An Early Study on the Mechanisms that Allow Tissue-Engineered Vascular Grafts to Resist Intimal Hyperplasia
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- Prichard, H.L., Manson, R.J., DiBernardo, L. et al. J. of Cardiovasc. Trans. Res. (2011) 4: 674. doi:10.1007/s12265-011-9306-y
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Intimal hyperplasia is one of the prominent failure mechanisms for arteriovenous fistulas and arteriovenous access grafts. Human tissue-engineered vascular grafts (TEVGs) were implanted as arteriovenous grafts in a novel baboon model. Ultrasound was used to monitor flow rates and vascular diameters throughout the study. Intimal hyperplasia in the outflow vein of TEVGs was assessed at the anastomosis and at juxta-anastomotic regions via histological analysis, and was compared to intimal hyperplasia with polytetrafluoroethylene (PTFE) grafts in the baboon model and in literature reports from other animal models. Less venous intimal hyperplasia was observed in histological sections with arteriovenous TEVGs than with arteriovenous PTFE grafts. TEVGs were associated with a mild, noninflammatory intimal hyperplasia. The extent of intimal tissue that formed with TEVG placement correlated with the rate of blood flow through tissue engineered vascular grafts at 2 weeks postimplant. Outflow vein dilatation was observed with increased flow rate. Both mid-graft flow rates and outflow vein diameters reached a plateau by week 4, which suggested that venous remodeling and intimal hyperplasia largely occurred within the first 4 weeks of implant in the baboon model. Given their compliant and noninflammatory nature, TEVGs appear resistant to triggers for venous intimal hyperplasia that are common for PTFE arteriovenous grafts, including (1) abundant proinflammatory macrophage populations that are associated with PTFE grafts and (2) compliance mismatch between PTFE grafts and the outflow vein. Our findings suggest that arteriovenous TEVGs develop only a mild form of venous intimal hyperplasia, which results from the typical hemodynamic changes that are associated with arteriovenous settings.
KeywordsTissue-engineered vascular graftIntimal hyperplasiaArteriovenous graftRemodelingBlood flow rateNoninflammatory
There are more than 347,000 patients on chronic hemodialysis . Each year, more than 100,000 new end stage renal disease patients begin therapy on hemodialysis . Native arteriovenous fistulas have recently been the first choice for access, but even with the best surgical care, fistula prevalence is only 47% in the USA . The remainder of access is dependent on arteriovenous grafts or catheters, with a preference for grafts when possible . Currently, most arteriovenous grafts that are placed for hemodialysis access are comprised of synthetic polytetrafluoroethylene (PTFE). Synthetic arteriovenous grafts suffer from significant drawbacks, which include a high rate of infection (9% per annum) and a propensity for occlusion due to thrombosis and intimal hyperplasia (40–60% in the first year), with a median patency of only 10 months [4–7]. PTFE grafts require frequent interventions to maintain patency throughout their lifetime, which necessitates costly surgical intervention, increased overall healthcare costs, and increased patient morbidity [8, 9].
By some reports, up to 85% of PTFE graft failures result from intimal hyperplasia at either the venous anastomosis or outflow vein . Intimal hyperplasia is typically characterized by intimal thickening of the vein, which diminishes the vein lumen, decreases blood flow rate, may lead to postcannulation bleeding due to intragraft pressurization, and eventually leads to thrombosis and occlusion . The intima is defined as the innermost layer of an artery or vein, on the luminal side of the internal elastic lamina. In a healthy vein, the intima is one cell layer thick and comprised solely of endothelial cells. With intimal hyperplasia, cells may migrate into the intima from the medial and adventitial layers of the vein and from the circulation [10, 12, 13]. Once they migrate into the intima, these cells express markers for myofibroblast and smooth muscle cell phenotypes. The cells proliferate and deposit extracellular matrix proteins [10, 14]. The formation of new tissue in the intima can compromise blood flow.
Intimal hyperplasia is thought to be triggered by the high wall shear stresses created by AV grafts , and compliance mismatch between PTFE and the native vein . Intimal hyperplasia also has been identified in regions with turbulent flow, flow separation, low shear stress, and oscillatory shear . In addition, PTFE’s synthetic composition commonly leads to inflammation at the graft placement site following implant, which promotes intimal hyperplasia formation .
Development of tissue-engineered vascular grafts may provide a new opportunity for hemodialysis patients. If designed correctly, a tissue-engineered graft has the potential to reduce incidence of failure mechanisms associated with PTFE grafts. We have recently described a new human tissue-engineered vascular graft (TEVG) with compliance between that of human vein and human artery , which obviates concern about compliance mismatch. Furthermore, our TEVGs are made of extracellular matrix proteins, which make them highly biocompatible and resistant to inflammation . These TEVGs are acellular, which allows them to be stored in simple refrigeration for up to 1 year, thereby making them readily available to patients at the time of need . We demonstrated excellent function of these TEVGs in multiple vascular settings. TEVGs placed as arteriovenous grafts in a baboon model for 1–6 months demonstrated a patency rate of 88%, without incidence of graft infection .
In this study, we evaluate intimal hyperplasia formation associated with arteriovenous placement of TEVGs. We also investigate the impact of flow rate and outflow vein remodeling on intimal hyperplasia formation.
Materials and Methods
Formation of TEVGs
Human TEVGs were made as described previously . Briefly, human aortic smooth muscle cells were isolated from donor aortas that were consented for research use. Cells were seeded onto tubular polyglycolic acid felt scaffolds (6 mm inner diameter) and strained cyclically (2.5% at 2.75 Hz)  in a bioreactor to produce grafts. The medium for growth of human TEVGs was high glucose Dulbecco’s modified Eagle’s medium with 20% serum, 0.13 U/ml insulin, 10 ng/ml basic fibroblast growth factor, 0.5 ng/ml epidermal growth factor, 10,000 U/ml penicillin G, 3 ng/ml copper sulfate, 50 ng/ml l-proline, 40 ng/ml l-alanine, and 50 ng/ml glycine, and was changed thrice weekly. l-Ascorbic acid was added thrice weekly to TEVG cultures.
After 10 weeks of culture, TEVGs were decellularized as described previously  in phosphate-buffered saline with 0.12 M sodium hydroxide, 1 M sodium chloride, and 25 mM EDTA, containing either 8 mM CHAPS or 1.8 mM sodium dodecyl sulfate. TEVGs were exposed to each detergent solution for up to 6 h at room temperature and were then washed with phosphate-buffered saline. All TEVGs were decellularized prior implantation. Decellularized TEVGs were stored at 4°C in phosphate buffered saline without calcium or magnesium.
All procedures were approved by Duke University’s Animal Care and Use Committee. Baboons received humane care according to the “Guide for the Care and Use of Laboratory Animals” . All surgical procedures were performed in sterile fashion under general anesthesia. After each surgery, graft patency was confirmed, wounds were closed, and animals were recovered. Baboons were anticoagulated with heparin at implant (100 U/kg given intravenously followed by 1,000 U/h for the duration of the procedure) and received aspirin (10 mg/kg) daily preoperatively until the end of the study.
An old world primate model was chosen to provide phylogenetic similarity to humans, which allowed implantation of noncross-linked human matrix-containing grafts without immunosuppression. Adult male baboons (Papio Anubis, 20–30 kg) are physically large enough to support implantation of a 6 mm inner diameter TEVG in a clinically relevant anatomic setting.
Surgical Implantation Techniques
The surgical portion of this study has been described elsewhere for TEVGs . Briefly, nine adult male baboons underwent arteriovenous placement of human TEVGs (6 mm inner diameter). One TEVG was placed between the aorta and the vena cava for 1 month. Eight TEVGs were placed for up to 6 months between the axillary artery and distal brachial vein in the upper arms of baboons, which provided a superficial site amenable for simulating hemodialysis access at 1, 3, and 6 months . Arteriovenous PTFE grafts were also placed in the baboon model between the aorta and vena cava (one graft for 1 month) and between the axillary artery and distal brachial vein in the upper arm (one graft for 6 months). All animals received only one graft to minimize risk of heart failure. All anastomoses were created with a running 6–0 prolene suture technique. One TEVG remained in vivo at the time of analysis. Two other animals with upper arm TEVGs were excluded from histological evaluation in this study. In one animal, technical difficulties with access resulted in prolonged manual pressure on the TEVG, which led to graft occlusion, unrelated to intimal hyperplasia. The other animal was excluded after pulling open its surgical incision site, exposing the TEVG and creating a wound infection.
Tissues were fixed in 10% neutral buffered formalin, embedded in paraffin, sliced (5-μm sections), and stained with hematoxylin and eosin (H&E) or Movat’s. Immunostaining was performed for α-smooth muscle actin (SMC and myofibroblast marker; Dako M0851, 1:400 dilution), CD31 (endothelial cell marker; Dako M0823, 1:700 dilution), and CD68 (macrophage marker; Thermo MS397-P1, 1:400 dilution), using 3,3′-diaminobenzidine stain. All were counterstained with hematoxylin.
Morphometric Analysis of Intimal Hyperplasia
Statistical analyses were performed with a Student’s two-sample t test, assuming unequal variances. Correlations were assessed using the Pearson method. Two-sided P < 0.05 indicated statistical significance. Numeric values are presented as the mean ± standard error of the mean.
Placement of TEVGs as Arteriovenous Grafts in a Baboon Model Triggers Mild, Nonaggressive Intimal Hyperplasia
Ratio of intimal area to medial area
Arteriovenous access creation method
Ratio of intimal area to medial area at venous anastomosis
Ratio of intimal area to medial area in outflow vein
TEVGs in a baboon model
0.37 ± 0.10
0.18 ± 0.10
PTFE grafts in a baboon model
1.3 ± 0.6
0.11 ± 0.01
PTFE grafts in a porcine modela
CD-31-positive cells (endothelial cells) were observed on the luminal surface, but were not observed within the intimal tissue (Fig. 3b). Others have shown microvessel formation within venous intima that is defined by positive staining for endothelial cell markers . Furthermore, microvessel formation indicates an aggressive type of intimal hyperplasia . Thus, the absence of microvessel formation within intimal tissue in this study suggests that TEVGs prompt a nonaggressive form of intimal hyperplasia.
CD-68-positive cells (macrophages) were very sparse (Fig. 3c). In contrast, a substantial macrophage population has been observed within intimal tissue adjacent to PTFE arteriovenous grafts . The prominent macrophage population that infiltrates PTFE grafts releases cytokines and growth factors and thereby promotes intimal hyperplasia [14, 23, 24]. Thus, the inflammatory characteristic of synthetic PTFE is thought to increase the aggressiveness of intimal hyperplasia. TEVGs likely have substantially less macrophage-related stimulation of intimal hyperplasia than PTFE.
Intimal hyperplasia at 3 and 6 month explants
Ratio of intimal area to medial area at venous anastomosis
Ratio of intimal area to medial area in outflow vein
TEVGs explanted at 3 months
0.57 ± 0.35
0.38 ± 0.38
TEVGs explanted at 6 months
0.30 ± 0.03
0.11 ± 0.05
The Mild Intimal Hyperplasia that Forms with Arteriovenous TEVG Placement is Influenced by Host Blood Flow Rate and Venous Adaptation to Flow Rate
The goal of placing arteriovenous grafts for hemodialysis access is to increase blood flow above 300 ml/min to allow for successful hemodialysis . Implantation of arteriovenous grafts allows blood to flow from the artery to the vein with diminished resistance. The new path of decreased resistance, from the artery to vein via the graft, minimizes the impact of back pressure from tapering distal arteries on arterial flow rate and thereby allows flow to increase.
Intimal hyperplasia has been shown to be triggered by high wall shear stresses that accompany high flow rates . Others have observed that flow rates decrease as intimal hyperplasia progresses . Therefore, we considered the hypothesis that (1) the high week 2 flow rates trigger intimal hyperplasia and (2) the absence of a decrease in flow rate after week 4 may indicate that intimal thickening occurred primarily within the first 4 weeks of implant.
At week 2, TEVG mid-graft flow rates positively correlated with the extent of intimal hyperplasia formation in the vein (Fig. 4b). Specifically, higher flow rates at week 2 were associated with an increase in the ratio of intimal thickness to medial thickness in the vein at explant, both in anastomotic and in juxta-anastomotic sections (P = 0.04 for correlation between flow rate at week 2 and venous anastomosis thickness ratio, and P = 0.02 for correlation between flow rate and juxta-anastomotic outflow vein thickness ratio). Our findings for TEVGs are in agreement with a clinical study, which demonstrated that week 2 velocity was correlated with the extent of venous intimal hyperplasia formation triggered by arteriovenous PTFE grafts .
No significant correlations were observed between intimal thickening and flow rate through TEVGs at any time points other than week 2 (P > 0.3 for weeks 0, 4, 12, and 24). The lack of a correlation between flow rate and intimal hyperplasia beyond week 4 suggests that much of the intimal thickening may have occurred largely within the first 4 weeks of implant. Time-course assessments of intimal hyperplasia with PTFE grafts in a porcine model have shown substantial intimal growth in histological sections by week 2 and another increase in intimal growth between weeks 2 and 4 , which supports the ability of intimal hyperplasia to form in this early time frame.
Given that outflow vein dilatation is thought to be prompted by the increase in shear stress that accompanies an increase in flow rate  and that veins dilate in an attempt to return shear stress levels back to normal , it is logical that our diameter observations match the temporal trend presented for flow rate in Fig. 4a. This agrees with one of the few clinical studies that has tracked flow and dilatation using ultrasound, wherein increases in flow rate led to venous dilatation in fistulas .
The observed decrease in diameter between weeks 2 and 4 (Fig. 5) likely correlates with a period of active intimal thickening. Given that diameter did not decrease after week 4, we submit that venous intimal thickening occurred mostly within 4 weeks of TEVG implant. Note that there was no statistical correlation between preoperative vein diameter and intimal hyperplasia formation, which suggests that flow-rate-mediated remodeling, and not preoperative anatomy, dictated intimal hyperplasia formation.
TEVGs have compliances within the range of human artery and vein and have been shown to be noninflammatory in vivo . In this study, we demonstrate that the venous intimal hyperplasia that forms in response to arteriovenous placement of TEVGs in a baboon model is only a mild type of intimal hyperplasia, as indicated by less intimal hyperplasia formation than observed with PTFE grafts, the absence of intimal microvessel formation, and a very sparse macrophage population. Furthermore, this mild intimal hyperplasia did not progress between 3 and 6 months. For TEVGs, we conclude that the extent of venous intimal tissue formation was likely driven by early changes in flow rate. High flow rates may be associated with high shear stress, turbulent flow, flow separation, and oscillatory shear. Additionally, we suggest that the intimal hyperplasia associated with TEVGs largely forms within the first month of implant and does not grow aggressively thereafter.
In addition to posing a problem for arteriovenous grafts, intimal and medial hyperplasia is also a significant problem in arteriovenous fistulas . Some triggers for formation of intimal hyperplasia in arteriovenous fistulas differ from those in PTFE grafts. Unlike PTFE grafts, fistulas do not have a large macrophage population to stimulate intimal formation. However, venous intimal thickening with fistulas has been shown to be stimulated in part by expression of growth factors within the artery .
TEVGs are acellular at implant, and the absence of cells may aid in resistance to intimal hyperplasia. While we have not performed any analysis for presence or absence of growth factors in human TEVGs, it is possible that acellular TEVGs present less growth factor expression than a native artery, thereby making the outflow vein less susceptible to intimal hyperplasia. Furthermore, the absence of cells at early time points makes acellular TEVGs reasonably inert during the early implant phase, where dynamic changes in flow are prevalent. A TEVG containing cells might respond to high shear stresses via cellular proliferation, forming intimal tissue within the first month of implant when flow rates and shear stresses are at their highest. The absence of cells in TEVGs at the time of implant may thereby aid its ability to resist early cell-mediated intimal injury.
The impact of host blood flow rate on intimal hyperplasia in the vein suggests that future TEVGs (and PTFE grafts) might better control venous intimal hyperplasia if the grafts have a mechanism to limit flow rate at the graft exits. Such a design might prevent exposure of excessive flow rates to the venous anastomosis and may thereby reduce the vein’s intimal thickening response. Tapered PTFE grafts have been evaluated to restrict flow, with the goal of reducing steal, but have not demonstrated definitive functional improvements in the clinic . Thus, an alternate approach to coarctation of the graft likely will be necessary to confirm the hypothesis that high flow rates lead to more intimal hyperplasia and address the flow-related mechanism of intimal hyperplasia formation.
Several animal studies in other labs have focused on controlling flow rate or shear stress to determine their impact on intimal hyperplasia formation, yet these studies have been performed primarily in the arterial circulation or the venous circulation, but not in arteriovenous models. In the arterial circulation, increasing blood flow across preformed intimal tissue led to regression of the intima in a baboon model . In the venous setting, extremely low shear stress has been shown to promote intimal hyperplasia in a rabbit model . Substantial differences in hemodynamics exist between bypass and arteriovenous grafts , and therefore, it is difficult to extrapolate these findings to the arteriovenous setting.
The study described herein has several known limitations. First, this is an early study with a small number of subjects. The trends observed are sensible, but we plan to continuously monitor these trends in future animals as more data on arteriovenous TEVG implantation is acquired. Second, animals were treated with aspirin throughout the course of this study, which has been shown to decrease intimal hyperplasia . However, aspirin therapy is recommended clinically  and is used routinely in preclinical models that study intimal hyperplasia, including those referenced as benchmarks in this study [11, 22, 25].
The baboon model had clear benefits for evaluation of a human vascular graft. Baboons are old world primates, which are phylogenetically closer to humans than more common cardiovascular large animal models, such as pigs, dogs, and sheep. The concordant baboon model abrogated risk of xenogenic immune response to a human cardiovascular implant. Furthermore, the vascular anatomy of baboons was large enough to support implantation of a 6 mm diameter graft. In addition, the clotting and fibrinolytic systems of primates are more closely related to humans . Therefore, baboons served as the best model for human-based cardiovascular implants. In contrast, PTFE grafts are frequently evaluated in animal models that are affordable and widely available (e.g., pigs) because PTFE is not at risk of triggering a xenogenic immune response.
The baboon model, however, also had clear limitations. Primates are significantly more expensive to purchase and maintain than any other animal , are difficult to handle and maintain , and are limited in availability. In order to circumvent the issues of high costs and limited animal availability, we considered implanting a PTFE graft in the contralateral arm of each animal. After careful consideration, we did not pursue this strategy because implantation of two high-flow arteriovenous grafts in each animal would lead to a substantial increase in cardiac output, which would create a real risk of heart failure. These limitations constrained our ability to evaluate a large number of PTFE control grafts, so only two control grafts were implanted. Therefore, in addition to presenting data on these two control PTFE grafts in the baboon model, we have presented data from literature reports of arteriovenous PTFE grafts in porcine animal models.
The results of this study provide a useful framework with which we can think about intimal hyperplasia formation. The correlation between early flow rates and intimal formation may also translate to venous intima development with fistulas and PTFE grafts. Only a handful of studies have histologically analyzed intimal hyperplasia in fistulas and PTFE grafts, yet these studies are primarily focused on failed arteriovenous grafts or fistulas [10, 21, 23] since functioning access sites are not explanted. Furthermore, failed access sites are rarely removed. Thus, the insights provided by this study can contribute the body of knowledge regarding progression of intimal hyperplasia and its triggers.
Use of TEVGs in a baboon arteriovenous model led to mild, nonaggressive intimal hyperplasia that likely formed within 1 month of implant. TEVGs are noninflammatory and compliant, and thereby avoid two common triggers of arteriovenous PTFE grafts for progression of intimal hyperplasia. Histological assessments demonstrated that TEVGs had less intimal hyperplasia than PTFE grafts. TEVGs that resist substantial intimal hyperplasia could possibly provide a new treatment option for patients with end stage renal disease. Both reduced incidence of intimal hyperplasia failure and slowed progression of intimal hyperplasia-related failure could lead to a decrease in surgical intervention of arteriovenous access grafts. Decreased surgical intervention, in turn, could decrease overall end stage renal disease healthcare costs and patient morbidity.
We would like to acknowledge Taylor Hensley and Letia Dean for assistance with histological staining, and Terry Williams for performing ultrasound measurements. This study was funded by Humacyte, Inc.
Conflict of interest
H.L.P. and S.L.M.D. are employed by Humacyte. R.J.M., J.H.L., L.D., and L.E.N. have either been paid as consultants to Humacyte or have a financial interest in Humacyte.
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