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Introduction: Treatment of coronary artery disease has made strides over the last decades. Development of drug eluting stents (DES), coated with a polymer layer and an anti-proliferative drug to reduce neointimal hyperplasia, has reduced the incidence of in-stent-restenosis relative to treatment with bare metal stents. Patients treated with first generation DES more likely suffer from (very) late events which can be cause by the permanent presence of a polymer. Therefore second generation DES with more biocompatible coatings, and third generation DES, with very thin struts coated with biodegradable polymers, were developed. Areas covered: The MiStent SES is one of these third generation DES and is designed to limit the duration of polymer exposure, optimize coronary vessel healing and more precisely and consistently control drug elution to improve safety and clinical outcomes. This review provides a detailed description of the technique behind the MiStent SES, and describes the pre-clinical and clinical trials conducted with this device to date. Expert commentary: Recent clinical trials have shown non-inferiority of very thin strut biodegradable polymer coated DES compared to durable polymer coated DES, whilst maintaining an excellent safety profile. Longer follow-up, to see the real potential benefits of these devices, is mandatory however.

Drug-eluting stents (DES) have dramatically improved the long-term efficacy of percutaneous coronary intervention (PCI). Over the last decade there have been numerous advances in DES platforms, however, all but one currently approved DES in the United States and many of the approved DES worldwide still have 3 common features: a metal stent platform, an anti-proliferative drug, and a permanent polymer. In this context, the polymer is critical to control drug release, but the polymer serves no purpose after the drug is eluted. While designed to be completely biocompatible, synthetic polymers have the potential to illicit an inflammatory response within the vessel including but not limited to delayed healing and hypersensitivity. Adverse vascular reactions to these polymers have been implicated as a cause of very late stent thrombosis, ongoing intimal hyperplasia and late "catch-up" in addition to neoatherosclerosis. To avoid the long-term risks associated with prolonged polymer exposure, DES with bioabsorbable polymers have been developed. The MiStent® Sirolimus-Eluting Absorbable Polymer Coronary Stent System (MiStent SES) (MiCell Technologies, Durham, NC, USA) combines crystalline sirolimus, a rapidly absorbing polylactide-co-glycolic acid (PLGA) coating and a thin-strut cobalt chromium alloy stent platform (Genius MAGIC® Stent System, EuroCor GmbH, Germany). MiCell's supercritical fluid technology allows a rigorously controlled, solvent-free drug and polymer coating to be applied to a bare-metal stent. This solvent-free application of drug uniquely allows a crystalline form of sirolimus to be used on the MiStent SES potentially providing improved clinical benefits. It avoids the uncontrolled burst of drug seen with other DES, provides uniform drug delivery around and between the stent struts, and allows the anti-inflammatory and anti-restenotic drug (sirolimus) to be present in the tissue through the entire polymer absorption period and for months after the polymer has been absorbed. On the MiStent SES, the PLGA/crystalline sirolimus combination is cleared from the stent within 45-60 days and PLGA is fully absorbed within 90 days. The crystalline form of sirolimus uniquely remains in the tissue and continues to expose the surrounding tissue to therapeutic levels of drug for up to 9 months which is long after the polymer is resorbed.

Background: Novel vascular scaffolds aim at equipoise between safety and efficacy. Intravascular optical coherence tomography (OCT) allows in-vivo serial assessment of stent-vessel interactions with high resolution and frequent sampling and may complement histology assessment. We investigated the vascular response to a novel absorbable coating sirolimus-eluting stent (AC-SES) by means of serial OCT and histology evaluation in a porcine model., Methods: One AC-SES and one bare-metal stent (BMS) were implanted in separate coronary arteries of three Yucatan mini-swine. Serial OCT was performed post procedure and at 3-, 28-, 90-, and 180-day follow-up. Normalized optical density (NOD) was used for the assessment of tissue response over time. Histological evaluation was performed at day 180., Results: A total of 6408 stent struts were analyzed. OCT revealed 100% of struts covered at 28 days, and a significant difference in NOD from 3 to 28 days (0.64 ± 0.07 vs 0.71 ± 0.05, respectively; P<.001) in the AC-SES group. Neointimal thickness was 0.14 ± 0.08 mm, 0.17 ± 0.11 mm, and 0.16 ± 0.09 mm in the AC-SES group and 0.18 ± 0.10 mm, 0.14 ± 0.09 mm, and 0.10 ± 0.08 mm in the BMS group, while rates of uncovered struts were 0%, 0%, and 3.1% and 1.4%, 7.8%, and 21.5%, respectively, at 28, 90, and 180 days. Minimal inflammation and a mature endothelialization were demonstrated in both groups by histology., Conclusion: OCT serial assessment of vascular response suggested NIH maturation 28 days following AC-SES implantation in pigs. These findings, coupled with histological demonstration of low inflammation scores and complete endothelial coverage as measured at 180 days, suggest a satisfactory healing response to AC-SES.

Current drug eluting stent (DES) technology is not optimized with regard to the pharmacokinetics of drug delivery. A novel, absorbable-coating sirolimus-eluting stent (AC-SES) was evaluated for its capacity to deliver drug more evenly within the intimal area rather than concentrating drug around the stent struts and for its ability to match coating erosion with drug release. The coating consisted of absorbable poly-lactide-co-glycolic acid (PLGA) and crystalline sirolimus deposited by a dry-powder electrostatic process. The AC-SES demonstrated enhanced drug stability under simulated use conditions and consistent drug delivery balanced with coating erosion in a porcine coronary implant model. The initial drug burst was eliminated and drug release was sustained after implantation. The coating was absorbed within 90 days. Following implantation into porcine coronary arteries the AC-SES coating is distributed in the surrounding intimal tissue over the course of several weeks. Computational modeling of drug delivery characteristics demonstrates how distributed coating optimizes the load of drug immediately around each stent strut and extends drug delivery between stent struts. The result was a highly efficient arterial uptake of drug with superior performance to a clinical bare metal stent (BMS). Neointimal thickness (0.17±0.07 mm vs. 0.28±0.11 mm) and area percent stenosis (22±9% vs. 35±12%) were significantly reduced (p<0.05) by the AC-SES compared to the BMS 30 days after stent implantation in an overlap configuration in porcine coronary arteries. Inflammation was significantly reduced in the AC-SES compared to the BMS at both 30 and 90 days after implantation. Biocompatible, rapidly absorbable stent coatings enable the matching of drug release with coating erosion and provide for the controlled migration of coating material into tissue to reduce vicissitudes in drug tissue levels, optimizing efficacy and reducing potential toxicity., (Copyright © 2012 Elsevier B.V. All rights reserved.)

Beta-actin is a cytoskeletal protein that has been implicated as a potentially important mediator of the growth, signaling, migration, and remodeling of cells. Beta-actin is upregulated in remodeling myocardium in response to either pressure or volume overload. The cellular localization of this response has, however, not been determined and is a necessary first step to begin to clarify the role of beta-actin in myocardial remodeling. Here we demonstrate that beta -actin protein was confined primarily to the cardiac interstitium using immunofluorescent and immunohistochemical staining. Furthermore, both staining and immunoblotting showed markedly increased beta-actin protein in myocardium within 24 h of either regional left ventricular damage or chronic volume overload. More importantly, this increase persisted up to 90 days in both models. Double staining showed co-localization of beta-actin protein and von Willebrand factor, a specific endothelial cell marker. These results suggest that increased beta-actin expression predominantly localized in cardiac interstitial cells, including endothelial cells. The increased beta-actin could be due to either proliferation of the interstitial cells or upregulation of the beta-actin gene., (Copyright 1999 Academic Press.)

This study examined whether alterations in myocardial creatine kinase (CK) kinetics and high-energy phosphate (HEP) levels occur in postinfarction left ventricular remodeling (LVR). Myocardial HEP and CK kinetics were examined in 19 pigs 6 wk after myocardial infarction was produced by left circumflex coronary artery ligation, and the results were compared with those from 9 normal pigs. Blood flow (microspheres), oxygen consumption (MVO2), HEP levels [31P magnetic resonance spectroscopy (MRS)], and CK kinetics (31P MRS) were measured in myocardium remote from the infarct under basal conditions and during dobutamine infusion (20 micrograms. kg-1. min-1 iv). Six of the pigs with LVR had overt congestive heart failure (CHF) at the time of study. Under basal conditions, creatine phosphate (CrP)-to-ATP ratios were lower in all transmural layers of hearts with CHF and in the subendocardium of LVR hearts than in normal hearts (P < 0.05). Myocardial ATP (biopsy) was significantly decreased in hearts with CHF. The CK forward rate constant was lower (P < 0.05) in the CHF group (0.21 +/- 0.03 s-1) than in LVR (0.38 +/- 0.04 s-1) or normal groups (0.41 +/- 0.03 s-1); CK forward flux rates in CHF, LVR, and normal groups were 6.4 +/- 2.3, 14.3 +/- 2.1, and 20.3 +/- 2.4 micromol. g-1. s-1, respectively (P < 0.05, CHF vs. LVR and LVR vs. normal). Dobutamine caused doubling of the rate-pressure product in the LVR and normal groups, whereas CHF hearts failed to respond to dobutamine. CK flux rates did not change during dobutamine in any group. The ratios of CK flux to ATP synthesis (from MVO2) under baseline conditions were 10.9 +/- 1.2, 8. 03 +/- 0.9, and 3.86 +/- 0.5 for normal, LVR, and CHF hearts, respectively (each P < 0.05); during dobutamine, this ratio decreased to 3.73 +/- 0.5, 2.58 +/- 0.4, and 2.78 +/- 0.5, respectively (P = not significant among groups). These data demonstrate that CK flux rates are decreased in hearts with postinfarction LVR, but this change does not limit the response to dobutamine. In hearts with end-stage CHF, the changes in HEP and CK flux are more marked. These changes could contribute to the decreased responsiveness of these hearts to dobutamine.

Delayed reperfusion has a beneficial effect on prognosis, independent of infarct size. One potential mechanism to explain this observation may be an effect on infarct healing. In this study, the impact of delayed reperfusion on two aspects of the healing process was examined, the activity of matrix metalloproteinase (MMP) enzymes and the expression of fibronectin (FN) mRNA. The rat model of coronary artery ligation was used and rats were randomly assigned to delayed reperfusion (150 min following coronary ligation) or permanent ligation. Animals were subsequently killed 1, 2, 3 and 7 days following infarction. Infarct tissue was harvested for MMP activity (zymography), FN mRNA (RNase protection analysis) and protein (immunofluorescence microscopy and Western analysis), and collagen content (hydroxyproline concentration). Infarction produced marked activation of MMP-1, -2, and -9. Reperfusion significantly attenuated the activity of these enzymes (approximately 50% reduction in MMP-1, P=0.03 and ;60% reduction in MMP-2 at 7 days, P=0.001; approximately 55% reduction in MMP-9 at 24 h and 84% reduction at 48 h, P=0.01 and 0.002, respectively). Delayed reperfusion also produced a trend toward a greater increase in FN mRNA 24 h following infarction and immunofluorescent staining suggested the presence of more FN protein at this point. These data demonstrate that delayed reperfusion alters matrix metalloproteinase activity and fibronectin mRNA expression in the infarct zone. The impact of these changes on infarct healing and their association with the improved prognosis of a patent infarct vessel following infarction will require further study., (Copyright 1997 Academic Press Limited.)

Beta-actin, a cytoskeletal protein important in the maintenance of cytoarchitecture, has long been thought to be expressed constitutively in myocardial tissue. As such, beta-actin mRNA has been used as a control gene in a wide range of experiments. However, we have uncovered consistent changes in beta-actin mRNA expression in canine myocardium remodeling as a result of insult to the left ventricle. The experimental canine models used were either DC shock damage to the left ventricle or volume overload resulting from severe mitral regurgitation. The remodeling process in both canine models is characterized by an increase in left ventricular mass. PCR amplification using primers designed to selectively amplify the 3' end and a portion of the 3' untranslated region of beta-actin mRNA resulted in the generation of a 297 base pair product predominant only in normal canine myocardium and a 472 base pair product that became increasingly prominent from 1 to 30 days after DC shock damage to the left ventricle and from 10 to 90 days after creation of mitral regurgitation. Northern analysis showed a three-fold increase in beta-actin mRNA after either DC shock or creation of mitral regurgitation. Western analysis revealed an early increase in beta-actin protein followed by an apparent decrease to below baseline levels. These observations suggest that changes in beta-actin mRNA expression accompany the structural alterations that occur in response to myocardial damage. Whether or not the changes in beta-actin mRNA expression play a role in mediating these structural alterations remains to be determined.

The heart is made up of many different cell types, including myocytes, fibroblasts and vascular cells. The cardiac myocyte, although not likely to divide, may respond to gross organ injury by a process of growth or hypertrophy. Cellular hypertrophy, though a normal biological adaptation, has the potential to contribute to the change in the shape and the size of the heart, such as occurs in chronic heart failure. We are now just beginning to understand the signals and early pathways involved in the cardiac myocyte growth response, some of which are reviewed herein.