Bioresorbable drug-eluting scaffolds for treatment of vascular disease.

Expert Opinion on Drug Delivery

ISSN: 1742-5247 (Print) 1744-7593 (Online) Journal homepage: http://www.tandfonline.com/loi/iedd20

Bioresorbable drug-eluting scaffolds for treatment of vascular disease Pannipa Suwannasom MD, Yohei Sotomi MD, Hiroki Tateishi MD, PhD., Erhan Tenekecioglu MD, Yaping Zeng MD, PhD, Robin P. Kraak MD, Joanna J. Wykrzykowska MD, PhD, Robbert J. de Winter MD, PhD, Patrick W Serruys MD, PhD & Yoshinobu Onuma MD, PhD To cite this article: Pannipa Suwannasom MD, Yohei Sotomi MD, Hiroki Tateishi MD, PhD., Erhan Tenekecioglu MD, Yaping Zeng MD, PhD, Robin P. Kraak MD, Joanna J. Wykrzykowska MD, PhD, Robbert J. de Winter MD, PhD, Patrick W Serruys MD, PhD & Yoshinobu Onuma MD, PhD (2016): Bioresorbable drug-eluting scaffolds for treatment of vascular disease, Expert Opinion on Drug Delivery, DOI: 10.1517/17425247.2016.1153062 To link to this article: http://dx.doi.org/10.1517/17425247.2016.1153062

Accepted author version posted online: 10 Feb 2016.

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Date: 22 February 2016, At: 19:46

Publisher: Taylor & Francis Journal: Expert Opinion on Drug Delivery DOI: 10.1517/17425247.2016.1153062 REVIEW Bioresorbable drug-eluting scaffolds for treatment of vascular disease

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Pannipa Suwannasom1,2,3MD;Yohei Sotomi1,MD;Hiroki Tateishi2,MD, PhD; Erhan Tenekecioglu2, MD; Yaping Zeng2, MD, PhD; Robin P. Kraak1, MD; Joanna J. Wykrzykowska1, MD, PhD; Robbert J.de Winter1, MD, PhD; Patrick W Serruys4, MD, PhD; Yoshinobu Onuma2*, MD, PhD

1. AMC Heartcenter, Academic Medical Center, University of Amsterdam, Amsterdam, The Netherlands. 2. ThoraxCenter, Erasmus Medical Center, Rotterdam, The Netherlands. 3. Northern Region Heart Center, Faculty of Medicine, Chiang Mai University, Chiang Mai, Thailand 4. International Centre for Circulatory Health, NHLI, Imperial College London, London, United Kingdom.

Abstract Introduction: Theoretical advantages of fully bioresorbable scaffold (BRS) stem from transient vessel support without rigid caging. Therefore, it could reduce long-term adverse events associated with the presence of foreign materials. Areas covered: This article will provide an overview of: drug-eluting BRS for various applications in the treatment of vascular disease; The mechanisms of active agent release from


such scaffolds; currently available drug-eluting BRS and their future applications are also discussed. Expert opinion: The current BRS have been developed in order to achieve optimal vascular patency while providing long-term safety. The clinical efficacy and safety of BRS in coronary treatment have been reported as equal to that of the current metallic drug eluting stents in simple lesions. The application of BRS can potentially be expanded to other vascular beds. The research in bioengineering for the appropriate materials should not only focus on biocompatibility but also should be tailored according to the sites of implantation, which may require different strength and supporting period. The ultimate goal in this field is to develop a biocompatible device that provides equivalent and complementary therapy to other devices, and is able to disappear when the mechanical support and drug delivery are no longer required. Keywords: Bioresorbable scaffold , drug-eluting, magnesium, polymer

Article highlights box •

BRS provides temporary drug elution and scaffolding until the vessel has healed.

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Sirolimus-derivative agents developed through modifications on the carbon C40 of the macrocyclic ring except novolimus and myolimus.

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The polymer composition, coating thickness, and stent design greatly influence the drug


release behavior. •

The most dominant release mechanism of drug incorporated in DES is diffusion-based drug delivery.

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The current BRSs are composed of either a polymer or bioresorbable metal alloy.

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Different materials have different chemical compositions, mechanical properties, and therefore bioabsorption times.

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The BRS application in vasculature has expanded beyond treatment of coronary disease, such as congenital heart disease and peripheral vascular disease.

1. Introduction

The first reference to stent used in cardiovascular literature comes from Dotter in 1983[1]. At that time, Dotter reported the results of transluminal expandable Nitinol Stent Grafting in peripheral vascular disease. Four years later, the first report of the clinical use of coronary stents was published[2], followed by the landmarks BENESTENT and STRESS trials[3,4]. This technology has provided a solution to acute vessel occlusion by sealing the dissection flaps and


preventing elastic recoil. The rate of subacute occlusion was reduced to 1.5%, making emergency bypass surgery a rare occurrence. Despite the use of stent, the restenosis rates of bare metal stent were still high (22% at 7 months), and the neointimal hyperplasia inside the stent was even more prominent than with angioplasty, necessitating repeat treatment in large proportion of patients.[3] In-stent restenosis is caused by the migration and proliferation of vascular smooth muscle cells (SMCs) in response to the trauma to the vessel wall [5]. To circumvent the problem of in-stent restenosis, drug eluting stents (DES) have been introduced in clinical practice to prevent neointimal hyperplasia by delivering antiproliferative agents to the lesion.[7,8] Both large scale randomised trials and all-comer registries showed excellent results in terms of reducing the need for repeat revascularization. However, the early enthusiasm has been tempered in recent years following widespread concerns regarding the increased risk of late and very late stent thrombosis.[9-13] This problem has been now largely solved with the development of metallic stents with thin struts covered by a thin biodegradable polymer or metallic DES without polymer to minimize stent thrombosis. Considering the serious and often debilitating consequences of stent thrombosis, bioresorbable technology has been developed to eliminate the presence of the permanent foreign material. Such bioresorbale device further

eliminates deleterious caging effects of the permanent metallic endoluminal prosthesis, namely their permanent effects on vessel geometry, wall shear stress and cell signaling [14]. The novel technology of fully bioresorbable scaffold (BRS) offers the possibility of transient scaffolding of the vessel to prevent acute vessel closure and recoil whilst also transiently eluting an antiproliferative drug to counteract the constrictive remodeling and excessive neointimal hyperplasia[15]. The BRS application in vasculature has expanded beyond treatment of coronary


disease. The scaffold has been applied as vasculature support in congenital heart disease. It is also being tested as a reservoir for local drug delivery in cancer treatment and gene therapy. This article will provide 1) an overview of landscape of drug-eluting BRS for various applications in vasculature; 2) mechanisms of active agent release from a scaffold for treatment; 3) currently available drug-eluting BRS in vasculature that acquired CE mark, those under clinical investigation and those in pre-clinical phase trials. 2. Theoretical concept of bioresorbable devices in vasculature Theoretical advantages of BRS stem from transient vessel support without rigid caging. The potential benefits of BRS over current metallic DES technology proposed by authors are summarized as follows: 2.1. A reduction in long-term adverse events from permanent materials. As drug elution and scaffolding are temporary until the vessel has healed, no foreign material potentially triggering very late stent thrombosis (such as non-endothelialised struts and drug polymers) [16] could persist in the long-term. 2.2. The removal, through bioresorption, of the stented vessel’s rigid caging.

This can facilitate the return of vasomotion, physiological cyclic shear stress, late luminal enlargement and late expansive remodeling. Furthermore, this might also reduce the problems of jailing the ostium of side branches as seen with permanent metallic stent struts (non-apposed in front of the side-branch struts). 2.3. Suitability for future treatment options. The treatment of complex multi-vessel disease frequently results in the use of multiple long


DESs, so called “full metal jacket” stenting. In such cases, repeat revascularization – either percutaneous or surgical, is potentially challenging because of the metallic caging of distal runoffs with previously implanted stents. The use of a BRS implies no restriction to future percutaneous or surgical revascularization. 2.4. Allowing the use of non-invasive imaging techniques such as multislice computed tomographic (MSCT) angiography or magnetic resonance imaging (MRI) for follow-up. Presently, metallic stents can cause a blooming effect with these imaging modalities making interpretation more difficult.[17] The polymeric scaffold should not restrict the use of MSCT or MRI as it is non-metallic. Even with metallic BRS such as magnesium or iron, MSCT and MRI can be efficiently used once bioresorption is completed. MSCT has provided reliable assessment of the angiographic results up to 3 to 5 years after translucent scaffold implantation. [18,19] 2.5. Reservoir for the local delivery of drugs. Since the duration of bioresorption is modifiable, according to the type of polymers/co-polymers, a fine-tuned elution of multiple drugs can potentially be achieved (e.g. early elution of antiproliferative agent from a coated polymer and chronic elution of anti-inflammatory or other agent from the backbone polymer).

2.6. Relief of anxiety of implanted foreign materials The use of BRS eliminates patient’s concern about having an implant in their bodies for the rest of their lives.[22] 2.7. Pediatric application Congenital heart disease (e.g. pulmonary stenosis, aortic coarctation, aortopulmonary collaterals,


atrial septal defect) can be potentially treated with BRS.[23-26] After bioresorption, scaffolded arteries can adapt a natural growth pattern. However, this indication for the treatment is still offlabel, and the long term results need to be monitored. 2.8. Peripheral vascular disease BRS may prevent the late complications related to stent placement such as strut fracture from high stresses due to complex vascular motion[27]. BRS may provide a superior flexibility and a vessel support only for the time that is needed. 3. Drug release control from bioresobable drug-eluting scaffold BRS can keep the vessel lumen patent and simultaneously serve as a drug/protein delivery platform. However, most drugs and all proteins are destroyed when exposed to high melting temperature. Certain drugs, such as steroids, can be incorporated in small drug quantities into PLLA fiber during the melting process without compromising the mechanical properties of the scaffold.[28] In order to make a BRS carry adequate amount of anti-proliferative agent, coating layer controlling drug release is added to the scaffold backbone. There are three main release mechanisms for drugs incorporated into DES: 1) diffusion-based drug delivery: the most common release mechanism for drugs incorporated into DES[29]; 2) erosion-based drug

delivery: drug is released due to the polymer degradation and erosion from coating.[30]; 3) dissolution-based delivery: the drug particles may either be incorporated into a polymer or coated directly onto the device surface.[31] Dissolution is mostly used in polymer-free metallic DES. The current drug-eluting BRS are coated with biodegradable polymers, therefore drug release kinetics depend on the kinetics of polymer degradation time. The polymer composition, coating thickness, and stent design greatly influence the drug release


behavior. The total achievable drug load and the prolongation of release depend on the coating thickness and the integrity of polymer during device expansion. Hydrophilic characteristics of the polymer promote biocompatibility while the hydrophobic characteristics control drug elution.[32] Prolongation of drug release and increase of drug load remain to be a challenge for BRS technologies. BRS platform might allow the incorporation of the drugs into the entire stent or scaffold made up of polymers or metal alloy. The drug release mechanism might either be the diffusion control or the stent degradation or the combination of both processes.[29] 4. Drugs used in coronary BRS The primary aim of loading a drug on BRS is to prevent neointimal hyperplasia, therefore, the anti-proliferative agents which retard hyper-proliferation and migration of SMCs, have antiinflammatory and anti-thrombogenic characteristics are the major candidates for DES application. Several immunosuppressive, antiproliferative drugs or even statins[33,34] have been tested. However, only two classes of antiproliferative agents have proven their efficacies in preventing neointimal hyperplasia and in-stent restenosis: paclitaxel and the rapamycin analogs (limus family). The current family of drug-eluting BRS can be classified into; i) limus family elution from biodegradable coating; ii) non-limus drug elution from biodegradable coating.

4.1Mechanism of action of antiproliferative drug available in current BRS 4.1.1limus family elution from biodegradable coating There are eight limus family compounds being used in coronary metallic DES. These compounds target either the mammalian target of rapamycin (mTOR) (sirolimus, everolimus, zotarolimus, biolimus A9, myolimus and novolimus) or calcineurin (tacrolimus and pimecrolimus).[35] Nevertheless, only mTOR inhibitors have been tested in BRS. Amongst six of mTOR inhibitors,


there are only three substances: sirolimus, everolimus and novolimus, which are being used in the current BRS platforms.

1. Sirolimus is a natural macrocyclic lactone with potent immunosuppressive and antiproliferative properties; it is also known as Rapamycin. It is synthesized by the bacterium Streptomyces hygroscopicus.[38] Initially, it was developed as an antifungal agent, but was soon discovered of immunosuppressive activity and antitumor activity. It has also allowed for a positive turn in coronary artery stenosis treatment. The chemical structure of sirolimus and its analogues are shown in figure 1, All mTOR inhibitors share an almost identical lipophilic chemical structure and bind to their major cytosolic FK-506 binding protein-12 (FKBP12) forming a complex which subsequently inhibits the mTOR. mTOR is a serine/threonine kinase which is a member of the phosphatidylinositol 3-kinase-(PI3K) related protein kinase (PIKKs) family. mTORC1 is involved with critical steps of the cell cycle, including the checkpoints that govern DNA damage and repair.[39] Inhibition of mTORC1 induces cell-cycle arrest at the juncture of the G1 and S phase[40],resulting in inhibition of SMCs proliferation [41] and migration[42]. Therefore, the mechanism of action of mTOR inhibitor is cytostatic rather than cytotoxic (see Figure 2).

Sirolimus includes two separated moieties, the TOR-binding and the FKBP12-binding regions. (see figure 1a) The formation of a rapamycin–FKBP12 complex binds directly to mTOR and inhibits the mTOR function and the mTOR-mediated signaling network.[6] Other anti-restenotic properties of Sirolimus include the inhibition of total protein and collagen synthesis involved in extracellular matrix formation and promoting a contractile rather than a proliferative phenotype.[43]


2.Everolimus is a hydroxyethyl ether derivative of sirolimus, with a 2-hydroxyethyl group in carbon C40. (see figure 1a) Everolimus has immunosuppressive potential, which relies on preventing lymphocyte and SMC proliferation mediated by inflammatory cytokines and growth factors.[44] A stent-based delivery of everolimus was found to selectively clear macrophages in rabbit atherosclerotic plaques by autophagy.[45] Due to its molecular and chemical structure, the lipophilic properties of everolimus are greater compared to sirolimus, leading to a more rapid absorption into the arterial wall[44] and lower half-life than sirolimus.[35] 3. Myolimus is a macrocyclic lactone which is produced by replacement of the oxygen on C32 of the macrocyclic ring (see figure 1a), and has a comparable potency, in terms of inhibition of SMCs, to sirolimus.[46] 4.Novolimus is a macrocyclic lactone, which has been developed by removal of a methyl-group from carbon C16. Notably, this differs from the other macrocyclic lactone agents that are used in DES, which have been developed through modifications on the carbon C40 of the macrocyclic ring (see figure 1a). Nevertheless, in a similar fashion to these other agents in limus family, Novolimus has been shown in in vitro studies to have a high potency to inhibit human SMCs, comparable to that of sirolimus.[47,48]

4.1.2 Non-limus drug elution from biodegradable coating. Paclitaxel is a lipophilic molecule with potent anti-proliferative and anti-migratory activity. The drug binds specifically to the β-tubulin subunit of microtubules and appears to antagonize the disassembly of microtubules, and thus aberrant structures derived from microtubules accumulate in the mitotic phase of the cell cycle. Paclitaxel impacts primarily the M phase of the cell cycle, inhibiting growth factor-induced DNA synthesis and cell proliferation, and leads to apoptosis or


cell death. Compared with the limus family, the mode of action of paclitaxel is primarily cytotoxic It has narrow toxic-therapeutic window and has hydrophobic properties.[38] Paclitaxel has been used in the first generation of magnesium BRS before changing to sirolimus in the new generation. 5. Landscape of materials and technologies to create bioresorbable scaffold The key mechanical traits for candidate materials for coronary indications include: high elastic moduli to impart radial stiffness, large break strains to impart the ability to withstand deformations from the crimped to expanded states, and low yield strains to reduce the amount of recoil and over-inflation necessary to achieve the target deployment. Stent developers look to increase stent strut dimensions to compensate for mechanical shortcomings of bioresorbable materials. As the thickness of these struts increases, strain levels imposed on the material increases proportionally. The current BRSs are composed of either a polymer or bioresorbable metal alloy. Numerous different polymers are available, each with different chemical compositions, mechanical properties, and subsequently bioresorption times. The mechanical properties of material being tested as a BRS platform are summarized in table 1.

6. Currently available drug-eluting BRS in vascular disease 6.1. Drug-eluting BRS in coronary artery disease This section is focused on currently available drug-eluting BRS that were 1. clinically successful and acquired CE mark, 2. Are under clinical investigation or 3. in pre-clinical phase. A short summary of first in man trial results of each platform is tabulated in Table 3. 6.1.1 Coronary drug-eluting BRS with an acquired CE mark.


6.1.1.1 Absorb BVS 1.1 Absorb BVS backbone (Abbott Vascular, Santa Clara, California, USA) is made of semicrystalline polymer called Poly-L-lactic acid (PLLA).[63] The thickness of the strut is 156 µm. The struts are either directly joined or linked by straight bridges. Because the devices are radiolucent under fluoroscopy, two adjacent cylindrical radio-opaque platinum markers have been incorporated in the proximal and distal edges of the polymeric device. The coating consists of poly D,L-lactide (PDLLA), which is a random copolymer of D- and L-lactic acid with lower crystallinity than the BVS backbone and fully bioresorbable. The coating contains and controls the release of everolimus, with a coating-to-drug ratio of 1:1.[63,64] The second- generation Absorb BVS 1.1 claims to elute 75% of loaded everolimus within 30 days and with the same dose density (100 μg/cm2) as the cobalt–chromium everolimus-coated Xience V coronary stent. The release kinetics of everolimus in AbsorbTM are purely diffusion-controlled.[35] The diffusion follows an inherently Fickian first-order release behavior proportional to square-root of time, according to the well-known relationship from Higuchi.[65] The bioresorption process of PLLA is as follows: First, hydration of the polymer occurs. The semicrystalline property of polylactide allows water to penetrate deeply inside the implant. Second, depolymerisation by hydrolysis is observed and reduction in molecular weight takes

place. The latter starts from the time of implantation, gradually progresses and is completed at 36-months. Thirdly, polymer fragmentation into segments of low-weight polymer due to the scission of amorphous tie chains linking the crystalline regions, resulting in subsequent gradual loss of the radial strength, starts from 6-month after implantation and is completed at 12-month after implantation. Final process is assimilation or dissolution of monomers. Phagocytes can assimilate small particles less than 2 µm and convert them to soluble monomeric anions. Lastly,


the soluble monomer (e.g., L-lactate) is changed into pyruvate, which eventually enters the Krebs cycle and is further converted into carbon dioxide and water, eliminated by the lungs and kidneys. [49] To date, Absorb BVS is the most extensively studied BRS. In the ABSORB-III randomized trial, Absorb BVS was non-inferior to Xience for target-lesion failure at 1 year.[66] This observation is also supported by a patient level meta-analysis involving 3,738 patients enrolled into the ABSORB II, ABSORB III, ABSORB JAPAN and ABSORB CHINA, EVERBIO-II and TROFIII randomized trials.[67] These trials included patients with relatively simple lesions. Performance of this device in all-comers patient population is being studied in the AIDA trial, which is nearing enrollment completion. Its primary endpoint of TVF will be reported in 2 years[68]. 6.1.1.2 DESolve DESolve® (Elixir Medical, Sunnyvale, CA) also has a PLLA backbone with antiproliferative drug, novolimus which is an active metabolite of sirolimus. There are two platinum markers at each end of the scaffold. The coating-polymer is a biodegradable polylactide-based polymer. The drug-polymer matrix is applied to the surface of the stent, without a primer polymer coating underneath, using a proprietary spray resulting in a coating thickness of 24 months). The fast resorption of magnesium was considered as one of the reasons of failure in the PROGRESS trial where the late recoil of the device was a prominent etiology of restenosis. The second and the thirdgeneration of magnesium BRS therefore use polymeric coating to slow down the biodegradation by limiting access of water to magnesium and to enable longer drug release. Despite the inherent mechanical advantage, the current magnesium scaffold still has a thick strut (150 µm) just as polymeric BRS. If next generation magnesium BRS should succeed to make the struts thinner and stronger, it might offer some advantage of the polymeric BRS. According to the European task force recommendation, the following additional analyses are required for non-clinical evaluation of BRS; i) bench testing that should be performed through time of significant mass loss; ii) biochemical analysis of degradation products in BRS is mandatory; and iii) critical time points of follow-up should cover complete resorption as determined by histopathology. In clinical assessment, BRS should be directly compared with a CE-approved metallic DES or with other CE-approved bioresorbable coronary stents. The indication for BRS is not only limited to the field of coronary artery disease, it could also expanded to peripheral vascular disease and congenital heart abnormalities. Therefore, the

design, material and degradation time of the “ideal” BRS drug-eluting vascular stent would also depend on the implantation site since the need for support is different. The research on BRS in non-coronary applications is still in its infancy, however, the dedicated devices for the particular indications with improved and optimized mechanical properties are being developed.


Declaration of Interest P Suwannasom has received a grant from Northern region heart center, Chiang Mai University. Y Sotomi has received a grant from the Fukuda Memorial Foundation for Medical Research. E Tenekecioglu has received a grant from TUBITAK (The Scientific and Technological Research Council of Turkey). The institution of RJ de Winter and JJ Wykrzykowska receives a research grant from Abbott Vascular. PW Serruys and Y Onuma are members of the Advisory Board for Abbott Vascular. The authors have no other relevant affiliations or financial involvement with any organization or entity with a financial interest in or financial conflict with the subject matter or materials discussed in the manuscript apart from those disclosed.

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Table 1 Mechanical properties and degradation time for different polymers.


Polymer composition Poly(L-lactide) Poly (DL-lactide) Poly (glycolide) 50/50 DL-lactide/glycolide 82/18 L-lactide/glycolide 70/30 L-Lactide/ε- caprolactone 78/22 L-lactide/ poly(4hydroxybutyrate Magnesium alloy Iron Cobalt chromium Stainless steel 316L Nitinol

Tensile modulus of elasticity (Gpa) 3.1-3.7 3.1-3.7 6.5-7.0 3.4-3.8 3.3-3.5 0.02-0.04 1.0

Tensile strength (Mpa) 60-70 45-55 90-110 40-50 60-70 18-22 36

Elongation at break (%) 2-6 2-6 1-2 1-4 2-6 >100 126

Degradation time (months) >24 12-6 6-12 1-2 12-18 12-24 >12

40-45 200 210-235 193 45

220-330 300 1449 668 700-1100

2-20 25 〜40 40+ 10-20

1-3 >48 Biostable Biostable Biostable

Adapted from Onuma Y et al.[65]

Tensile modulus is the tendency of an object to deform along an axis when opposing forces are applied along that axis. Tensile strength is defined as

the maximum stress that a material can withstand without significant contraction in cross-section while being stretched.

Abbreviation: Gpa = Giga pascal, Mpa = Mega pascal

41

Table 2 Drug release characteristics of current bioresorbable drug-eluting scaffold


Drug

Stent name (manufacturer)

Stent platform

Paclitaxel

DREAMS 1.0 (Biotronik)

WE43 alloy, 93% Mg and 7% rare earth elements

Sirolimus

DREAM 2G (Biotronik)

WE43 alloy, 93% Mg and 7% rare earth elements

Strut thickness , µm 120

Coating material

Coating thickness

Radial support

Resorption time

Reported release profile

Drug dose

Status

Site of implantation

ref

PLGA

1 µm

3–6 months

9 months

Controlled release in 3 months, both paclitaxel release and magnesium degradation completed

0.07 μg/mm2

Discontinued

Coronary

[106]

150

PLLA

1 µm

3–6 months

9 months

Over 3 to 6 months

1.4 μg/mm2

Clinical trials

Coronary

[107]

ReZolve (Reva Medical)

PTD-PC

115-230

--

--

4–6 months

4–6 months

--

80 µg

Discontinued

Coronary

[108]

Fantom (Reva Medical)

PTD-PC

125

Bioresorbable polymer

--

--

within 3 years

--

115 µg

Clinical trials

Coronary

[109]

8.3 µg/mm

Discontinued

Coronary

[110]

IDEAL BTI 1st generation (Xenogenics)

Poly-lactic anhydride containing 2 salicylic acid molecules linked to 1 sebacic acid molecule

200 2nd gen 175

SA/AA

--

3 months

9-12 months

XINSORB (HuaAn Biotech)

PLLA

160

PDLLA + PLLA

--

--

2 to 3 years

About 80% of sirolimus eluted from the polymer in 28 days ex vivo

8 µg/mm

Clinical trials

Coronary

[75,1 11]

MIRAGE BRMS (Manli)

PLLA

PLLA

--

--

14 months

--

--

Clinical trials

Coronary

[112]

FORTITUDE (Amaranth)

PLLA

125 for diameter 3.0 mm and 150 for 3.5 mm 120

Bioresorbable polymer

--

3–6 months

3–6 months

--

--

Clinical trials

Coronary

[113]

NeoVas (Lepu Medical)

PLLA

180

PDLA

--

--

24 months

--

15.3 μg/mm

Clinical trials

Coronary

[114]

Microport BRS (Microport)

PLLA

100-125

PDLLA

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