization of human hearts inside a pressurized pouch with time-lapse monitoring of flow rate and cell debris removal. The pericardium-like pouch keeps the orientation of the heart stable throughout the decellularization procedure. Submerging and inverting the whole hearts inside a pouch prevents dehydration and minimizes excessive strain on the aorta (from heart weight) when compared to the conventional upright Langendorff perfusion decellularization method9. This, in turn, preserves the competency of the aortic valve.
To achieve maximal decellularization efficiency, coronary vascular resistance must be low to ensure adequate and consistent perfusion of fluid through the entire myocardium. In the whole-heart decellularization model using retrograde perfusion, fluid accumulates in the ventricles and elevates intraventricular pressure, which, in turn, increases coronary vascular resistance and limits the flow of fluids. Even though the aortic valve is intact, the ventricular cavity fills secondary to physiological leakage and in turn compresses the ventricular wall.
Our technique of decellularizing a heart inside a pressurized pouch is aimed to alleviate this problem and increase decellularization efficiency. A pressure of 120 mmHg at the aortic root and 14 mmHg in the pouch is maintained throughout the decellularization process. These pressure values are very close to physiological range (80-120 mmHg in aorta and 15 mmHg for Left ventricular end-diastolic pressure22). According to Murthy et al.23, the myocardial blood flow rate ranges from 0.61 to 1.10 mL/min/g, and the human heart weight24,25 is about 245 to 308 g; hence, the physiological coronary flow rate is about 149.45 to 338.80 mL/min, but depends on heart weight. Our outflow rate from PA ranged from 20 to 50 mL/min, which is less than the value of physiological coronary flow rate and could have resulted from 2 different situations: 1) the infusion of solutions to the heart produce edema and there is also normal anatomical drainage of the coronary system to the left ventricle cavity; 2) as the decellularization occurs, liquid is also lost through the decellularized walls due to a natural increase in their permeability. This pressure differential prevents collapse of the vessels and allows them to remain patent. Moreover, this system maintains the heart in relative anatomic conditions without compressing the myocardial wall, which would increase coronary vascular resistance and impair the intravascular circulation of the decellularization solutions. The infusion flow rate profile of human hearts (Figure 7A) is very similar to what we observed in our inverted decellularization of porcine heart9, with lowest infusion flow rate occurring during the hypotonic perfusion and a slight increase in flow rate (110.61±14.40 mL/min to 176.31±44.03 mL/min) occurring during 1% SDS perfusion. Our infusion flow rate (mean value=151.50±3.71 mL/min) during 1% SDS perfusion was comparable to, or even less than that for human heart decellularization reported by Guyette et al.14 However, our method is performed with pressure control of 120 mmHg and their method used 60 mmHg. This difference in perfusion pressures suggests a superior effectiveness of aortic valve closure in our technique since a lower infusion flow rate could maintain higher pressure. Another possibility is that the increased coronary resistance was due to the applied 14 mmHg pressure inside the pouch. Additionally, our human heart method showed a similar trend of decreasing coronary perfusion efficiency (~30%, Figure 7C, 7D) from hyper to hypotonic solution change when compared to our inverted porcine heart decellularization (~10% in inverted orientation9 vs. 1-2% in upright orientation). However, this novel method could preserve coronary perfusion efficiency during SDS perfusion comparable to solution perfusion and thus appears superior to our prior method of sample inversion. Table 1 lists the pros and cons of conventional upright perfusion vs. inverted Langendorff perfusion inside a pressurized pouch.
In addition to flow rate, outflow turbidity monitoring could be another useful tool to evaluate decellularization progress and efficiency. During decellularization, turbidity of the effluent from the PA was higher than that of the effluent from non-PA sites (Figure 8B). This suggests that most of the perfused solution was going through the vasculature for "proper" decellularization. Yet for this to be valid, the following must be addressed: inter-chamber shunts, or patency of the aortic valve. Careful and meticulous inspection is therefore needed to prevent failure of the method due to anatomical non-conformities. The turbidity profile (Figure 8B) of the whole heart decellularization process demonstrated similar trends as previously shown, with abrupt turbidity change during the initial transition period of different perfusates9.
A main goal for decellularized tissues is to be able to repopulate them with cells and achieve high cell attachment, proliferation, maturation and functionality. Our decellularized tissues have been successfully cellularized for various applications26,27, where the tissues were successfully cellularized and achieved lower thrombogenicity. In our biochemical analyses of decellularized human hearts, we evaluated 19 regions with different tissue thicknesses. The DNA and SDS in decellularized tissues varied, with the highest value obtained in the right and left atrium. This could be caused by the orientation of the heart in an upside-down configuration, wherein cell debris was trapped at the bottom of the pouch or where external pressure reduced flow. Perfusion decellularization relies on undamaged heart structures, including intact coronaries and tributaries. As these organs are procured from multi-organ donors, these hearts usually have a large portion of their atria removed. During the preparation of these organs and repair of the atrial wall, there was disruption in the irrigation of these regions, jeopardizing the flow of the decellularization solutions. For non-perfusion heart decellularization, other research groups have reported 2-6% leftover DNA in rat28, porcine29,30 and human31 as compared with respective cadaveric heart. However, they used freeze-thaw28,29,30, enzyme29,30 and serum31 in their decellularization protocol, which may damage the ECM to a greater degree than our perfusion-based technique. Developing methods to adequately address these limitations will be critical.
The authors have nothing to disclose.
This research was supported by the Houston Endowment grant and the Texas Emerging Technology Fund. The authors acknowledge the organ procurement agency LifeGift, Inc. and the donor's families for making this study possible.
2-0 silk suture | Ethicon | SA85H | Suture used to ligate superior and inferior vena cava |
1/4" x 3/8" connector with luer | NovoSci | 332023-000 | Connect aorta and pulmonary artery |
Masterflex platinum-cured silicone tubing | Cole-Parmer | HV-96410-16 | Tubing to connect heart chambers/veins |
infusion and outflow line | Smiths Medical | MX452FL | For flowing solutions through the vasculature |
Polyester pouch (Ampak 400 Series SealPAK Pouches) | Fisher scientific | 01-812-17 | Pericardium-like pouch for containing heart during decellularization |
Snapware Square-Grip Canister | Snapware | 1022 | 1-liter Container used for perfusing heart |
Black rubber stoppers | VWR | 59586-162 | To seal the perfusion container |
Peristaltic pump | Harvard Apparatus | 881003 | To pump fluid through the inflow lines and to drain fluids |
2 L aspirator bottle with bottom sidearm | VWR | 89001-532 | For holding solutions/perfusate |
Quant-iT PicoGreen dsDNA Assay kit | Life Technologies | P7589 | For quantifying dsDNA |
Calf thymus standard | Sigma | D4522 | DNA standard |
Blyscan Glycosaminoglycan Assay Kit | Biocolor Ltd | Blyscan #B1000 | GAG assay kit |
Plate reader | Tecan | Infinite M200 Pro | For analytical assays |
GE fluoroscopy | General Electric | OEC 9900 Elite | Angiogram |
Visipaque | GE | 13233575 | Contrast agent |