Measurement of the Compressibility of Cell and Nucleus Based on Acoustofluidic Microdevice

Summary

Here a protocol is presented to build a fast and non-destructive system for measuring cell or nucleus compressibility based on acoustofluidic microdevice. Changes in mechanical properties of tumor cells after epithelial-mesenchymal transition or ionizing radiation were investigated, demonstrating the application prospect of this method in scientific research and clinical practice.

Abstract

Cell mechanics play an important role in tumor metastasis, malignant transformation of cells, and radiosensitivity. During these processes, studying the mechanical properties of the cells is often challenging. Conventional measurement methods based on contact such as compression or stretching are prone to cause cell damage, affecting measurement accuracy and subsequent cell culture. Measurements in adherent state can also affect accuracy, especially after irradiation since ionizing radiation will flatten cells and enhance adhesion. Here, a cell mechanics measurement system based on acoustofluidic method has been developed. The cell compressibility can be obtained by recording the cell motion trajectory under the action of the acoustic force, which can realize fast and non-destructive measurement in suspended state. This paper reports in detail the protocols for chip design, sample preparation, trajectory recording, parameter extraction and analysis. The compressibility of different types of tumor cells was measured based on this method. Measurement of the compressibility of nucleus was also achieved by adjusting the resonance frequency of the piezoelectric ceramic and the width of the microchannel. Combined with the molecular level verification of immunofluorescence experiments, the cell compressibility before and after drug-induced epithelial to mesenchymal transition (EMT) were compared. Further, the change of cell compressibility after X-ray irradiation with different doses was revealed. The cell mechanics measurement method proposed in this paper is universal and flexible and has broad application prospects in scientific research and clinical practice.

Introduction

Cell mechanical properties play an important role in tumor metastasis, malignant transformation of cells, and radiosensitivity^1,2. To gain an in-depth understanding of the role of cell mechanical properties in the above process, accurate measurement of cellular mechanics is critical, and the measurement should not cause damage to the cells for subsequent culture and analysis. The measurement process should be as fast as possible, otherwise cell viability may be affected if cells are removed from the cultivation environment for a long time.

Existing cell mechanics measurement methods face some limitations. Some methods, such as magnetic twisting cytometry, magnetic tweezers and particle-tracking microrheology, cause cell damage due to the introduction of particles into cells^3,4,5. Methods that measure by contact with cells, such as atomic force microscope (AFM), micropipette aspiration, micro-constriction, and parallel-plate technique, are also prone to cell damage and the throughput is difficult to increase^6,7,8. In addition, ionizing radiation will flatten cells and increase their adhesion⁹; it is therefore necessary to measure whole cell mechanics in suspension.

In response to the above challenges, a cell mechanics measurement system based on acoustofluidic method^{10,11,12,13,14} has been developed. The channel width is matched to the acoustic half wavelength, thus creating a standing wave node at the midline of the microchannel. Under the action of acoustic radiation force, the cells or standard beads can move to the acoustic pressure node. Since the physical properties of the standard beads (size, density, and compressibility) are known, the acoustic energy density can be determined. Then, the cell compressibility can be obtained by recording the motion trajectories of cells in the acoustic field. Non-destructive high-throughput measurement of cells in suspension state can be achieved. This paper will introduce the design of the microfluidic chip, the establishment of the system and the measurement steps. Measurement of various types of tumor cells has been carried out to verify the accuracy of the method. The application scope of this method had been extended to subcellular structures (such as nucleus) by adjusting the resonance frequency of the piezoelectric ceramic and the width of the microchannel. In addition, the changes in cell compressibility after drug-induced EMT or X-ray irradiation with different doses were investigated. The results demonstrate the broad applicability of this method as a powerful tool for studying the correlation between biochemical changes and cellular mechanical properties.

Protocol

1. Fabricating and assembly of the acoustofluidic microdevice

1. Fabrication of the microfluidic chip.
   1. Design a single-channel chip with only one inlet and outlet as shown in Figure 1. For measuring cells, keep the rectangular cross-section of the microchannel at 740 µm wide and 100 µm deep. For measuring cell nucleus, change the width and depth of the microchannel to 250 µm and 100 µm, respectively.
   2. Prepare the microchannel on silicon wafer via reactive ion etching. Seal the top of the microchannel with a piece of transparent heat-resistant glass by anodic bonding¹⁵. Wash the chips with an ultrasonic cleaner for 10 min. Dry them in a drying oven at 50 °C for later use.
2. Fabricate polydimethylsiloxane (PDMS) blocks.
   1. Add 30 mL of pre-polymer to a 100 mm (in diameter) glass dish. Add 3 mL of curing agent to the pre-polymer with a syringe.
      NOTE: The volume ratio of the curing agent and pre-polymer is 1:10.
   2. Vigorously mix the PDMS pre-polymer and curing agent with a glass rod for about 10 min. Look for small and uniformly separated air bubbles in the solution, which indicate that the PDMS pre-polymer and curing agent are well mixed.
   3. Place the glass dish in a vacuum desiccator and evacuate for 15-25 s. Repeat this process until there are no air bubbles in the mixture.
   4. Place the glass dish in a drying oven set at 50 °C for 1 h to allow the mixture to cure. After the incubation, use a scalpel to cut the PDMS into blocks of suitable size about 1.2 cm long and 1 cm wide.
      NOTE: The length of the PDMS block is consistent with the width of the chip, and the width is selected to ensure that there is enough space in the middle for the piezoelectric ceramic when two PDMS blocks are adhered on the chip.
3. Bind the PDMS block to the chip.
   1. Punch holes in the PDMS block for inlet and outlet ports with a 1 mm diameter hollow needle. Put the PDMS blocks and chip (back side up) in a plasma cleaner for 1 min.
   2. Align the holes on the PDMS blocks with the chip inlet and outlet. Gently press the PDMS blocks to the chip for 15 s. This should cause bonding to occur between the PDMS blocks and the surface of the chip.
4. Connect the polytetrafluoroethylene (PTFE) catheter to the chip (Figure 2B).
   1. Cut two pieces of PTFE catheter with an inner diameter of 0.8 mm and a length of 10 cm. Bend a stainless-steel needle with an inner diameter of 0.7 mm and a length of 1.5 cm by 90° into an L shape. Connect it to one end of the catheter. Prepare two such catheters with needles.
   2. Insert the stainless-steel needles into the holes of the PDMS blocks. For the inlet, connect a 19 G dispensing needle to the other end of the catheter as a connector for a syringe.
   3. After completing the above steps, inject deionized water to test the tightness of the overall channel. Impervious to water means a good seal.
5. Piezoelectric ceramic assembly (Figure 2C)
   1. Use a diamond wire cutter to cut piezoelectric ceramic sheets with a diameter of 2 cm into four strips with a width of 5 mm.
   2. Ensure that the resonant frequency of the piezoelectric ceramic matches the width of the chip microchannel. For the 740 µm and 250 µm wide microchannel, use piezoelectric ceramics with resonance frequencies of 1 MHz and 3 MHz, respectively.
   3. Weld wires on both sides of the piezoelectric ceramic at one end.
   4. Glue the piezoelectric ceramic to the middle of the back of the chip with cyanoacrylate glue.
   5. To spread the glue evenly, place a drop of glue on the piezoelectric ceramic, smooth the glue with a toothpick and remove the excess glue. Then, quickly press it on the chip and continue to press for about 1 min. Ensure that the piezoelectric ceramic and the chip are firmly bonded and evenly contacted.
6. Mount the microdevice (Figure 2D).
   1. Cut a piece of PDMS (about 1.5 cm long and 1 cm wide) as the base of the microdevice. Using double-sided tape, stick one side of the base to the inlet and outlet PDMS blocks, and the other side to a transparent glass slide. Fix the whole microdevice to the microscope stage to keep the chip in one focal plane.

2. Sample preparation

1. Preparation of polystyrene standard particle solutions.
   1. Add 0.05 mL of polystyrene particle (6 µm in diameter) solution (2.1 x 10⁸ particle/mL) to 10 mL of phosphate buffered saline (PBS) and mix well.
      NOTE: In order to reduce the measurement error caused by the change of the acoustic energy density, the polystyrene particle solution was mixed with the sample solution in each experiment as calibration.
2. Preparation of cell suspensions.
   1. Wash the adherent cells (e.g., MCF7, MDA-MB-231, HCT116) at 90% confluency (~5 x 10⁵ cells) with PBS. Add 500 µL 0.25% trypsin (1x) for 1-2 min at room temperature (25 °C). Remove the trypsin, add 1 mL complete medium and form a cell suspension by pipetting.
   2. Centrifuge the cell suspension at 100 x g for 5 min. Remove the supernatant and resuspend in 0.5-1 mL of PBS in order to obtain a cell suspension. Cells were counted with a hemocytometer and the concentration was about 3-5 x 10⁵ cells/mL.
3. Preparation of cell nucleus suspension
   1. Carry out step 2.2. Then, remove the supernatant and add 200 µL of cytoplasmic protein extraction reagent A (supplemented with 1% PMSF) per 20 µL cell pellet (approximately 5 million cells) and mix well.
   2. Vortex the above mixture at 220 x g for 5 s, and then place on ice bath for 10 min. After incubation, add 10 µL of cytoplasmic protein extraction reagent B to the solution.
   3. Vortex at 220 x g for 5 s. Place on ice bath for 1 min and vortex again at 220 x g for 5 s. Then, finally centrifuge at 1,000 x g for 5 min at 4 °C.
      NOTE: The volume ratio of cytoplasmic protein extraction reagents A and B is 20:1.
   4. Remove the supernatant and resuspend the pellet in 1 mL of PBS. Then, centrifuge at 1,000 x g at 4 °C for 4 min. Remove the supernatant and resuspend in 100 µL of PBS as cell nucleus suspension.
   5. Add trypan blue to the above cell nucleus suspension and stain at room temperature (25 °C) for 4 min. The volume ratio of trypan blue solution to nucleus suspension is 1:1. Count the number of nuclei under the inverted microscope with a 10x objective.
      NOTE: To clearly identify the cell nuclei under the microscope, trypan blue staining is required. Trypan blue solution needs to be in a 37 °C water bath for 10 min before use for effective staining.
   6. Dilute the above cell nucleus suspension with PBS buffer to a concentration of 2-3 x 10⁵ nucleus/mL. Filter the cell nucleus suspension through a 70 µm sieve.

3. Measuring the compressibility of cell and nucleus

1. Set up the measurement system (Figure 3)
   1. Turn on the light source of the microscope and open the camera software. Use the 4x objective to find the middle position of the microchannel, i.e., the position of the piezoelectric ceramic.
   2. Connect the wires and weld them to the positive and negative terminals of the signal generator output on the piezoelectric ceramic, respectively.
   3. Place the syringe on the microinjection pump and connect it to the inlet catheter. Place a small container at the end of the outlet catheter to hold the fluid flowing out of the microchannel.
2. Determine measurement parameters
   1. Aspirate the polystyrene particle solution with the syringe and inject it into the chip microchannel. Avoid air bubbles in the chip microchannel to ensure accurate measurement. Ensure that particles are evenly distributed in the chip microchannel.
      NOTE: Measurement can be conducted without flow or syringe pump. If needed, the flow rate of the microinjection pump should be set to a proper value. Here, the range of flow rate is 0-20 µL/h.
   2. Set the output of the signal generator to a sine signal with a frequency of 1 MHz (3 MHz for cell nucleus measurement) and peak-to-peak voltage (Vpp) of 10 V.
   3. Fine tune the frequency of the signal until it's observed that the particles move toward the midline of the microchannel and remain in forward motion along the midline after reaching the midline (Figure 4).
      NOTE: The speed of the particles moving toward the midline is determined by the voltage amplitude, which can be adjusted between 5 Vpp and 20 Vpp.
3. Measure cells and nuclei
   1. Mix 1 mL cell or nucleus suspension with the standard particle solution at the ratio of 1:1 and inject it into the microchannel with a syringe.
   2. Start recording with CCD camera when the cells or nuclei enter the field of view. Then, turn on the signal generator. Stop recording when the cells or nuclei reach the midline.
   3. Rinse the microchannel with deionized water, 75% alcohol, and deionized water in sequence for later use.

4. Data processing

1. Map particle or cell trajectories.
   1. Import the captured video into ImageJ software: File > Open> Select Folder. Click on the ellipse shape in the toolbar of the ImageJ software to pick a cell of interest and its adjacent particle (Figure 5).
   2. As shown in Figure 5, preset measurement parameters in ImageJ software as Analyze→ Set Measurement →Area, Centroid, Display Label.
   3. Taking the frame where the target cell or particle undergoes longitudinal displacement as the start frame; record the pixel position and size of the cell or particle in each frame until it reaches the midline of the microchannel. Export the data as a spreadsheet file and repeat the step until trajectories for all cells of interest are obtained.
2. Coordinate transformation and correction.
   1. Record the pixel coordinates of the four corners of the microchannel in this field of view as (0, y1), (0, y2), (x3, y3), (x4, y4). Here x3 = x4.
   2. For each measurement point (xi, yi), calculate the new coordinate (xi', yi') after rotation correction using the following formulas:
      
      
      
   3. Convert pixel coordinates to real size coordinates. The actual coordinates can be obtained by multiplying pixel coordinates by the ratio. The ratio was the actual width of the microchannel divided by the pixel width (H) of the microchannel.
   4. Transform and correct the pixel coordinates of the cells and particles obtained in step 4.1 to the final motion trajectory data. All coordinates minus the coordinates of the lower-left corner, i.e., (0, y2). The frame rate of the video is 40 frames per second, so multiply the number of frames corresponding to each coordinate by 0.025 s to obtain the time of particle movement, thereby obtaining the change of the position in the y direction with time.
3. Calculate the acoustic energy density (Figure 6A,B).
   1. The motion of the cell or particle in the Y direction is driven by the acoustic force F_ac and hydrodynamic force F_D. Calculate the motion trajectory using the following formulas:
           (1)
           (2)
           (3)
      where r and D are the radius and diameter of the cell or particle, ρ and β are the density and compressibility, ν is the velocity vector. The subscripts c and f denote the cell and fluid, respectively. d is the distance from the nearest acoustic pressure node, μ is the dynamic viscosity of the fluid, k is the wave number, and E is the acoustic energy density.
      NOTE: The density of MCF7, HCT116, A549 and cell nuclei was 1068 kg/m³, 1077 kg/m³, 1073 kg/m³, and 1155 kg/m³, respectively ^12,16,17.
   2. According to the formulas described in step 4.3.1, use the MATLAB software to obtain the numerical solution for the standard particle trajectory under the acoustic field with finite difference method.
   3. Within the preset acoustic field range, change the acoustic energy density and fit the numerical solution (obtained in step 4.3.2) and the measured motion trajectory (obtained in step 4.2) for the standard particle. Select the best fitting result according to the fitting mean square error. The acoustic energy density obtained here is used as a parameter for subsequent calculation of cell compressibility.
4. Calculate the cell compressibility (Figure 6C,D).
   1. Set the acoustic energy density to the value obtained in step 4.3.3.
   2. According to the formulas described in step 4.3.1, use the MATLAB software to obtain the numerical solution for the cell trajectory under the acoustic field with finite difference method.
   3. Similar to step 4.3.3, within the preset compressibility range, change the compressibility and fit the numerical solution (obtained in step 4.4.2) and the measured motion trajectory for the cell (obtained in step 4.2). Use the compressibility coefficient corresponding to the best fitting result as the measured cell compressibility.

Representative Results

Here, the work presented a protocol for the construction of a fast and non-destructive cell compressibility measuring system based on acoustofluidic microdevice and demonstrated its advantages for measuring cell and nucleus under different situations. Figure 1 shows the schematic of the microfluidic channel. The components and assembly of the acoustofluidic microdevice are shown in Figure 2. Figure 3 shows the setup of the measurement system. Under the action of the acoustic field force, cells and particles will move toward the midline of the microchannel, as shown in Figure 4A. Measurement of the size and position of cells or particles is shown in Figure 5. The calculation of energy density and cell compressibility by fitting is shown in Figure 6. In order to extend the application scope of this device to cellular organelles, especially the nucleus, high purity and intact nuclei were isolated from cells (Figure 7A). By adjusting the resonance frequency of the piezoelectric ceramic and the width of the microchannel accordingly, the motion trajectory of the nucleus was obtained (Figure 4B) and the measurement of nucleus compressibility was achieved (Figure 7B).

Based on this system, the compressibility of different types of cancer cells was measured and compared (Figure 8A). In addition, the changes in cell compressibility after drug-induced EMT or X-ray irradiation with different doses were investigated (Figure 8B,C). For EMT induction, growth factor such as transforming growth factor beta (TGFβ), epidermal growth factor (EGF), and basic fibroblast growth factor (bFGF) were used. For irradiation, the dose rate was 153 mU/min, and the doses used were 1, 2, 4, and 8 Gy. These results demonstrate the broad applicability of this method as a powerful tool for studying the correlation between biochemical changes and cellular mechanical properties. Most importantly, this method was a non-destruction measurement. The measured cells were collected and seeded in a cell culture dish, and it was found that there was no significant difference in cell proliferation and viability compared to the untreated group after 48 h of culture, as shown in Figure 9, indicating that the measurement has no effect on cell proliferation and survival.

Figure 1: Schematic diagram of the chip microchannel. This image shows the structure and dimensions of the chip microchannel with a single inlet and outlet. The unit is mm. Please click here to view a larger version of this figure.

Figure 2: Assembly photo for the acoustofluidic microdevice. (A) Front and back photos of the chip. (B) This image shows the inlet PTFE catheter with attached 19 G dispensing needle and stainless-steel needle. (C) This image shows the piezoelectric ceramic with wires welded. (D) This image shows the assembly of the acoustofluidic microdevice with base for fixing. Please click here to view a larger version of this figure.

Figure 3: Setup of the cell compressibility measuring system. This image shows the setup of the measuring system consisting of signal generator, syringe pumper, the acoustofluidic microdevice, microscope, and CCD camera. This figure has been modified from¹⁰. Please click here to view a larger version of this figure.

Figure 4: The movement of cells and nuclei. This figure shows the movement of cells (A) and cell nuclei (B) to the midline of the microchannel under the action of the acoustic field force. Scale bar = 250 µm. Please click here to view a larger version of this figure.

Figure 5: Measurement of the size and position of a cell or particle using ImageJ software. This figure shows the button click for obtaining parameters such as area and centroid in the ImageJ software. The pixel coordinates of the four corners of the microchannel were recorded as (0, y1), (0, y2), (x3, y3), (x4, y4). The pixel width was represented as H. Please click here to view a larger version of this figure.

Figure 6: The calculation of energy density and cell compressibility by fitting. (A) Mean squared error (LS) values at different energy densities. The acoustic energy density was obtained from the best fitting result. The unit of energy density is J/m³. (B) This figure shows the fitting of the numerical solution and the measured motion trajectory for the particle. (C) Mean squared error (LS) values at different cell compressibility. The cell compressibility was obtained from the best fitting result. (D) This figure shows the fitting of the numerical solution and the measured motion trajectory for the cell. The unit of cell compressibility is 10^-10 Pa^-1. Please click here to view a larger version of this figure.

Figure 7: Nuclei extraction and compressibility measurement. (A) This image shows the cell nuclei extracted from A549 cells viewed with a 40x objective. Scale bar = 20 µm. (B) This image shows the measured compressibility comparison of A549 cells (N = 38) and their nuclei (N = 45). The unit of cell compressibility is 10^-10 Pa^-1. The length of the box represents the standard deviation. Student's t-test and chi-square analysis were used to assess significance. **P < 0.01. Please click here to view a larger version of this figure.

Figure 8: The compressibility of different types of cancer cells and cells after drug-induced EMT or X-ray irradiation. (A) The cell compressibility of various types of cancer cells. HCT116 (N = 36), A549 (N = 68), and MDA-MB-231 (N = 32) were the cell lines of colorectal carcinoma, lung adenocarcinoma, and breast adenocarcinoma, respectively. (B) The cell compressibility of MCF7 and A549 before and after induction of EMT. (C) Cell compressibility measured at 3 h after irradiation with different doses. The unit of cell compressibility is 10^-10 Pa^-1. The end bars of the boxplot represent the 10% and 90% values, respectively. The length of the box represents the standard deviation. The middle horizontal line represents the median value. ns means no statistical significance. Student's t-test and chi-square analysis were used to assess significance. *P < 0.05, **P < 0.01. Part of this figure has been modified from^18,19. Please click here to view a larger version of this figure.

Figure 9: Cell proliferation and viability after compressibility measurement. This figure shows the A549 cell proliferation (A) and viability (B) after compressibility measurement. Control groups are untreated cells. Test groups are the cells grown for 48 h after compressibility measurement. Each experiment has at least three replicates. For cell viability, at least 300 cells were counted. Student's t-test and chi-square analysis were used to assess significance. ns indicates not statistically significant. Please click here to view a larger version of this figure.

Discussion

Commonly used cell mechanics measurement methods are AFM, micropipette aspiration, microfluidics methods, parallel-plate technique, optical tweezers, optical stretcher, and acoustic methods²⁰. Microfluidics methods can work with three approaches: micro-constriction, extensional flow, and shear flow. Among them, optical stretcher, optical tweezers, acoustic methods, extensional flow, and shear flow approaches are non-contact measurements. In contrast to contact measurements, non-contact measurements can effectively avoid the cell damage problem caused by contact or local deformation. Optical tweezers are very sensitive to the measurement environment²¹. Perturbations in optical conditions can cause significant differences in measurement results, and high laser power during measurement may also cause cell damage. Besides, optical stretcher and optical tweezers generally have low throughput^20,22. Microfluidics methods such as extensional flow and shear flow cannot measure micromechanics of tumor cells directly²³. Compared with other methods, acoustic methods have the advantages of non-destructive, high-throughput and wide applicability in the measurement of cell mechanics.

The measurement method based on acoustofluidic microdevice designed in this paper uses non-contact acoustic radiation force, and the greatest benefit is that it does not damage cells, which was confirmed by the experimental results shown here (Figure 9). Another advantage of this method is the high throughput, which can be adjusted by changing the cell concentration. Currently, a measurement speed of about 50-70 cells/min can be achieved on the premise of ensuring the accuracy of subsequent data analysis. Because the cells are measured in suspension, the measurement of non-adherent cells can be also achieved, which expands its scope of application. Moreover, measurement of the cell compressibility after irradiation was achieved in this paper, and the relationship between cell compressibility and irradiation dose was revealed (Figure 8). In addition, the measurement of cells or nucleus with different stiffness can also be adapted by adjusting the resonance frequency of the piezoelectric ceramic and the width of the microchannel. As shown in Figure 7, measurement of the compressibility of the nucleus was achieved.

Here, only the movement of cells along the length and width of the microfluidic channel was considered. The cells were considered to be in suspension because the density of the cells is close to that of the fluid. If there was cell settlement or friction with the bottom, it would be found in the subsequent trajectory fitting process. Such data will be eliminated. In order to validate the proposed method, two kinds of polystyrene beads with different diameter (6 µm and 10 µm) were tested. The beads with 6 µm diameter were used as control. The compressibility of beads with 10 µm diameter was obtained as 2.37 ± 0.11 x 10^-10 Pa^-1, consistent with the value (2.1-2.4 x 10^-10 Pa^-1) reported in another research^15,24.

Based on this method, the compressibility of cells and nuclei was measured. Since nucleus plays an important role in mechanosensing and mechanotransduction, measurement of the mechanical properties of nucleus can help to better understand how they respond to external stimulus such as ionizing radiation-induced DNA damage (Figure 8). Furthermore, experiments showed that cell compressibility can serve as a new indicator for monitoring the EMT process (Figure 8), showing its application prospects in cancer diagnosis. Since the acoustic radiation force is related to cell size, cell density, and compressibility, this method can also be used for cell isolation such as the separation of circulating tumor cells (CTCs) or their clusters from the blood sample. CTCs and their clusters play an important role in the early detection of metastatic tumors and the monitoring of radiotherapy efficacy^25,26. Therefore, this method has great clinical application prospects in cancer early screening and efficacy evaluation.

It is worth noting that the key factor affecting the measurement of this method is the matching of the resonant frequency with the width of the microchannel, resulting in the appearance of a standing wave node at the midline of the microchannel. At the same time, attention should be paid to the pasting of piezoelectric ceramics. Besides, in order to accurately identify and track the trajectory of cells or particles and avoid the problem of cell aggregation due to adhesion, the throughput should not be too high. How changes in other parameters (such as cell size, cell density, etc.) affect the measurement of compressibility has been studied in previous work¹⁸. Moreover, when measuring cell nuclei, due to their softness, a large acoustic radiation driving force is required to make them move smoothly to the midline of the microchannel, thus requiring a fast camera to accurately capture the trajectories.

Materials

Name	Company	Catalog Number	Comments
0.25% trypsin(1x)	GIBCO	15050-065
502 glue	Evo-bond		cyanoacrylate glue
A549	ATCC	CCL-185	lung adenocarcinoma
Cytonucleoprotein and cytoplasmic protein extraction kit	Beyotime	P0027	Contains cytoplasmic protein extraction reagents A and B
Dulbecco’s modified Eagle medium (DMEM)	corning	10-013-CVRC
Fetal Bovine Srum(FBS)	AUSGENEX	FBS500-S
HCT116	ATCC	CCL247	colorectal carcinoma
Heat-resistant glass	Pyrex
Leibovitz’s L-15 medium	GIBCO	11415-064
MCF-7	ATCC	HTB-22	breast Adenocarcinoma
MDA-MB-231	ATCC	HTB-26	breast Adenocarcinoma
Minimum Essential Medium (MEM)	corning	10-010-CV
Penicillin-Streptomycin	GIBCO	15140-122
Phosphate buffer	corning	21-040-cvc
PMSF	Beyotime	ST506	100mM
Polybead Polystyrene Red Dyed Microsphere	polysciences	15714	The diameter of microshpere is 6.00µm
propidium iodide(PI)	Sigma-Aldrich	P4170
SYLGARD 184Silicone ELASTOMER	Dow-Corning	1673921	Contains prepolymers and curing agents
Trypan Blue	Beyotime	C0011