Nondestructive Monitoring of Degradable Scaffold-Based Tissue-Engineered Blood Vessel Development Using Optical Coherence Tomography

Summary

A step by step protocol for nondestructive and long-period monitoring the process of vascular remodeling and scaffold degradation in real-time culture of biodegradable polymeric scaffold-based tissue-engineered blood vessels with pulsatile stimulation using optical coherence tomography is described here.

Abstract

Engineered vascular grafts with structural and mechanical properties similar to natural blood vessels are expected to meet the growing demand for arterial bypass. Characterization of the growth dynamics and remodeling process of degradable polymer scaffold-based tissue-engineered blood vessels (TEBVs) with pulsatile stimulation is crucial for vascular tissue engineering. Optical imaging techniques stand out as powerful tools for monitoring vascularization of engineered tissue enabling high-resolution imaging in real-time culture. This paper demonstrates a nondestructive and fast real-time imaging strategy to monitor the growth and remodeling of TEBVs in long-term culture by using optical coherence tomography (OCT). Geometric morphology is evaluated, including vascular remodeling process, wall thickness, and comparison of TEBV thickness in different culture time points and presence of pulsatile stimulation. Finally, OCT provides practical possibilities for real-time observation of the degradation of polymer in the reconstructing tissues under pulsatile stimulation or not and in each vessel segment, by compared with the assessment of polymer degradation using scanning electron microscopic(SEM) and polarized microscope.

Introduction

Tissue-engineered blood vessels (TEBVs) is of the most promising material as an ideal vascular graft¹. In order to develop grafts to be clinically useful with similar structural and functional properties as native vessels, multiple techniques have been designed to maintain vascular function^2,3. Although there have been engineered vessels with acceptable patency rates during implantation and in Phase III clinical study⁴, long-term culture and high cost also show the necessity of monitoring the development of TEBVs. Understanding of extracellular matrix(ECM) growth, remodeling, and adaptation processes in TEBVs in the biomimetic chemo-mechanical environment can provide crucial information for the development of vascular tissue engineering.

The ideal strategy to track the development of small-diameter engineered vessels⁵ should be nondestructive, sterile, longitudinal, three-dimensional and quantitative. TEBVs under different culture conditions could be assessed by this imaging modality, even including changes before and after vascular transplantation. Strategies to describe features of living engineered vessels are needed. Optical imaging techniques allow visualization and quantification of tissue deposition and biomaterials. Other advantages are the possibility to enable deep-tissue and label-free imaging with high resolution^6,7. However, image-specific molecules and less easily accessible optical equipment for real-time monitoring is a significant practical obstacle, which has limited the extensive application of nonlinear optical microscopy. Optical coherence tomography (OCT) is an optical approach with intravascular imaging modality as a widely-used clinical tool to guide cardiac interventional therapy⁸. In the literature the method of OCT was reported as a way to assess the wall thickness of TEBVs^9,10, coupled with affirmative imaging modalities for vascular tissue engineering research. Whereas, the dynamics of engineered vascular growth and remodeling was not observed.

In this manuscript, we detail the preparation of biodegradable polymeric scaffold-based TEBVs for four weeks culture. Human umbilical arteries vascular smooth muscle cells (HUASMCs) are expanded and seeded into a porous degradable polyglycolic acid (PGA) scaffolds in the bioreactor. Biodegradable polymers play the role in a temporary substrate for tissue engineering and have a certain degradation rate¹¹. In order to ensure an appropriate match between scaffold degradation and neo-tissue formation, ECM and PGA scaffolds are crucial factors for effective vascular remodeling. The perfusion system simulates the biomechanical microenvironment of native vessels and maintains a consistent deformation under pressure stimulation.

The aim of the presented protocol is to describe a relatively simple and nondestructive strategy for TEBVs imaging and long-term monitoring of culture. This protocol can be utilized for visualization of morphological changes and thickness measurements of engineered vessels under different culture conditions. Additionally, the analyses of polymer-based materials degradation in the tissue engineering scaffolds can be performed for the identification. By combining methods of scanning electron microscopic(SEM) and polarized microscope used in this protocol, correlation and quantification of extracellular matrix distribution and PGA degradation can be made, which can facilitate assessing scaffold degradation combined with OCT imaging.

Protocol

1. Degradable PGA Scaffold based Tissue-engineered Vessels Culture

1. PGA Scaffold Fabrication
   1. Sew PGA mesh (19 mm diameter and 1 mm thick) around silicone tubing sterilized by ethylene oxide (17 cm length, 5.0 mm diameter, and 0.3 mm thick) using 5-0 suture.
   2. Sew polytetrafluoroethylene (ePTFE, 1cm length) with 4-0 suture onto each end of PGA mesh and overlapped by 2 mm.
   3. Dip PGA scaffolds with the hand in 1 mol/L NaOH for 1 min to adjust the spatial structure of the mesh and soak with tissue culture grade water three times for 2 min each. Gently pat dry the scaffold with a tissue paper each time. Then dry up scaffolds in a hood with a blower for 1 h.
2. Assembly of bioreactor and the Y-junction for OCT imaging
   1. Soak the self-developed glass cylindrical bioreactor (10 cm diameter and 11.7 cm in height with four lips inside and four side-arms outside the reactor as shown in Figure 1), PGA scaffolds, silicone tube (external diameter 5 mm, thickness 0.3 mm), biocompatible tubes, connectors, stir bar and equipment for assembly in a 95% ethanol tank for 2 h.
   2. Pull PGA scaffold through side-arms of the bioreactor connected to one side with a connector as well as another side with the Y-junction used to deliver OCT guidewire. Assemble another PGA scaffold in the bioreactor in the same way. Please refer to Figure 1.
   3. Fit ePTFE to bioreactor lips by tightening with 4-0 sutures.
   4. Put the bioreactor in the ethanol tank again for 1 h and dry up overnight in hood with blower on.
3. Seeding of HUASMCs and Static Bioreactor Conditioning
   1. Isolate HUASMCs from human umbilical arteries by standard explant techniques.
   2. Expand and maintain cells in smooth muscle cell growth medium composed of DMEM medium, 20% fetal bovine serum, 2.36 mg/mL HEPES, 100 U/mL penicillin G, 50 µg/mL proline, 20 µg/mL alanine, 50 µg/mL glycine, 1.5 µg/mL CuSO4, 50 µg/mL ascorbic acid, 10 ng/mL basic fibroblast growth factor and 10 ng/mL platelet-derived growth factor.
   3. Seed HUASMCs at a concentration of 5×10⁶ cells/mL in the above culture medium onto the PGA scaffolds.
   4. Put a stir bar (1.5 cm length) in the bioreactor. Insert one feeding tube (5 mm diameter, 15 cm length) and three short tubing segments (5 mm diameter, 7 cm length) for gas exchange through the silicone stopper lid.
   5. Attach PTFE 0.22 µm filters to each air change tube and one heparin cap to the feeding tube. Adjust the stir bar with a stirring speed of 13 rounds per minute. Assemble the glass bioreactor, silicone stopper lid and PGA scaffold into the culture system.
   6. Allow HUASMCs to adhere for 45 min by leaning the bioreactor every 15 min with stand, to the left and right. The reactor ports and joints are all sealed with paraffin film.
   7. Connect the Luo-Ye pump, PBS bag, the driver with biocompatible tubes as the perfusion system. Open the drive to fill the tubes with PBS.
   8. Place the overall bioreactor in a humidified incubator with 5% CO₂ at 37 °C. Fill the culture chamber with 450 mL of the HUASMCs culture medium.
   9. Press the stop button and turn off the power of the drive device. Grow the seeded scaffolds under static culture for one week.
   10. Change the culture medium every 3-4 days by aspirating half of the old medium through the feeding tube and refilling the reactor with an equivalent amount of fresh culture medium.
4. Preparation of the perfusion system for OCT imaging
   1. Pump fluids in the PBS bag to circulate through biocompatible tubes and back to the bag.
   2. Open the power of the driver and regulate pump setting with a frequency of 60 beats per minute and output systolic pressure of 120 mmHg. Adjust the mechanical parameters according to the needs of tissue engineering vascular culture.
   3. Click the run button to make the perfusion system work. Provide the above fixed pulsatile stimulation to the vessels for 3 weeks by iteratively pressurizing biocompatible tubes^10,12 after 1 week of static culture.

2. Performing Optical Imaging with OCT

1. Use a light source to ensure the axial resolution of 10-20µm and the image depth of 1-2 mm to identify the structure of TEBV based on the frequency-domain OCT intravascular imaging system⁹.
2. Turn on the power switch and open the image capture software.
3. Connect the fiber optic imaging catheter to the drive-motor and optical controller (DOC) with catheter automatic retreat function.
4. Set parameters of image acquisition rate to 10 frames per second with an automatic pullback speed of 10 mm/s.
5. Attach imaging catheter to Y-junction via heparin cap with a 18G needle.
6. Place the catheter into the silicone tube and identify the suture tightness of PGA mesh before loading PGA scaffold onto the bioreactor.
7. Place the catheter tip over the region of interest. Adjust the pullback device and check for the image quality⁸.
8. Acquire images at 1, 4, 7, 10, 14, 17, 21, 28 days in culture for each individual TEBV and save sequentially with real time observation of TEBV microstructure, including surface morphology, internal structure and composition.
9. Repeat the measurement for 3 times to get reliable measurement of engineered vessels each time. Capture a series of images throughout testing using the image capture software.

3. Imaging Analysis

1. Use image analysis software to measure TEBV wall thickness. Select the image to be analyzed. Click the tracking tool to identify the inner side of TEBV by the software automatically and manually sketch the outer side. A diagram of thickness will appear on the screen.
2. Repeat the measurement for 5 times to get reliable measurement of the constructs. The OCT analysis was performed by two independent investigators blinded to the obtained information.

4. Harvest of TEBV and Tissue Processing

1. Open the silicone stopper lid placed over the bioreactor when the culture is finished and discard the culture medium. Loosen ePTFE from bioreactor lips and cut the silicone tubes from the outer side of ePTFE with scissors. Harvest TEBVs from the bioreactor and cut into sections for scanning electron microscopy examination.
2. Take out the rest of TEBVs and cut into 4 µm thick sections. Pull out the supporting silicone tube and fix sections with 4% paraformaldehyde. Perform routine histological staining of Masson's trichrome and Sirius red to examine the morphology of collagen and PGA^10,13,14.
3. To assess PGA content and collagen component, observe histologic samples with Sirius red staining by a polarized microscope. PGA remnants are clearly demarcated through birefringence and the remnant area can be quantified based on the cross-sectional area¹⁰.

Results

The three-dimensional culture system consisted of a culture chamber in the bioreactor and the perfusion system with a closed fluid cycle^10,13 (Figure 1). The OCT imaging catheter was inserted into the distal end of the Y-junction and pulled back in the silicone tube for imaging. OCT imaging was first used to delineate the structural characterization of biodegradable polymeric scaffold-based TEBVs duri...

Discussion

To generate engineered vessels with structural and mechanical properties similar to those of native blood vessels can lead to shorten the time for clinical use and is the ultimate goal of vascular engineering. Optical imaging techniques permit the visualization of tissue engineered vascular specific components, which cannot monitor individual constructs throughout culture and exposure grafts to a culture environment without compromising sterility⁷. In this article, the culture chamber is separated...

Materials

List of materials used in this article

Name	Company	Catalog Number	Comments
PGA mesh	Synthecon
silicone tube	Cole Parmer
connector	Cole Parmer
intravascular OCT system	St. Jude Medical, Inc	ILUMIEN™ OPTIS™ SYSTEM
scanning electron microscopic	Philips	FEI Philips XL-30
polarized microscope	Olympus	Olympus BX51
sutures	Johnson & Johnson
pulsatile pump	Guangdong Cardiovascular Institute
LightLab Imaging software	St. Jude Medical, Inc