Estrogen-Eluting Stents

Abstract

Coronary stenting is routinely utilized to treat symptomatic obstructive coronary artery disease. However, the efficacy of bare metal coronary stents has been historically limited by restenosis, which is primarily due to excessive neointima formation. Drug-eluting stents (DES) are composed of a stainless steel backbone encompassed by a polymer in which a variety of drugs that inhibit smooth muscle cell proliferation and excessive neointima formation are incorporated. DES have significantly reduced the incidence of restenosis but are also associated with a small (~0.5% per year) but significant risk of late stent thrombosis. In that regard, estrogen-eluting stents have also undergone clinical evaluation in reducing restenosis with the additional potential benefit of enhancing reendothelialization of the stent surface to reduce stent thrombosis. Estrogen directly promotes vasodilatation, enhances endothelial healing, and prevents smooth muscle cell migration and proliferation. Due to these mechanisms, estrogen has been postulated to reduce neointimal hyperplasia without delaying endothelial healing. In animal studies, estrogen treatment was effective in decreasing neointimal hyperplasia after both balloon angioplasty and stenting regardless of the method of drug delivery. The first uncontrolled human study using estrogen-coated stents demonstrated acceptable efficacy in reducing late lumen loss. However, subsequent randomized clinical trials did not show superiority of estrogen-eluting stents over bare metal stents or DES. Further studies are required to determine optimal dose and method of estrogen delivery with coronary stenting and whether this approach will be a viable alternative to the current DES armamentarium.

Effects of Estrogens on Blood Vessels

Various cardioprotective properties of estrogens have been reported for decades [1]. One major beneficial effect is the improvement in the lipid profile with reduction of total and low-density lipoprotein cholesterol and increases in high-density lipoprotein cholesterol in postmenopausal women [2, 3]. Furthermore, in a recent study of 27,736 women, estrogen replacement was associated with significantly lower levels of lipoprotein(a) [4]. Estrogen also reduces fibrinogen and plasminogen activator inhibitor 1 levels, suggesting that it may possess enhanced fibrinolytic potential [5, 6]. However, in the randomized, double-blind, placebo-controlled Heart and Estrogen/progestin Replacement Study trial testing the efficacy and safety of estrogen plus progestin therapy for prevention of recurrent coronary heart disease (CHD) events in women, hormone replacement therapy did not reduce the incidence of CHD [7]. Unexpectedly, it did significantly increase the incidence of thromboembolic events compared to placebo.

Balloon angioplasty and stent placement routinely result in almost complete loss of the endothelial surface overlying the injured area. Over 1–6 months following the procedure, reendothelialization occurs by islets of endothelial cells dividing and filling in the gags over the injured subendothelial surface, which is an important factor in the recovery of the vessel wall from vascular injury [8]. This is particularly relevant in DES, where reendothelialization can be delayed or even prevented altogether, resulting in potential adverse effects [9]. Rapid reendothelialization prevents various unfavorable processes of vessel healing like smooth muscle cell (SMC) migration, excessive neointimal growth, and endothelial dysfunction. Estrogen promotes reendothelialization by enhancing vascular endothelial growth factor gene expression [10–12] and directly increases synthesis of nitric oxide (NO) with resultant vasodilatory effects and inhibition of SMC proliferation [1].

Rationale for Development of Estrogen-Eluting Stents

Intracoronary stenting is widely used for the treatment of obstructive coronary artery disease. Although stenting reduces the restenosis rate compared to balloon angioplasty [13, 14], neointimal proliferation after bare metal stenting still limits its efficacy. Endothelial cells control some aspects of the growth of SMC by release of NO, which has a growth-inhibitory effect, and blocks SMC which from circulating growth factors and secreting matrix proteins and proteoglycans. Following coronary stenting, the neointima generated is generally proportional to the degree of endothelial damage [8, 15]. Rapid endothelialization can prevent overgrowth of neointima, a major mechanism of in-stent restenosis. Therefore, promotion of endothelialization after stenting could be helpful in limiting in-stent restenosis.

DES have significantly reduced the rate of restenosis and subsequent target lesion revascularization compared to bare metal stents [16, 17]. The current formulations of DES are composed of stainless steel or cobalt chromium struts to which is attached a nondissolvable polymer imbedded with a variety of lipophilic drugs from the limus family (sirolimus, everolimus, zotarolimus, biolimus) or paclitaxel, which are either cytostatic or cytotoxic to SMC. These effects result in significant inhibition of SMC proliferation and ultimately in a reduction of excessive neointima formation. However, these drugs may also interfere with the normal healing mechanism of endothelialization after stent placement which may lead to increased risk of late stent thrombosis [18–21]. Unlike the drugs used in DES, estrogen could prevent restenosis by promoting endothelial healing and preventing SMC proliferation. Therefore, several groups have generated estrogen-eluting stents for the prevention of restenosis. A description of an example of estrogen-eluting stents is shown in Fig. 1 [22]. The ISAR stent platform can deliver drugs such as rapamycin and estrogen. With its microporous surface, estrogen can be attached to the stent and released slowly.

Fig. 1.

The unique microporous surface of the ISAR stent platform allows for drug deposition and retards drug release without obligate application of a polymer. The roughness of the stent surface as determined by perthometer is 1.96 ± 0.21 µm. Various kinds of drugs or drug combinations including rapamycin and estrogen can be loaded on ISAR stent with the same mechanism. a Uncoated microporous stent under a magnification of ×400 illustrating the rough surface achieved by mechanical treatment. The open-cell stent design is illustrated on the small photograph on the upper left corner. b Expanded microporous stent coated with 0.5% rapamycin solution (gold-sputtered to improve visibility, ×200), visually highlighting uniform drug distribution across the entire stent surface. The surface of a noncoated (c) and rapamycin-coated (d) microporous stent at a magnification of ×1,000. Reprinted with permission from Wessely et al. [21]

Animal Studies with Estrogen Stents

In 1981, Beldekas et al. [23] reported that bovine aortic SMC cultured with 17-β-estradiol (17βE) had reduced production of collagen. Chandrasekar et al. [24] showed that local delivery of 600 µg 17βE reduced both the proliferative activity of SMC as well as neointimal hyperplasia after balloon injury of porcine coronary arteries [25]. New et al. [26] took this a step further by using a phosphorylcholine (PC)-coated estrogen-eluting stent and demonstrated a reduction in neointimal hyperplasia without delaying reendothelialization. A recent study using a similar porcine model [27] showed that intracoronary estrogen delivery using the InfusaSleeve catheter decreased percent stenosis by 47% (30 → 16%) in balloon group and 23% (71 → 55%) in stent group. In addition, type 1 collagen significantly correlated with the vessel wall injury scale and was reduced in the 17βE group. Overall, although publication bias cannot be ruled out, these experimental studies suggested a strong rationale for moving forward and assessing the role of estrogen-eluting stents in patients. It is also to be emphasized that many experimental studies are positive in animal models of restenosis, such as the rat carotid artery, rabbit iliac, and pig coronary arteries, but that the vast majority of compounds used in these models have not been successful in clinical trials.

Human Studies with Estrogen Stents

Table 1 describes the clinical studies evaluating estrogen coated stents. The first human study evaluating an estrogen-coated stent used the BiodivYsio™ stent, where 17βE was loaded onto the stent just prior to insertion into the patients by dipping it in an estrogen solution. The BiodivYsio™ stent is a stainless steel stent coated with phosphorylcholine, which is present on phospholipids on the surface of cell membranes, to presumably optimize biocompatibility, although this has not been definitively demonstrated clinically. The Estrogen And Stents To Eliminate Restenosis (EASTER) trial [28] was a single-center study of 30 patient study in which short (<18 mm), single, de novo lesions were treated. In this initial feasibility study, the number of patients was small; there was no control group; instead, each patient was used as their own control. With this version of the stent, drug was released for only the first 24 h. Manual drug-loading methods may lack reproducibility and likely limit the amount loaded onto the stent and also result in rapid loss of estrogen from the stent once implanted in the coronary artery.

Table 1.

Summary of clinical trials on estrogen-eluting stents

Author	Year	No.	Duration of dual antiplatelet therapy	Study design	Method of drug coating	End point	Results	Stent thrombosis
Abizaid et al. [28] (EASTER)	2004	30	60 days (clopidogrel 75 mg)	Single center, no control group	On-site coating, PC coat on BiodivYsio™ stent 2.52-μg/mm2 stent surface	12-month clinical data 6- month coronary angiography and IVUS	Good (late loss 0.54 ± 0.44 mm)	None
Airoldi et al. [30]	2005	108	12 weeks (ticlopidine 500 mg or clopidogrel 75 mg)	Multicenter randomized 17βE on PC coat vs. PC coat only	Precoated 2.52-μg/mm2 stent surface	12-month clinical data 6-month coronary angiography and IVUS	No difference in clinical and angiographic outcome	3 deaths or MI in PC coat group/no death or MI in estrogen group
Abizaid et al. [31] (ETHOS-1)	2007	95	2 months (ticlopidine 500 mg or clopidogrel 75 mg)	Randomized, double-blind, multicenter control vs. slow release vs. moderate release	Precoated 250 μg/15 mm of stent length, moderate release 50% in 1 day, slow release 50% in 8 days	6-month percent volume obstruction by IVUS, clinical outcome of 6 months	No difference in %VO/no difference in clinical outcome	Slow-release group 1 death/1 MI, control and moderate release group no death or MI
Adriaenssens et al. [32] (ISAR-PEACE)	2007	502	6 months (clopidogrel 75 mg)	Randomized rapamycin vs. estradiol plus rapamycin-eluting stent	On-site coating, none PC coat, stainless steel stent with micropore/95% RES, 60% ERES release in 1 month	Primary: six month in-stent late lumen loss, secondary: binary restenosis, TVR, death, nonfatal MI	No difference in late lumen loss and binary restenosis rate/no difference in clinical outcome	ERES 2 patients/RES 3 patients

RES rapamycin-eluting stent, ERES estrogen–rapamycin-eluting stent, IVUS intravascular ultrasound, 17βE 17-β-estradiol, PC phosphorylcholine, VO volume obstruction, MI myocardial infarction

Six-month angiographic and intravascular ultrasound (IVUS) was performed and clinical follow-up was obtained at 12 months. The 6-month late luminal loss, defined as the minimal lumen diameter (MLD) at the end of the procedure minus the MLD at follow-up (6–9 months) angiography, was 0.54 ± 0.44 mm, which is less than the reported late loss of 0.95 ± 0.61 mm with a PC-coated BiodivYsio™ stent without estrogen loading and also similar to results obtained with other bare metal stents [29]. The late loss was still greater than previously noted with the paclitaxel and sirolimus-eluting stents [16, 17]. Binary restenosis (diameter stenosis > 50%), another angiographic indicator of stent efficacy, occurred in only two patients and there were no major adverse cardiovascular events (MACE) reported at 12-month clinical follow-up. Neointimal hyperplasia as measured by IVUS was also significantly reduced compared to bare metal stents. Dual antiplatelet therapy was prescribed for only 60 days but there were no stent thromboses.

The next human trial was a randomized multicenter study in 104 patients in which preloaded 17βE-eluting PC-coated BiodivYsio™ stents were used [30]. Study inclusion and exclusion criteria were similar to the EASTER trial but longer lesions (<40 mm) in larger diameter vessels (4 mm) were treated. Dual antiplatelet therapy (ticlopidine 500 mg daily and aspirin 100 mg daily) was administered for 12 weeks. There were no significant differences between the BiodivYsio™ stent without estrogen loading and the estrogen-coated BiodivYsio™ stent in late lumen loss, binary restenosis rate, or MACE rates. Overall, this study demonstrated safety and feasibility of 17βE-eluting stents, but there was no superiority over the control group.

The estradiol-eluting stents in humans for restenosis trial (ETHOS-1) [31] performed by the same research group as the EASTER trial was a randomized multicenter study randomizing three groups of subjects: a control BiodivYsio™ stent without estrogen and two formulations of the BiodivYsio™ stent coated with 17βE in a slow versus moderate programmed-release preparation. To optimize short-term and long-term action of estrogen, approximately 50% of drug was released within 1 day in the moderate-release and 8 days in the slow-release groups, with the remainder of the drug eluted over 30 days. The estrogen dose was 240 µg/15 mm of stent length, representing the maximum dose that could be implanted on the stent. Oral clopidogrel was administered for 60 days. The main result of the study was that no differences in any efficacy measures were noted between the two groups at the 6-month angiographic and IVUS evaluation revealed

In the most recently published human study, ISAR-PEACE, the additive effect of estrogen on a rapamycin-eluting stent was evaluated [32]. To deliver the drugs, a polymer-free stainless steel stent with micropores was used. Dual antiplatelet therapy with aspirin and clopidogrel was done for 6 months. The primary end point was late lumen loss. In 250 patients, rapamycin-eluting stents (RES) were deployed and in 252 patients rapamycin plus estrogen-eluting stents (ERES) were deployed. Late lumen loss was not significantly different between the two groups (ERES 0.52 ± 0.58 mm, RES 0.51 ± 0.58 mm). The incidence of binary restenosis and stent thrombosis were not significantly different. Because an IVUS analysis was not performed, the effect of estrogen on neointima formation could not be evaluated.

Conclusions

In summary, human stent trials evaluating estrogen-eluting stents did not show any significant benefit over bare metal stents as suggested by animal studies. Although the animal models of restenosis and initial uncontrolled clinical studies were initially very promising, recent well-designed clinical trials have not show equivalence or superiority over bare metal stents or to have an additive efficacy when incorporated on existing DES. Despite theoretical vascular benefits of estrogen, no definitive explanation for the failure of estrogen-eluting stents in preventing restenosis has been provided. Based on the above studies, it is unlikely that estrogen-eluting stents will become clinically available without some new fundamental improvements in potency of estrogen compounds, elution kinetics, and/or improvements in stent design and incorporation of estrogen compounds.