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Cancer Research

Establishing a Physiologic Human Vascularized Micro-Tumor Model for Cancer Research

Published: September 15, 2023 doi: 10.3791/65865

Summary

This protocol presents a physiologically relevant tumor-on-a-chip model to perform high-throughput basic and translational human cancer research, advancing drug screening, disease modeling, and personalized medicine approaches with a description of loading, maintenance, and evaluation procedures.

Abstract

A lack of validated cancer models that recapitulate the tumor microenvironment of solid cancers in vitro remains a significant bottleneck for preclinical cancer research and therapeutic development. To overcome this problem, we have developed the vascularized microtumor (VMT), or tumor chip, a microphysiological system that realistically models the complex human tumor microenvironment. The VMT forms de novo within a microfluidic platform by co-culture of multiple human cell types under dynamic, physiological flow conditions. This tissue-engineered micro-tumor construct incorporates a living perfused vascular network that supports the growing tumor mass just as newly formed vessels do in vivo. Importantly, drugs and immune cells must cross the endothelial layer to reach the tumor, modeling in vivo physiological barriers to therapeutic delivery and efficacy. Since the VMT platform is optically transparent, high-resolution imaging of dynamic processes such as immune cell extravasation and metastasis can be achieved with direct visualization of fluorescently labeled cells within the tissue. Further, the VMT retains in vivo tumor heterogeneity, gene expression signatures, and drug responses. Virtually any tumor type can be adapted to the platform, and primary cells from fresh surgical tissues grow and respond to drug treatment in the VMT, paving the way toward truly personalized medicine. Here, the methods for establishing the VMT and utilizing it for oncology research are outlined. This innovative approach opens new possibilities for studying tumors and drug responses, providing researchers with a powerful tool to advance cancer research.

Introduction

Cancer remains a major health concern worldwide and is the second leading cause of death in the United States. For the year 2023 alone, the National Center for Health Statistics anticipates more than 1.9 million new cancer cases and over 600,000 cancer deaths occurring in the US1, highlighting the urgent need for effective treatment approaches. However, currently, only 5.1% of anti-cancer therapeutics entering clinical trials ultimately gain FDA approval. Failure of promising candidates to successfully progress through clinical trials can be partially attributed to the use of non-physiological model systems, such as 2D and spheroid cultures, during preclinical drug development2. These classical cancer models lack essential components of the tumor microenvironment, such as a stromal niche, associated immune cells, and perfused vasculature, which are key determinants of therapeutic resistance and disease progression. Thus, a new model system that better mimics the human in vivo tumor microenvironment is necessary to improve the clinical translation of preclinical findings.

The field of tissue engineering is rapidly advancing, providing improved methods for studying human diseases in laboratory settings. One significant development is the emergence of microphysiological systems (MPS), also known as organ chips or tissue chips, which are functional, miniaturized human organs capable of replicating healthy or diseased conditions3,4,5. Within this context, tumor chips, which are three-dimensional microfluidic-based in vitro human tumor models, have been developed for oncology research2,3,4,5,6,7,8,9,10,11,12,13. These advanced models incorporate biochemical and biophysical cues within a dynamic tumor microenvironment, enabling researchers to study tumor behavior and responses to treatments in a more physiologically relevant context. However, despite these advancements, few groups have successfully incorporated a living, functional vasculature, particularly one that self-patterns in response to physiologic flow3,4,5,6. The inclusion of a functional vascular network is crucial as it allows for modeling physical barriers that affect drug or cell delivery, cell homing to distinct microenvironments, and transendothelial migration of tumor, stromal, and immune cells. By including this feature, the tumor chip can better represent the complexities observed in the in vivo tumor microenvironment.

To address this unmet need, we have developed a novel drug-screening platform that enables micro-vessel networks to form within a microfluidic device8,9,10,11,12,13,14,15,16. This base organ chip platform, termed the vascularized micro-organ (VMO), can be adapted to virtually any organ system to replicate original tissue physiology for disease modeling, drug screening, and personalized medicine applications. VMOs are established by co-culturing endothelial colony-forming cell-derived endothelial cells (ECFC-EC), HUVEC or iPSC-EC (hereafter EC), and multiple stromal cells in the chamber, including normal human lung fibroblasts (NHLF), which remodel the matrix, and pericytes that wrap and stabilize the vessels. The VMO can also be established as a cancer model system by co-culturing tumor cells with the associated stroma to create a vascularized micro-tumor (VMT)8,9,10,11,12,13, or tumor chip, model. Through the co-culture of multiple cell types in a dynamic flow environment, perfused microvascular networks form de novo in the tissue chambers of the device, where vasculogenesis is closely regulated by interstitial flow rates14,15. Medium is driven through the microfluidic channels of the device by a hydrostatic pressure head that supplies the surrounding cells of the tissue chamber with nutrients exclusively through the micro-vessels, with a permeability coefficient of 1.2 x 10-7 cm/s, similar to what is seen for capillaries in vivo8.

The incorporation of self-organizing micro-vessels into the VMT model represents a significant breakthrough because it: 1) mimics the structure and function of vascularized tumor masses in vivo; 2) can model key steps of metastasis, including tumor-endothelial and stromal cell interactions; 3) establishes physiologically selective barriers for nutrient and drug delivery, improving pharmaceutical screening; and 4) allows direct assessment of drugs with anti-angiogenic and anti-metastatic capabilities. By replicating the in vivo delivery of nutrients, drugs, and immune cells in a complex 3D microenvironment, the VMO/VMT platform is a physiologically relevant model that can be used to perform drug screening and study cancer, vascular or organ-specific biology. Importantly, the VMT supports the growth of various types of tumors, including colon cancer, melanoma, breast cancer, glioblastoma, lung cancer, peritoneal carcinomatosis, ovarian cancer, and pancreatic cancer8,9,10,11,12,13. In addition to being low-cost, easily established, and arrayed for high throughput experiments, the microfluidic platform is fully optically compatible for real-time image analysis of tumor-stromal interactions and response to stimuli or therapeutics. Each cell type in the system is labeled with a different fluorescent marker to allow direct visualization and tracking of cell behavior throughout the entire experiment, creating a window into the dynamic tumor microenvironment. We have previously shown that the VMT more faithfully models in vivo tumor growth, architecture, heterogeneity, gene expression signatures, and drug responses than standard culture modalities10. Importantly, the VMT supports the growth and study of patient-derived cells, including cancer cells, which better models the pathology of the parent tumors than standard spheroid cultures and further advances personalized medicine efforts11. This manuscript outlines the methods for establishing the VMT, showcasing its utility for studying human cancers.

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Protocol

1. Design and fabrication

  1. Device design
    1. For microfluidic device fabrication, create an SU-8 mold using a 200 µm layer of SU-8 spin-coated onto a Si-wafer (RCA-1 cleaned and 2% hydrogen fluoride (HF) treated), followed by a single mask photolithography step as described previously8,9.
    2. Cast a 4 mm thick polydimethylsiloxane (PDMS) replica from the SU-8 mold to generate a durable polyurethane mold for downstream fabrication steps. Various design iterations can be used8,9,10,11,12,13,14,15.
    3. In the current iteration, design the microfluidic device to be custom-fitted into a standard 96-well plate format and consisting of a 2 mm thick PDMS feature layer with 12 microfluidic device units enclosed by a thin (1/16 inch) transparent polymer membrane layer on the bottom (Figure 1A).
    4. Ensure that individual tissue units consist of a tissue chamber flanked by gel loading inlet (L1) and outlet (L2), a pressure regulator (PR)16, and decoupled microfluidic channels connected to 2 media inlets and outlets on each side (M1-M2, M3-M4; Figure 1B).
    5. Position each inlet and outlet within a single well that serves as a medium reservoir to establish hydrostatic pressure (10 mm H2O) across the microfluidic channel. To allow vascular network anastomoses with the outer channels, connect microfluidic channels to the tissue chamber via 50 µm wide communication pores (6 on top, 6 on bottom).
      NOTE: Microfluidic resistors create a 5 mm H2O interstitial pressure gradient across the tissue chamber that becomes intraluminal once the vascular network is fully formed8,10. The subsequent procedures begin with a fully assembled high throughput plate.

Figure 1
Figure 1. Microfluidic platform design. (A) The schematic of the platform assembly shows the PDMS feature layer with 12 device units bonded to a bottomless 96-well plate and sealed with a thin transparent polymer membrane. Each device unit occupies a column of wells on the plate. The single device unit outlined in red is shown with details in (B). (B) Schematic of one device unit shows a single tissue chamber positioned within one well of the 96-well plate and two loading ports with inlet and outlet (L1-L2) hole punched to allow cell-matrix mix to be introduced. Medium inlets and outlets (M1-M2, M3-M4) are hole-punched and positioned within wells that serve as media reservoirs. Different volumes of media establish a hydrostatic pressure gradient across the tissue chamber via decoupled microfluidic channels. The pressure regulator (PR) unit serves as a gel burst valve to increase ease of loading. Note that the device is 200 µm deep, and the tissue chamber is 2 mm x 6 mm. Please click here to view a larger version of this figure.

2. Preparations prior to loading

  1. Cell culture
    1. Maintain cells according to the manufacturer's recommendations in a humidified 37 °C and 5% CO2 incubator.
    2. Plate T75 flasks of transduced EC, NHLF, or other fibroblast/stromal cell and desired cancer cells 3-4 days prior to loading at a density informed by manufacturer and user protocols. For this protocol, plate 1 x 106 cells per flask for each cell type. Culture EC in Endothelial Growth Media 2 (EGM2) complete media, NHLF in Dulbecco's Modified Eagle Medium (DMEM) with 10% FBS, and cancer cells in appropriate media depending on cell type.
    3. Maintain cells by feeding with the respective media every 2-3 days and reconfirm the transduction or labeling efficiency by visualizing cells under a fluorescent microscope. On the day of loading, ensure EC is 80%-100% confluent, whereas NHLF is subconfluent at 70%-80%.
  2. Preparation of fibrinogen
    1. Prepare the fibrinogen solution to the desired concentration (typically, 5-8 mg/mL supports robust vascular network formation), accounting for the percent clotting of fibrinogen. Calculate the amount of fibrinogen needed with the following equation:
      Fibrinogen (mg) = (volume (mL)) x (concentration (mg/mL))/ (clotting %)
    2. Dissolve the fibrinogen in an appropriate volume of endothelial basal media 2 (EBM2), warmed to 37 °C, by gently flicking the tube (do not vortex). Incubate fibrinogen in a 37 °C water bath to allow it to completely go into solution. Importantly, do not use a complete medium.
    3. Sterile-filter fibrinogen solution with 0.22 µm filter and aliquot to desired volume, typically 400 µL per microcentrifuge tube.
      ​NOTE: Other matrix proteins (e.g., collagens, fibronectin, or laminin) can be spiked into the fibrinogen mix.

3. Loading of samples

NOTE: Loading is time-sensitive and should be completed from start (cell lifting) to finish (addition of media to devices) within about 1.5-1.75 h to ensure optimal results. Each step is noted with a suggested timer to help keep the user on track.

  1. Preparation of materials (Day of loading)
    1. Place the following in a 37 °C water bath for 10-15 min: Hank's balanced salt solution (HBSS) or phosphate-buffered saline (PBS) for washing cells, cell dissociation reagent, media (e.g., EGM2, DMEM)
    2. Keep the following reagents in a 4 °C fridge until ready for use: thrombin, laminin (thawed overnight at 4 °C).
    3. Thaw fibrinogen aliquot at room temperature. Prepare 1.5 µL aliquots of thrombin into 500 µL microcentrifuge tubes, with one tube per device unit. Ensure that the thrombin aliquot is at the bottom of each tube to facilitate loading.
    4. Place UV-sterilized high throughput plates into a desiccator for at least 30 min prior to loading to remove air trapped in the microfluidics.
  2. Cell preparation (Timer start = begin at 0 min)
    1. Check cells under the microscope at 4x magnification to confirm confluency and transduction efficiency.
    2. Wash each T75 flask of cells 2x with 5 mL of HBSS and aspirate completely. Add 1 mL of dissociation reagent to each flask and incubate at 37 °C, 5% CO2 for 1-2 min.
    3. Gently tap the plate using the palm of your hand and check that all cells have been lifted.
    4. Wash the cells off the flask with 9 mL of appropriate media and collect them into a 15 mL conical. Immediately remove a small aliquot for cell counting.
    5. Centrifuge the cells at 300 x g for 3-5 min at 4 °C. While centrifuging cells, count the cells. A confluent T75 flask of EC or NHLF should yield at least 2 x 106 cells.
    6. After centrifugation, aspirate media and resuspend the pellet in appropriate media at a concentration of 1 x 106 cells/mL. Keep cells on ice.
  3. Preparation of cell and fibrinogen mixture (Timer = begin at 20 min)
    1. Determine how many devices will be loaded, adding 1-2 to account for pipetting loss, and multiply by the volume of cell/fibrinogen mix needed per device. This will depend on device configuration, but for the device design presented in this article, 6 µL per device is required.
    2. The concentration of each cell type should be determined experimentally. For a starting point, load EC at a concentration of approximately 7 x 106 cells/mL and NHLF at a concentration of 3.5 x 106 cells/mL. The concentration of cancer cells can vary considerably based on their growth rate but typically lies within the range of 0.5-2 x 106 cells/mL. Use this equation to calculate the number of cells needed:
      Number of cells needed = (volume of fibrin (µL))/1000 µL x (concentration of cells)
    3. Resuspend the cells at a concentration of 1 x 106 cells/mL and use the following equation to determine the volume of cells needed:
      Volume of cells needed (µL) = (number of cells needed)/1000
    4. Mix respective volumes of EC, NHLF, and cancer cells (for VMT only) in a conical tube and centrifuge at 300 x g for 3-5 min at 4 °C.
    5. After spinning, carefully aspirate media and pipet away any residual media near the pellet. Gently but thoroughly resuspend the pellet into the calculated volume of fibrinogen, taking extra care not to introduce air bubbles. Keep on ice.
    6. Bring sterilized plates and thrombin aliquots into the tissue culture hood.
  4. Loading devices (Timer = begin at 30-35 min)
    1. Using a P20 pipette, pipet 6 µL of volume from the cell/fibrin mix. Be sure to pipet the mixture up and down at least 5x to ensure uniform cell suspension. Keep the mix on ice to slow clotting.
    2. Gently mix the cell/fibrin into one tube of thrombin by putting the pipet tip directly into the thrombin aliquot at the bottom of the tube. Immediately pipet up and down at least 2x, taking care not to introduce air bubbles. The fibrin will begin to clot once mixed with thrombin, so quickly but deliberately complete steps 3.4.3. and 3.4.4. before the fibrin gels in the pipette tip (~3 s).
    3. Lift the high throughput plate at an angle and quickly insert the pipet tip into one of the device loading ports (L1 or L2). See Figure 2A for schematic.
    4. Push the pipet plunger down to the first stop with a smooth, fluid motion to inject the cell/fibrin mix into the tissue chamber. Watch for the gel to cross completely through the chamber.
      NOTE: Applying too much pressure during this step can lead to bursting of the gel into the microfluidic channels at the top and/or bottom of the tissue chambers.
    5. Gently place the plate back down flat in the tissue culture hood without removing the pipette tip, releasing the pipette plunger, or disturbing the pipette. Use your hand to twist and remove the pipette tip from the P20 and leave it in the loading port hole. Do not use the ejector button to remove the tip as this will cause too much pressure.
    6. Proceed with steps 3.4.1-3.4.5 for the remaining devices.
    7. When loading is complete, allow the plate to sit for 2 min undisturbed in the tissue culture hood.
    8. Remove pipette tips by gently twisting and pulling them from the loading ports. Replace the lid on the plate.
    9. Incubate the entire plate for 15-20 min in a 37 °C incubator to allow the gel to fully polymerize.
    10. After incubating, check each device unit under the microscope. Check to see that cells are evenly distributed throughout the chamber without any air bubbles and that there is a clearly visible gel interface between the tissue chamber and the microfluidic channels, as in Figure 2B-C.
  5. Channel coating with laminin (Timer = begin at 45-50 min)
    1. After the gels are completely solid, introduce laminin into the microfluidic channels to promote vascular anastomosis.
    2. Using a P20, introduce 4 µL of laminin into each microfluidic channel (top and bottom) of the device. Insert the pipet tip into M1 or M3 and expel the laminin slowly, watching to ensure that the laminin coats the entire top channel, and then repeat for M2 or M4 to coat the entire bottom channel.
    3. Determine the orientation by pipetting laminin from the side opposite to the pressure regulator to allow sufficient pressure to push it through. However, if laminin does not travel easily from one side, remove the tip from one side and push the laminin from the other side. Going to the second stop of the pipette (i.e., push the plunger all the way down) may be needed to generate sufficient pressure to push the laminin through the entire channel.
    4. Remove the tip gently from the media inlet/outlet. Do not use the ejector button on the P20.
    5. Repeat steps 3.5.1-3.5.4 for each device and incubate the plate at 37 °C, 5% CO2 for 10 min.
  6. Media addition (Timer = begin at approximately 1 h 10 min)
    1. Add 275 µL of EGM2 complete media into the uncoupled media reservoirs of wells in rows A and B or G and H. This will be the high side, and the orientation should be determined by making the wells on the side opposite to the pressure regulator high volume to start. Media will be pushed from the high side by gravity.
    2. Using a P200 pipette, introduce 75 µL of media into the medium inlets/outlets of the wells containing the 275 µL of EGM2. Insert the tip into the media inlet hole and slowly expel the medium, watching that the media travels through the channel and bubbles up on the other side.
    3. Remove the pipet tip and push the remaining media from the tip into the media reservoir so that the total volume on the high side is 350 µL.
    4. Repeat steps 3.6.1-3.6.3 for each device unit, top and bottom channels.
    5. Add 50 µL of media to completely cover the low side, wells in rows A and B or G and H, depending on the orientation described above. Ensure that there is an even layer of media covering the bottom of the well. Refer to Figure 2D for a schematic showing volumes of media in the reservoirs.
  7. Removing air bubbles (post-loading)
    NOTE: Removing bubbles is a critical step to ensure proper flow in each device. By day 2, endothelial cells and fibroblasts will begin to stretch out in response to flow (Figure 2E).
    1. Once all media is added, incubate plates for 1-2 h in a 37 °C, 5% CO2 incubator before checking for air bubbles in the channels or at the medium inlets/outlets.
    2. Visualize bubbles in the media channels on the microscope and expel by reintroducing 75 µL of media into the channels to push the bubbles out.
    3. Visualize bubbles in the medium inlets/outlets by eye. Use a P200 pipette to remove air bubbles trapped at the medium inlets and outlets by pushing the plunger down, introducing the tip into the hole, and pulling the bubble out by lifting the plunger to apply negative pressure and suck up the bubble.

Figure 2
Figure 2. Schematic of device loading. (A) Using a P20 pipette, cell/fibrin mix is introduced into the tissue chamber of each device unit via one of the loading ports. (B) Brightfield micrograph shows a microfluidic device loaded EC, fibroblasts, and cancer cells to form a VMT. Scale bar = 500 µm. (C) Fluorescence micrograph of the device in B showing EC in red, tumor in cyan, and fibroblasts in blue. (D) The schematic shows the addition of medium into the reservoirs, with 350 µL on the high side and 50 µL on the low side to generate the hydrostatic pressure head. (E) Day 2 of VMT culture shows fibroblasts and EC beginning to stretch out to form the vascular network. Scale bar = 200 µm. Please click here to view a larger version of this figure.

4. Device maintenance and experimental applications

  1. Maintenance and drug treatment
    NOTE: To maintain flow in the system, hydrostatic pressure must be re-established daily by pipetting the volume of media from the low side back to the high side or vice versa, ensuring the total volume in the high side remains at 350 µL. Flow direction is switched every day after day 2 of VMO or VMT establishment. Additional maintenance and treatment details are provided below.
    1. Change media every other day with EGM2 complete until the vasculature is fully established (day 5-6). Aspirate old media completely and replace high-pressure wells (350 µL) and low-pressure wells (50 µL).
      NOTE: Experimental determination of optimized media formulations can be conducted for other cell types, often involving a 50:50 mix or addition of specific components into EGM2.
    2. Once the vascular network is formed and tissue is fully developed (day 4-7), perform a dextran perfusion test before using the devices for experiments (step 4.2.1.). Only use devices that have sufficient perfusion into the tissue chamber.
    3. For experiments using therapeutics, on the day treatment begins, take images in all fluorescent channels for each device. This will serve as a baseline.
    4. Treat devices with desired therapeutic by replacing the medium with fresh medium containing the diluted drug at the desired concentration. Ensure drugs are diluted in appropriate vehicles depending on manufacturer's recommendation, but do not exceed 0.01% DMSO in the media.
    5. Expose devices to the drug for the desired amount of time (typically 48 h but can be informed by pharmacokinetics).
    6. Image every channel of each device at the desired time interval to monitor treatment response. Maintain plates as indicated in step 4.1.1 for the duration of the experiment.
    7. At completion of experiment, bleach plates and place in a biohazard container, fix with 4% PFA for immunofluorescent staining (step 4.3.), or harvest for live cell or RNA isolation (step 4.4.).
  2. Perfusion assays
    1. Perfusion of dextran
      NOTE: Vascular permeability/patency can be determined by perfusing the vascular network with fluorescently labeled dextran of varying molecular weights (40 kD, 70 kD, or 150 kD). FITC- or rhodamine-dextran can be used depending on the fluorescent label of the EC.
      1. Prior to perfusion, determine the appropriate exposure of the FITC or rhodamine channel by adding a few µL of dextran within the fluidic channel or chamber of an empty device. Set exposure time just below the saturation level through the use of microscope software to display a histogram of pixel intensities, ensuring a dynamic range characterized by uniformly distributed pixels without any notable concentration of high-intensity values.
      2. Take micrographs of all devices in channels of interest, including a background image of all devices in the fluorescent dextran channel, to calibrate against the background. Use the same exposure as determined above and align the tissue chamber at the center of the image frame to ensure consistent images for quantification.
      3. Prepare a main stock of FITC-dextran or rhodamine-dextran at a concentration of 5 mg/mL in 1x DPBS. This stock can be kept at 4 °C.
      4. To prepare a working stock, dilute 5 mg/mL stock to a final concentration of 50 µg/mL in EGM2.
      5. Replace the media in the reservoirs with the diluted dextran solution as half maximal volume (175 µL into one well as the high side on the top or bottom channel of the tissue chamber). Replace the media in the other wells so that the uncoupled high side gets 175 µL of fresh EGM2 without dextran, and the wells on the low side only have 50 µL in each.
        NOTE: Dextran should only be added to one side of the microfluidic channels (top or bottom) to allow visualization of dye traveling through the high-pressure side, into the vascular bed, and out the low-pressure side.
      6. Under the microscope, watch for the fluorescent dextran to flow through the vascular network. This typically will occur within approximately 2 min after adding the dye to the media reservoir.
      7. Begin imaging the fluorescent dextran channel (and other channels, if desired). This is T = 0 timepoint. Take additional images at multiple time points (typically every 10 min) or a single end-point image.
    2. Perfusion of cells
      NOTE: Various cell types can be perfused through the vasculature depending on the study design, including lymphocytes or macrophages for cancer immunology studies, as well as cancer cells for metastasis studies. Cells must be fluorescently labeled to facilitate tracking over time.
      1. At least 2 h before perfusing cells, perform dextran perfusion on all devices as outlined above. This step is important to determine vascular patency prior to adding cells.
      2. Determine the appropriate camera exposure for the cells to be perfused. Take a small sample of cells to view under the microscope and set the exposure time for that fluorescent marker. Set exposure time just below the saturation level.
      3. Take micrographs of all devices in channels of interest, including a background image of all devices in the fluorescent dextran channel, to calibrate against the background. Use the same exposure as determined in step 4.2.2.1.
      4. Confirm that dextran has diffused completely out of the tissue chambers before harvesting the cells for perfusion. Harvest and count the cells of interest.
      5. Resuspend cells at appropriate density into EGM2. For example, T cells are typically added at approximately 1 x 106 cells/mL to mimic the concentration in blood.
        NOTE: EC are sensitive to media composition but can tolerate up to 50% mix with most other media. Test beforehand.
      6. Add 175 µL of cell suspension into one well on the high side of each device and add 175 µL of EGM2 complete to the other well. On the low side, add 50 µL of EGM2 complete media to both wells.
      7. Under the microscope, watch for the fluorescent cells to flow through the vascular network. This will typically occur within approximately 2 min after adding the cells to the media reservoir.
      8. Once cell flow is established, begin imaging the fluorescent cell channel (and other channels, if desired). This is T = 0 timepoint. Take additional images at multiple time points or a single end-point image, depending on the study design. For example, imaging every 10 min will result in high-resolution time courses or every 6-12 h to track periodic cell movements.
  3. Immunofluorescent (IF) staining
    1. Aspirate media from wells. Add 200 µL of 4% PFA to both wells of the high side of each device unit and 50 µL to the low side. Allow PFA to flow through the chambers for 15 min at room temperature or 30 min at 4°C.
    2. During the incubation, prepare a 24-well plate with 500 µL of 1x PBS per well. Calculate how many wells are needed to stain each device.
    3. Remove PFA completely from wells. Turn the plate upside down and carefully remove the plastic backing on the membrane.
      NOTE: IF staining can also be performed in situ without removing the membrane and device. To do so, perform staining steps by perfusing reagents through the VMO/VMT and increase the duration of each incubation step by approximately 6-fold.
    4. Very gently and carefully peel the bottom membrane layer off the feature layer of the device to expose the tissue chambers by gripping both corners and pulling down in a slow and smooth motion. Most of the tissue should remain in the tissue chamber. Please refer to Figure 3A.
    5. Use a razor blade or scalpel to apply sufficient force to fully cut through the feature layer and cut a small rectangle around each individual device unit, as shown in Figure 3B.
    6. Wedge a spatula between the feature layer and the well plate. Apply gentle pressure underneath the feature layer to carefully remove the entire feature layer containing the tissue chamber from the well plate.
    7. Place each rectangular PDMS feature layer piece containing the tissue face down into a single well containing PBS.
    8. Once all units are in wells, wash with PBS by placing the plate on a gentle rocker for 5 min, aspirating PBS from the well, and replacing it with 500 µL of fresh PBS. Repeat for a total of 3 washes.
    9. Aspirate PBS from each well and permeabilize tissues with 500 µL of 0.5% Triton-X in PBS, 2x for 10 min each on a gentle rocker. Remove permeabilization solution.
    10. Block in 500 µL of 10% serum in 0.1% Triton-X per device for 1 h at room temperature with gentle rocking.
    11. Dilute primary antibodies in 3% serum in 0.1% Triton-X to the desired concentration and volume. Remove the blocking solution and add enough primary antibody solution to fully cover the bottom of each well and allow free movement of the device tissues (~200 µL). Cover the plate with a transparent film.
    12. Incubate the plate rocking overnight at 4 °C. The next day, bring the plate containing device tissues back to room temperature (~15 min).
    13. Aspirate primary antibody solution from each well and wash chambers with 500 µL of PBS, 3x for 5 min each on a gentle rocker.
    14. Add 200 µL of secondary antibody in 3% serum in 0.1% Triton-X at the desired concentration. Incubate the plate with gentle rocking for 1 h at room temperature in the dark.
    15. Aspirate secondary antibody solution and wash with PBS, 3x for 5 min each with gentle rocking. Add a solution of 1x DAPI in 0.1% Triton-X for 10 min while rocking in the dark.
    16. Remove rectangular device cut-outs containing stained tissues from the plate using tweezers and place tissue-side up on a paper towel.
    17. Pipette a few µL (~10 µL) of antifade solution directly on each chamber and coverslip, taking care not to introduce bubbles. Allow antifade to cure on chambers overnight at room temperature in the dark and then proceed with imaging.
  4. Tissue and cell isolation for molecular assays
    NOTE: Each high throughput plate will contain approximately 1-2 x 105 cells, depending on the time point of harvest. Scale the number of experimental replicates to account for total cells as well as potential loss during harvesting.
    1. Single-cell analyses
      1. Aspirate media from each well and invert the high-throughput plate so that the device layer is facing up.
      2. Remove the plastic backing on the membrane. Very gently and carefully peel the PDMS bottom membrane off the feature layer of the device to expose the tissue chambers by gripping both corners and pulling down in a slow and smooth motion.
      3. The membrane can be removed even with proper bonding. Most of the tissue should remain in the tissue chamber after removing the membrane; however, if any portion is stuck to the membrane, follow the steps below on the membrane itself.
      4. Wash each device unit with 500 µL of HBSS or PBS. To each device unit, add 100 µL of dissociation reagent and allow it to sit as a droplet on top of the device. Put the plate back in the 37 °C incubator for 5 min.
      5. After digestion, use a P200 pipette to pipet up and down across the tissue chambers and collect the tissues in the dissociation reagent. Move the pipet tip back and forth across each device to ensure full removal of the tissue and collect into a 15 mL conical with 500 µL of EGM2 to neutralize the dissociation reagent.
      6. For full removal of remaining cells from the tissue chamber, add 500 µL of EGM2 to each device unit and wash with a P200 pipette.
      7. Centrifuge the digestion solution containing the dislodged tissues at 300 x g for 5 min at 4 °C to pellet single cells and whole tissues.
      8. Carefully aspirate media and add 500 µL of 1 mg/mL (200 U/mL) collagenase type IV, 0.1 mg/mL hyaluronidase type V, and 200 U/mL DNAse type IV in HBSS to the tissues.
      9. After gentle resuspension, allow the solution to sit for 2 min at room temperature before pipetting gently again to dissociate the gel.
      10. Wash digestion mix with 10 mL of EGM2 and centrifuge at 300 x g for 5 min at 4 °C. Resuspend cells in 1x DPBS with 1% BSA or HSA and pass through a pre-wetted 70 µm filter by spinning at 200 x g for 1 min.
      11. Count the cells and adjust the volume so that the final concentration is 1000 cells per µL. Cellular suspensions can then be subjected to FACS, flow cytometry, or single-cell RNA sequencing.
    2. RNA isolation from whole tissues
      1. Follow steps 4.4.1.1 and 4.4.1.2 above.
      2. Add approximately 10 µL of RNA lysis buffer onto each exposed tissue chamber, ensuring that buffer pools directly on top of tissues. Do not use more than 100 µL of RNA lysis buffer in total.
      3. Incubate for 3 min at room temperature. Use the P20 to pipet up and down on each device unit and use the pipet tip to scrape any residual material from the tissue chamber if necessary.
      4. Transfer as much lysis buffer as possible into a 1.5 mL microcentrifuge tube. Repeat steps 4.4.2.2.-4.4.2.3. for remaining devices and pool samples into the 1.5 mL tube.
      5. Follow the manufacturer's instructions for isolating RNA, depending on the kit or reagents.

Figure 3
Figure 3. Preparing platform for immunostaining. (A) Schematic of fully assembled device platform with membrane layer on top. To remove the membrane, carefully pull each corner of the outer layer down in a steady, gentle motion. (B) Once the membrane layer is removed completely, use a blade, scalpel, or knife to cut rectangles around the tissue chamber of each device unit, taking care not to cut into the tissue itself. A spatula can then be wedged under each rectangle to dislodge it from the plate and place each unit into a single well of a 24-well plate with PBS for staining. Please click here to view a larger version of this figure.

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Representative Results

Following the protocols outlined here, VMOs and VMTs were established using commercially purchased EC, NHLF, and, for VMT, the triple-negative breast cancer cell line MDA-MB-231. Established VMOs were also perfused with cancer cells to mimic metastasis. In each model, by day 5 of co-culture, a vascular network self-assembles in response to gravity-driven flow across the tissue chamber, serving as a conduit for in vivo like delivery of nutrients, therapeutics, and cancer or immune cells to the stromal niche (Figure 4). VMOs were first established by introducing mCherry-labeled EC into the tissue chamber, as shown in Figure 4A (day 0 of culture), with an even distribution of cells. On day 2 of VMO culture, EC begin to stretch out and lumenize (Figure 4B), and by day 4, EC have anastomosed with the outer microfluidic channels and form a continuous vascular network (Figure 4C). After the vasculature formed anastomoses and lined the outer channels, VMO tissue was perfused with 70 kD FITC-dextran to confirm vascular patency (Figure 4D). FITC-dextran was introduced into the media reservoir with the highest hydrostatic pressure and allowed to perfuse across the tissue chamber via micro-vessels from the high-pressure side to the low-pressure side, as indicated by the arrows. In the VMO, FITC-dextran fully perfused the microvascular network within 15 min with minimal vascular leak, confirming tight vascular barrier function (Figure 4E). MDA-MB-231 cells were then perfused into VMO, where cells adhered to the endothelial lining (Figure 4F) and extravasated into the extra-vascular space within 24 h post-perfusion, forming multiple micro-metastases within the tissue chamber (Figure 4G). Time-lapse microscopic fluorescent images were taken every 50 ms with 4x and 10x air objectives on an inverted confocal microscope to observe cancer cells perfusing through the microvasculature in real-time (Supplementary Video 1, Supplementary Video 2).

In the VMO, T cells can be seen extravasating into the extracellular space over the course of 45 min (Figure 4H-I). Time-lapse fluorescent micrographs were taken on a confocal microscope to acquire a z-stack of 150 µm depth every 15 min to observe T cell extravasation in real time (Supplementary Video 3). As shown in Figure 4J, MDA-MB-231 VMT with fully formed, non-leaky vessels were perfused with T cells (yellow), many of which rapidly adhered to the vascular wall (arrowheads; Figure 4K, Supplementary Video 4, Supplementary Video 5). These results, in addition to prior studies8,9,10,11,12,13,14,15, demonstrate the utility of the VMO and VMT platforms for immunology and immune-oncology research, respectively.

Figure 4
Figure 4. Representative results for MDA-MB-231 VMT and VMO. (A) VMO on day 0 immediately after loading cells into the tissue chamber. EC are shown in red. Scale bar = 500 µm. (B) By day 2 of VMO culture, EC begin to stretch in response to flow. (C) VMO day 4 shows that the vascular network is anastomosed with the outer microfluidic channels, and vessels are nearly mature. (D) VMO networks are fully perfused and patent on day 5 of culture. Vessels shown in red, 70 kD FITC-dextran green. The direction of flow is indicated by arrows. Scale bar = 500 µm. (E) Zoom view of perfused VMO. Scale bar = 100 µm. (F) MDA-MB-231 (cyan) is perfused through the same VMO network shown in E, and at time 0, cancer cells have adhered to the endothelial vessel lining (arrowheads). Scale bar = 100 µm. (G) By 24 h, MDA-MB-231 cells have extravasated into the extracellular space, establishing multiple micro-metastases within the vascular niche. Scale bar = 100 µm. (H) Time-lapse confocal fluorescent microscopy reveals T cell extravasation through a micro-vessel within the VMO (I) over the course of 45 min. Arrowheads denote areas of extravasation. Scale bar = 50 µm. (J) Triple-negative breast cancer cell line MDA-MB-231 is established in the VMT and perfused on day 5. Scale bar = 500 µm. The vascular network shows minimal leak at 15 min post-perfusion (inset, scale bar = 100 µm). (K) MDA-MB-231 VMT (same as in B) is perfused with T cells (yellow), with multiple areas of T cell adherence to the vascular wall (arrowheads). Scale bar = 500 µm. Please click here to view a larger version of this figure.

Supplementary Video 1. Perfusion of ovarian cancer cells in the VMO. Time-lapse fluorescent microscopy of COV362 cells (cyan) perfused through a vascular network (red) and imaged at 4x objective every 50 ms for 1 min. Please click here to download of this Video.

Supplementary Video 2. Perfusion of triple-negative breast cancer cells in the VMO. Time-lapse fluorescent microscopy of MDA-MB-231 cells (cyan) perfused through a vascular network (red) and imaged at 10x objective every 50 ms for 30 s. Please click here to download of this Video.

Supplementary Video 3. T cell perfusion of VMO. Time-lapse confocal fluorescent microscopy captured the process of T cell extravasation through a micro-vessel within the VMO over a 45 min duration. Z-stack images were obtained every 15 min, with a step size of 2 µm and a depth of 150 µm. The vessel is red, T cells are yellow. Please click here to download of this Video.

Supplementary Video 4. T cell perfusion of VMT. Time-lapse fluorescent microscopy of T cells perfused through MDA-MB-231 VMT at 4x objective. Images were acquired every 50 ms for 30 s. T cells are shown in yellow, MDA-MB-231 in cyan, and vessels/EC in red. Please click here to download of this Video.

Supplementary Video 5. Zoom view of T cell-VMT perfusion. Magnified 10x view of MDA-MB-231 VMT perfused with T cells (from Supplementary Video 4). Images were acquired every 50 ms for 30 s. T cells are shown in yellow, MDA-MB-231 in cyan, and vessels/EC in red. Please click here to download of this Video.

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Discussion

Nearly every tissue in the body receives nutrients and oxygen through the vasculature, making it a critical component for realistic disease modeling and drug screening in vitro. Moreover, several malignancies and disease states are defined by vascular endothelial dysfunction and hyperpermeability3. Notably, in cancer, tumor-associated vasculature is often ill-perfused, disrupted, and leaky, thus acting as a barrier to therapeutic and immune cell delivery to the tumor. Furthermore, vasculature serves as a conduit through which cancer cells can metastasize to seed distant tissues and facilitates cell-cell communications that dampen the immune response while further promoting cancer cell growth and dissemination. These phenomena highlight the crucial role the vascular niche plays in therapeutic resistance and cancer progression and the need to accurately model the tumor microenvironment during preclinical study. Yet standard in vitro model systems fail to include appropriate stromal and vascular components or incorporate dynamic flow conditions. To address these shortcomings in current model systems, methods to establish a well-characterized microphysiological system that supports the formation of a living, perfused human micro-tumor (VMT) for physiologic oncology research were presented. Importantly, the VMT models key characteristics of aberrant tumor-associated vessels and tumor-stromal interactions, making it ideal for biomimetic disease modeling and therapeutic efficacy testing10.

For ease of use, the platform does not require any external pumps or valves and, owing to the 96-well plate format can be adapted to standard culture equipment and workflows. Further, different device iterations to address distinct biological questions and established tissue- and patient-specific compartments have been validated8,9,10,11,12,13,14,15,16,17. While the platform can be adapted to virtually any organ- or tissue-specific use by integrating various cell types, cells must be tested first for growth and vasculogenic capacity within the VMO/VMT at varying cell concentrations to determine the optimal seeding density and co-culture conditions. To establish the vasculature, human endothelial colony-forming cell-derived endothelial cells (ECFC-EC) can be purchased commercially or freshly isolated from cord blood by selecting CD31+ cells. Human umbilical vein endothelial cells (HUVEC) can also be used to establish vasculature within the VMO/VMT and can either be purchased commercially or freshly isolated from umbilical cords. Additionally, induced pluripotent stem cell-derived endothelial cells (iPSC-EC) have been successfully tested in the platform, opening the possibility of a completely autologous system18. Commercially derived fibroblasts (standard, normal human lung fibroblasts for their vasculogenic potential) work well in the VMO/VMT, and some primary-derived stromal cell populations can be incorporated or substituted as well. Primary-derived tumors can be introduced into the VMT as single cells, spheroids, organoids, or tumor chunks. Matrix composition can be modified according to experimental needs, including spiking with collagens, laminin, fibronectin, or even decellularized tissue matrices19.

The protocol includes several critical steps where special care is essential to avoid common issues (Figure 5). During loading, ensure homogeneous mixing of the cell/fibrin slurry by careful pipetting and smooth introduction into the tissue chamber (Figure 5A). Apply proper pressure to expel the gel completely into the chamber to prevent partial loading (Figure 5B). Visualizing the cell/fibrin slurry transversing the entire tissue chamber is necessary to ensure complete chamber filling and can be facilitated by placing a gloved finger behind the device unit. Avoid pressing too hard on the micropipette plunger to prevent bursting the cell/fibrin mix into the microfluidic channels (Figure 5C). Care must be taken not to introduce air bubbles during pipetting to prevent interference with tissue development and downstream applications (Figure 5D). Proper mixing and loading speed are crucial to avoid areas of inconsistent clotting (Figure 5E) while removing the pipette tip prematurely may also disrupt the gel in the chamber (Figure 5F). Practice loadings are recommended to familiarize users with the timed element of the procedure and the loading step. Further, properly introducing laminin into the microfluidic channels is crucial for EC migration, anastomosis with outer channels, and the formation of a continuous, perfusable network for nutrient delivery. Incomplete or absent channel lining will lead to poor perfusion results and unusable VMO/VMT.

Figure 5
Figure 5. Common mistakes with loading. (A) Microfluidic device unit properly loaded without defects. (B) Cell/fibrin mix was not introduced completely into the chamber, resulting in partial loading. (C) Too much pressure applied during loading, resulting in gel bursting into the microfluidic channel, blocking flow. (D) Air bubbles introduced into the cell/fibrin mix within the chamber while pipetting. (E) Improper mixing of the cell/fibrin mix or slow loading causing inconsistencies in clotting. (F) Removing the pipette tip from the loading port before the gel has sufficiently set will result in disruption of the cell/fibrin mix in the tissue chamber. Please click here to view a larger version of this figure.

Robust and standardized workflows for analysis are crucial in VMO/VMT studies, as they generate substantial amounts of imaging data. Image processing and analytical methods for VMO/VMT have been described previously8,9,10,11,12,13. For tumor quantitative analysis, the fluorescent intensity in the color channel representing the tumor cells is measured using open-source software like ImageJ/Fiji (National Institute of Health)20 or CellProfiler (Broad Institute)21. The threshold of tumor micrographic images is set to select the fluorescent tumor region, and the mean fluorescence intensity is measured within that region. The tumor's total fluorescent intensity is calculated as the product of the fluorescent area and its mean intensity, normalized to baseline values (pre-treatment) to obtain the fold change in tumor growth per device over the experimental period. Regarding vessel quantitative analysis, AngioTool (National Cancer Institute)22, ImageJ/Fiji macro scripts, or MATLAB software, such as REAVER23, can be used to quantify total vessel length, number of endpoints, number of junctions, average vessel length, vessel diameter, mean lacunarity, and vessel percentage area. Machine learning algorithms can be integrated into workflows for automatic analysis of vascular images to identify compounds that effectively disrupt the vasculature24. Perfusion images are analyzed by measuring the change in fluorescence intensity within regions of the extracellular space and calculating the permeability coefficient10. Finite element simulations of intraluminal flow inside a microvascular network can be performed using COMSOL Multiphysics25. Implementation of standardized analytical methods is critical for extracting meaningful insights from the vast amount of data generated in VMT studies.

The protocol outlined here will allow the user to leverage the VMO/VMT platform to study many aspects of tumor biology, including tumor growth/progression, tumor metastasis, intra-tumor T cell dynamics, and tumor response to chemotherapy and anti-angiogenic treatment. To enable physiologically relevant immuno-oncology studies, it was demonstrated how freshly isolated T cells perfuse through the microvasculature, extravasate across the endothelial cell barrier, and migrate into the tissue construct. Time-lapse microscopic confocal imaging was presented as a tool to view spatially random, temporally rapid events, including T cell extravasation, that are not readily visualized with other model systems. In addition, we have previously tested multiple types of antineoplastic drugs in the VMT, including chemotherapeutics, small molecule/tyrosine kinase inhibitors, monoclonal antibodies (such as anti-PD1 and bevacizumab), anti-angiogenic compounds, and vascular stabilizing agents, underscoring how the platform can be used to test different classes of drugs targeting both the tumor and the associated stroma8,9,10,11,12,13. Effluent can be collected from the platform and analyzed for various cytokines as well as exosomes. In future studies, the VMT platform can be used to assess the sensitivity of tumor cells to T-cell-mediated attack at the individual patient level. In conclusion, the VMT is a flexible and powerful platform and one that is ideal for studying tumor biology, where remodeling of the vascular and stromal components is key to tumor progression.

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Disclosures

CCWH has an equity interest in Aracari Biosciences, Inc., which is commercializing a version of the technology described in this paper. The terms of this arrangement have been reviewed and approved by the University of California, Irvine, in accordance with its conflict-of-interest policies. There are no other conflicts of interest.

Acknowledgments

We thank members of Dr. Christopher Hughes' lab for their valued input into the procedures described, as well as our collaborators in Dr. Abraham Lee's lab for their assistance with platform design and fabrication. This work was supported by the following grants: UG3/UH3 TR002137, R61/R33 HL154307, 1R01CA244571, 1R01 HL149748, U54 CA217378 (CCWH) and TL1 TR001415 and W81XWH2110393 (SJH).

Materials

Name Company Catalog Number Comments
Fabrication
(3-Mercaptopropyl)trimethoxysilane, 95%  Sigma-Aldrich 175617-100G
Greiner Bio-One μClear Bottom 96-well Polystyrene Microplates Greiner Bio-One 655096
Methanol ≥99.8% ACS VWR Chemicals BDH BDH1135-1LP
MILTEX Sterile Disposable Biopsy Punch with Plunger, 1mm diameter, Integra Miltex 33-31AA-P/25
PDMS membrane PAX Industries HT-6240
Plasma Cleaner PDC-001 Harrick Plasma N/A
Smooth-Cast 385 Smooth-On N/A
SP Bel-Art Lab Companion Clear Polycarbonate Cabinet Style Vacuum Desiccator Bel-Art F42400-4031
Standard Lids with Condensation Rings, 96-well plate VWR 82050-827
SYLGARD 184 Silicone Elastomer Kit (PDMS) Dow 4019862
Cell culture/Loading
BioTek Lionheart FX Automated Microscope Agilent  CYT5MFAW
CELLvo Human Endothelial Progenitor Cells StemBioSys N/A
Collagen I, rat tail Enzo Life Sciences
Collagenase from Clostridium histolyticum (type 4) Sigma-Aldrich C5138
Corning Hank’s Balanced Salt Solution, 1X without calcium and magnesium Corning 21-021-CV
Corning DMEM with L-Glutamine, 4.5g/L Glucose and Sodium Pyruvate Corning 10013CV
DAPI Sigma-Aldrich D9542
DPBS, no calcium, no magnesium Gibco 14190144
EGM-2 Endothelial Cell Growth Medium-2 BulletKit Lonza CC-3162
Fibrinogen from bovine plasma Neta Scientific SIAL-341573
Fibronectin human plasma Sigma-Aldrich F0895
Fluorescein isothiocyanate–dextran (70kDa) Sigma-Aldrich FD70S-1G
Gelatin from porcine skin Sigma-Aldrich G1890
Hyaluronidase from sheep testes (type 4) Sigma-Aldrich H6254
Laminin Mouse Protein Gibco 23017015
Leica TCS SP8 Leica N/A
MDA-MB-231 ATCC HTB-26
NHLF – Normal Human Lung Fibroblasts Lonza CC-2512
Nikon Eclipse Ti Nikon N/A
Paraformaldehyde 4% in 0.1M Phosphate BufferSaline, pH 7.4 Electron Microscopy Sciences  15735-90-1L
PBMCs - Peripheral blood mononuclear cells Lonza CC-2702
PBS, pH 7.4 Gibco 10010049
Premium Grade Fetal Bovine Serum (FBS), Heat Inactivated Avantor Seradigm 97068-091
ProLong Gold Antifade Mountant Invitrogen P10144
Quick-RNA Microprep Kit Zymo Research R1051
Thrombin from bovine plasma Sigma-Aldrich T4648
Triton X-100 (Electrophoresis), Fisher BioReagents BP151-100
TrypLE Express Enzyme (1X), phenol red Gibco 12605028
Trypsin-EDTA (0.05%), phenol red Gibco 25300062
Vasculife Lifeline Cell Technology LL-0003

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References

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Tags

Vascularized Micro-tumor Model Cancer Research Tumor Microenvironment Solid Cancers Preclinical Cancer Research Therapeutic Development Tumor Chip Microphysiological System Human Cell Types Microfluidic Platform Perfused Vascular Network Endothelial Layer Therapeutic Delivery Immune Cell Extravasation Metastasis Fluorescently Labeled Cells Tumor Heterogeneity Gene Expression Signatures Drug Responses Personalized Medicine
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Cite this Article

Hachey, S. J., Gaebler, D., Hughes,More

Hachey, S. J., Gaebler, D., Hughes, C. C. W. Establishing a Physiologic Human Vascularized Micro-Tumor Model for Cancer Research. J. Vis. Exp. (199), e65865, doi:10.3791/65865 (2023).

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