Fabrication and in vitro deployment of a laser-activated shape memory polymer vascular stent
© Baer et al; licensee BioMed Central Ltd. 2007
Received: 10 May 2007
Accepted: 27 November 2007
Published: 27 November 2007
Vascular stents are small tubular scaffolds used in the treatment of arterial stenosis (narrowing of the vessel). Most vascular stents are metallic and are deployed either by balloon expansion or by self-expansion. A shape memory polymer (SMP) stent may enhance flexibility, compliance, and drug elution compared to its current metallic counterparts. The purpose of this study was to describe the fabrication of a laser-activated SMP stent and demonstrate photothermal expansion of the stent in an in vitro artery model.
A novel SMP stent was fabricated from thermoplastic polyurethane. A solid SMP tube formed by dip coating a stainless steel pin was laser-etched to create the mesh pattern of the finished stent. The stent was crimped over a fiber-optic cylindrical light diffuser coupled to an infrared diode laser. Photothermal actuation of the stent was performed in a water-filled mock artery.
At a physiological flow rate, the stent did not fully expand at the maximum laser power (8.6 W) due to convective cooling. However, under zero flow, simulating the technique of endovascular flow occlusion, complete laser actuation was achieved in the mock artery at a laser power of ~8 W.
We have shown the design and fabrication of an SMP stent and a means of light delivery for photothermal actuation. Though further studies are required to optimize the device and assess thermal tissue damage, photothermal actuation of the SMP stent was demonstrated.
Vascular stents are small tubular scaffolds used to maintain the luminal size of an artery. They are now widely used in conjunction with transluminal angioplasty in the treatment of arterial stenosis (narrowing of the vessel) to prevent acute vessel closure and late restenosis in a variety of large vessels such as coronary arteries , carotid arteries , and iliac arteries . Most stents are currently made of stainless steel, shape memory alloys (SMAs), and other metal alloys. Crimped over a catheter, they are navigated to the lesion site where they are expanded either by balloon expansion or by self-expansion. Though improvements in design and coating with drug-eluting agents have resulted in smaller, safer, and more biocompatible stents with reduced rates of restenosis , several drawbacks associated with the use of metallic stents still exist. First, metallic stents are too stiff to navigate highly tortuous vessels such as those of the neurovasculature; the need for treatment of stroke and intracranial stenosis is well known , but successful stenting with the current technology has been shown in a limited number of cases only . Second, compliance mismatch due to the stiffness of metallic stents at the arterial wall may potentially be a contributing factor in restenosis based on trapped proliferating cells observed for a stent with compliance-matched ends . Third, drug elution is currently achieved by coating the metal with a drug-doped polymer , which requires a costly additional fabrication step .
Thermally activated shape memory polymer (SMP) is a unique class of polymeric materials that can maintain a secondary shape and then recover a pre-determined primary shape when sufficiently heated. SMP has been shown to have promising applications in intravascular medical devices for thrombectomy [10, 11], aneurysm embolization [12, 13], and as vascular stents . Our previous investigation of the thermomechanical properties of shape memory polyurethane revealed high recovery strains, which are needed for large shape changes during stent deployment . In addition, the glassy modulus of SMP is lower than those of SMAs and stainless steel by a factor of at least 10 and 100, respectively, potentially yielding a more flexible and compliant structure depending on the amount of material and the stent design pattern . Ongoing biocompatibility studies have shown that the material has minimal effect on triggering an inflammatory response, activating platelets and neutrophils, and inducing thrombogenesis in vitro . Finally, drug embedding in polymer stents has already been demonstrated . Thus, the large strain recovery, flexibility, conformability, and compliance of SMPs could overcome the problems encountered with current metallic vascular stents.
Light absorption has been shown to be an effective heating mechanism for actuating SMPs [10, 11, 19, 20]. In this paper, we present a photothermally activated self-expanding stent made of shape memory polyurethane. The SMP stent is crimped over a light diffuser attached to the end of an optical fiber coupled to an infrared diode laser. The optical fiber serves as both the transport vehicle and the conduit for light energy delivery to the stent. We describe the design and fabrication of the device and demonstrate laser actuation in a water-filled in vitro artery model.
Shape memory polymer
The SMP used in this study was MM5520 thermoplastic polyurethane; it was obtained from DiAPLEX Company, Ltd. (a subsidiary of Mitsubishi Heavy Industries Ltd., Tokyo, Japan) in the form of pellets. The composition is proprietary, but it is known that the material is a segmented polyurethane with a microphase separated morphology consisting of a hard phase and a soft phase . The nominal temperature of the soft phase glass transition (Tg) was 55°C. The shape memory effect comes from the entropic potential for recovery of the primary shape, stored in macromolecular chains of the soft phase in the secondary shape. The primary shape can be formed by heating the material above the hard phase glass transition temperature, deforming the material into the desired shape, and then cooling to fix the shape. Alternatively, the material may be dissolved in a suitable solvent and cast in a mold or coated onto a surface (as was done in this study) and vacuum dried to establish the primary shape. The secondary shape is obtained by heating the material above Tg, deforming the material (in this case crimping), and cooling to fix the shape. Heating the material again to Tg results in recovery of the primary shape. Due to the broad soft phase glass transition of MM5520 , shape recovery begins to occur at 40–45°C (10–15°C below the nominal Tg of 55°C). The material exhibits different mechanical properties above and below the Tg. Our previous studies of this specific polymer have shown a glassy modulus of ~800 MPa (shear modulus at Tg-25°C), and a rubbery modulus of ~1.4 MPa (shear modulus at Tg + 25°C) . The glassy modulus of this SMP (~800 MPa) lies in the range of reported values for balloon-expandable polymer stents, which starts at 400 MPa (for applications requiring low mechanical strength, such as neural stenting) and extends up to 7 GPa . Accordingly, the relatively low glassy modulus (and, hence, low expansion force) of the SMP stent may require balloon angioplasty prior to laser expansion.
The light delivery/transport vehicle assembly consisted of two main components, both of which were fabricated using SMP: (1) a 300 μm diameter by ~16 mm long cylindrical light diffusing SMP rod attached to the end of an optical fiber and (2) a coaxial 5 mm diameter by ~16 mm long SMP foam cylinder surrounding the diffusing rod. This assembly was inserted inside the stent lumen prior to crimping (Fig. 1(a,c)). The diffuser was fabricated by casting an SMP formulation developed in-house  over the distal end of a 100 μm core diameter silica optical fiber (FIP100110125, Polymicro Technologies, LLC) using a tubular mold made of Teflon. To enable light diffusion, the surface of the cured SMP cylinder was abraded using a media blaster loaded with sodium bicarbonate powder. The longitudinal emission profile of the diffuser, acquired using a CCD camera with the optical fiber coupled to a red 4.2 mW diode laser, is shown in Fig. 1(d). Approximately 80% of the incident laser light was emitted in the first centimeter of the diffuser. The optical fiber was sheathed with a 711 μm outer diameter stainless steel hypotube to provide a pushable transport vehicle.
The foam component was made of in-house formulated SMP material consisting of hexamethylene diisocyanate (HDI), N,N,N'-tetrakis(2-hydroxypropyl)ethylenediamine (HPED), and triethanolamine (TEA) . The density of the foam was 0.020 g/cm3 with mostly open cells approximately 200 μm in size (determined by optical microscopy). The calculated volumetric void fraction was 98.4%, which would allow a theoretical expansion of 60 times from the fully condensed state. Differential scanning calorimetry measurements showed a Tg around 40°C. The foam cylinder was cut using a 5 mm biopsy punch and then slightly compressed under warm air to enable it to fit inside the expanded stent. The role of the foam cylinder is to assist photothermal expansion of the device by (1) centering the diffuser in the stent lumen, (2) increasing laser light scattering to improve illumination uniformity, and (3) reducing convective cooling of the stent. Though not necessary in this initial prototype, the foam would be bonded to the diffuser to facilitate withdrawal after stent deployment in a clinical device.
With the diffuser/foam assembly positioned inside the stent lumen as shown in Fig. 1(a,c), the final device was mechanically compressed using a crimping machine (Balloon Wrapping Fixture Model W8FH, Interface Associates, Inc.) from 4.1 mm down to 1.8 mm (smaller diameters are possible depending on the amount of material and stent design). The machine consists of eight radially arranged heated blades which form a cylindrical cavity; as the blades move inward, the cavity diameter decreases. The blades were heated to 88°C prior to and during compression, and then cooled to room temperature before the crimped device was removed. The device remained in the crimped shape before experimental actuation. Fig. 1(b) shows the device in its crimped state.
Artery model and device actuation
In two separate attempts, the stent expanded only about 60% during actuation at 8.6 W for several minutes when the flow rate was increased to 180 ml/min, a value in the range of reported flows in the internal carotid artery . This result suggests that the laser heating was overcome by convective cooling before full expansion was achieved.
In an actual clinical intervention, the inner foam would need to be withdrawn with the diffuser. As mentioned previously, one way to achieve this would be to bond the foam to the diffuser. Because the foam (Tg ~40°C) is compliant at body temperature, it can conform to the smaller diameter of the delivery catheter as it is pulled back for removal from the body. Tapering the proximal end of the foam may facilitate retraction back into the delivery catheter.
Physical properties of water and blood
Specific heat c
J/(kg · K)
Thermal conductivity k
W/(m · K)
Thermal diffusivity α = k/ρc
1.4 × 10-7
1.3 × 10-7
Absolute viscosity μ
7 × 10-4 
3.5 × 10-3 
Pa · s
Kinematic viscosity ν = μ/ρ
7 × 10-7
3.3 × 10-6
Coefficient of thermal expansion β
2.1 × 10-4 
4.0 × 10-4 
where g is gravity (9.81 m/s2), T i is the temperature of the inner cylinder (stent temperature ~Tg = 55°C) and T o is the temperature of the outer cylinder (body temperature = 37°C). Nu was calculated to be 1.8 for water and 1.6 for blood, indicating that heat transfer in the zero flow case is similar for the two fluids.
In the case of physiological flow, forced convection is the dominant heat transfer mechanism, though it depends on the flow characteristics. The flow is characterized by the Reynolds number (Re) given by  Re = U(D o - D i )/ν
where U is the flow velocity around the collapsed stent in the mock artery at the physiological flow rate of 180 ml/min (0.3 m/s). Re was calculated to be 940 for water and 200 for blood, values that are below the critical Re of ~2000 corresponding to the onset of turbulence in a circular tube . For laminar flow between two concentric cylinders with D i /D o = 0.45, Nu ≈ 6 for both fluids . Based on these estimates, heat transfer in water is similar to that of blood for both the zero and non-zero flow conditions in this study.
Due to their different values of absorption coefficient (μ a ) near the laser wavelength of 810 nm, photothermal actuation of the stent will proceed differently in water (μ a = 0.0021 mm-1 ) than blood (μ a = 0.466 mm-1 ). Initially, light emitted from the diffuser will reach the stent without encountering the fluid. However, as expansion continues the fluid can migrate into the pores of the inner foam cylinder. Ignoring the foam, the absorption mean free path (i.e., average distance a photon will travel before being absorbed) for water is 1/μ a = 476 mm; therefore, nearly all the emitted light will reach the stent throughout its expansion. For blood, the absorption mean free path is 2.1 mm, which is approximately equal to the radius of the fully expanded stent (note that scattering in blood is highly forward-directed with the average cosine of the scattering angle = 0.98 ). The percentage of light transmitted T to the expanding stent of radius r is given by T = 100exp(-μ a r); T = 39% for r = 2 mm (fully expanded). The probability that a photon will be absorbed by the blood prior to reaching the stent is higher than that for water; however, photons that are absorbed will locally heat the blood, which will, in turn, help heat the stent. For example, in the case of zero flow, the blood temperature rise due to absorption can be estimated by ΔT ≈ P abs t/cρV, where P abs is the absorbed laser power (~100-39 = 61% of the emitted light, ignoring absorption by the stent), t is the laser duration in seconds, c and ρ are the specific heat and density, respectively, of blood (see Table 1), and V is the volume of blood in the vicinity of the stent (~2.5 × 10-7 m3 for a 4-mm-diameter artery). This estimate assumes the heat load is evenly distributed in the blood volume and does not include heat losses to the blood and arterial wall adjacent to the heated volume. At the maximum laser power in this study, P abs ≈ 5 W and the blood temperature (ΔT + 37°C) would reach the SMP Tg of 55°C within 4 s. Accordingly, laser power and dye concentration in the stent may require adjustment relative to values suitable for use in water. Though laser actuation of the stent in blood is feasible in principle, experimental verification using blood is a necessary future step in the device development process.
Though in vitro biocompatibility studies analyzing immunostimulatory and thrombogenic properties of SMP are encouraging , other potential adverse effects of implantation (e.g., effect on renal function) and increased temperature due to thermal actuation are unknown and require additional study. In addition, the biocompatibility of the SMP doped with the laser-absorbing platinum dye has not been tested. If concerns were to arise based on such testing, a known biocompatible dye such as indocyanine green (ICG) could be used in place of the platinum dye. ICG is routinely administered intravenously as a contrast agent in retinal angiography, and has an absorbance band centered near the laser wavelength of 810 nm. ICG has been used to increase the laser absorption of SMP for photothermal actuation in previous work .
In addition to light absorption, various heating mechanisms may be employed for thermally activated SMP devices including electrical (Joule) heating [20, 37, 38], inductive heating , and heated fluid flush. For the stent application, light absorption provides a means of efficient localized heating of the dye-doped device, and the cylindrical geometry of the device is well-suited to illumination by a cylindrical light diffuser. In addition, the lack of physical connection between the light diffuser and the device enables the stent to expand freely. Inductive heating of a device doped with appropriate magnetic particles would also provide remote, localized heating, though such a device would require development of a clinically safe external source of alternating magnetic field. Localized Joule heating could be applied by embedding resistive heating elements (e.g., wires) into the device (though such elements must not interfere with shape recovery) or employing a conductive SMP composite material  and passing a current through the device; in either case, the stent would be physically connected to the power source and would have to be detached from the leads supplying the current following device deployment. Flowing heated saline through the delivery catheter either using a heated reservoir or embedding heating elements in the delivery catheter would expose a larger area of the vessel to elevated temperatures, which may or may not be detrimental.
Another option for SMP device deployment is to employ a low-Tg material (≤ 37°C) such that the device spontaneously actuates at body temperature. Such a stent would not require an external heating source, and therefore would not raise the concern of thermal tissue damage. However, the modulus of the SMP at or above Tg (~1–10 MPa)  is at least an order of magnitude lower than the modulus values of polymers typically used for stents in previous work . Nevertheless, the fact that the SMP stent would not permanently deform if compressed (e.g., during arterial spasm), unlike some metallic stents, suggests that further study of such a design may be warranted. One group has reported complete shape recovery of prototype SMP stents designed to expand at body temperature, noting that the recovery can be controlled by varying the glass transition temperature, polymer crosslink density, and stent geometry .
Photothermal actuation introduces the potential to cause thermal damage to tissue and blood in the vicinity of the device. While we did not measure the temperature of the stent, the fact that the stent fully actuated indicated that it at least approached the Tg of the stent (55°C). The temperature around the device depends on the cooling capacity of the blood and tissue, the laser power and duration, light absorption by the blood, tissue, and device, and blood flow. Thermal damage depends on the time-temperature history. For example, according to an Arrhenius damage model for arterial collagen denaturation , it would require several hours at a temperature of 55°C to induce irreversible damage, a timescale much longer than that needed for photothermal stent expansion. A similar model for arterial endothelial cell damage  indicates that cell damage would occur in less than a second at 55°C. However, standard intravascular catheter insertion and manipulation, as is used in conventional stent placement, is also known to damage the endothelial cell layer . Following acute injury (mechanical or thermal) to the vessel wall and/or endothelial layer, long-term arterial recovery has been shown [44, 45]. In vivo survival studies including histology at acute and long-term time points are required to assess the extent and tolerance of potential thermal damage caused by photothermal actuation of the SMP stent.
In practice, stents are generally placed under blood flow; however, certain other medical interventional devices, such as the MERCI Retriever for clot extraction in cerebral arteries , incorporate a protection mechanism to block blood flow during the intervention. The advantage of delivering the laser-activated SMP stent under a zero flow condition is that identical operating parameters (e.g., laser power and duration) can be used regardless of the flow conditions in the target vessel. In addition, by minimizing convective cooling, it reduces the amount of laser energy needed to achieve expansion.
Whether it will be clinically delivered with flow or without flow, this first prototype needs to be optimized for a controlled full actuation without causing detrimental thermal injury to the surrounding artery. Optimization could include systematically adjusting the dye concentration in the stent, possibly incorporating dye into the foam, improving the uniformity of emission along the length of the diffuser by modifying the media blasting parameters, and adjusting the foam density to enhance light scattering. In addition, the Tg of the stent and foam can also be varied by using a different SMP material or by varying the fabrication conditions [14, 15]. The Tg should be tailored to be low enough such that the stent can be actuated at the lowest possible laser power, but it should be high enough such that the stent does not self-expand at body temperature (37°C). The current prototype was designed for use in a large vessel such as the internal carotid artery, not in the narrow cerebral vasculature. The stent pattern and dimensions would need to be scaled down to enable the device to be crimped down sufficiently for intravascular catheter delivery.
We have shown the design and fabrication of a novel laser-activated stent made of shape memory polymer. In addition, we developed a fiber optic-based means of light delivery for photothermal actuation. Though further studies are required to optimize the device and assess potential thermal tissue damage, preliminary in vitro testing demonstrated the concept of intravascular photothermal deployment of an SMP stent.
The authors would like to thank Jeffrey Loge for helping to construct the artery model and Jennifer Rodriguez for creating the video. This work was performed under the auspices of the U.S. Department of Energy by Lawrence Livermore National Laboratory (LLNL) under Contract W-7405-ENG-48. Major support was provided by the National Institutes of Health/National Institute of Biomedical Imaging and Bioengineering, Grant R01EB000462. Additional support was provided by a LLNL Laboratory Directed Research and Development Grant (04-ERD-093) and the National Science Foundation Center for Biophotonics Science and Technology (CBST). CBST is managed by the University of California, Davis, under Cooperative Agreement No. PHY 0120999.
- Holmes DR Jr: State of the art in coronary intervention. Am J Cardiol 2003, 91: 50A-53A. 10.1016/S0002-9149(02)03150-8View ArticleGoogle Scholar
- Al-Mubarak N, Roubin GS, Iver SS, Vitek JJ, New G: Techniques of carotid artery stenting: the state of the art. Semin Vasc Surg 2000, 13: 117–129.Google Scholar
- Kudo T, Chandra FA, Ahn SS: Long-term outcomes and predictors of iliac angioplasty with selective stenting. J Vasc Surg 2005, 42: e1–466. 10.1016/j.jvs.2005.05.002View ArticleGoogle Scholar
- Hara H, Nakamura M, Palmaz JC, Schwartz RS: Role of stent design and coatings on restenosis and thrombosis. Adv Drug Deliv Rev 2006, 58: 377–386. 10.1016/j.addr.2006.01.022View ArticleGoogle Scholar
- Higashida RT, Meyers PM: Intracranial angioplasty and stenting for cerebral atherosclerosis: new treatments for stroke are needed! Neuroradiology 2006, 48: 367–372. 10.1007/s00234-006-0071-6View ArticleGoogle Scholar
- Hartmann M, Jansen O: Angioplasty and stenting of intracranial stenosis. Curr Opin Neurol 2005, 18: 39–45. 10.1097/00019052-200502000-00009View ArticleGoogle Scholar
- Rolland PH, Mekkaoui C, Vidal V, Berry JL, Moore JE, Moreno M, Amabile P, Bartoli JM: Compliance matching stent placement in the carotid artery of the swine promotes optimal blood flow and attenuates restenosis. Eur J Vasc Endovasc Surg 2004, 28: 431–438. 10.1016/j.ejvs.2004.06.018View ArticleGoogle Scholar
- Sousa JE, Serruys PW, Costa MA: New frontiers in cardiology: drug-eluting stents: part I. Circulation 2003, 107: 2274–2279. 10.1161/01.CIR.0000069330.41022.90View ArticleGoogle Scholar
- Eisenberg MJ: Drug-eluting stents: the price is not right. Circulation 2006, 114: 1745–1754. 10.1161/CIRCULATIONAHA.106.646190View ArticleGoogle Scholar
- Small W IV, Wilson TS, Benett WJ, Loge JM, Maitland DJ: Laser-activated shape memory polymer intravascular thrombectomy device. Opt Express 2005, 13: 8204–8213. 10.1364/OPEX.13.008204View ArticleGoogle Scholar
- Small W IV, Metzger MF, Wilson TS, Maitland DJ: Laser-activated shape memory polymer microactuator for thrombus removal following ischemic stroke: preliminary in vitro analysis. IEEE J Select Topics Quantum Electron 2005, 11: 892–901. 10.1109/JSTQE.2005.857748View ArticleGoogle Scholar
- Metcalfe A, Desfaits A-C, Salaskin I, Yahia LH, Sokolowski WM, Raymond J: Cold hibernated elastic memory foams for endovascular interventions. Biomaterials 2003, 24: 491–498. 10.1016/S0142-9612(02)00362-9View ArticleGoogle Scholar
- Small W IV, Buckley PR, Wilson TS, Benett WJ, Hartman J, Saloner D, Maitland DJ: Shape memory polymer stent with expandable foam: a new concept for endovascular embolization of fusiform aneurysms. IEEE Trans Biomed Eng 2007, 54 Part II: 1157–1160. 10.1109/TBME.2006.889771View ArticleGoogle Scholar
- Gall K, Yakacki CM, Liu Y, Shandas R, Willett N, Anseth KS: Thermomechanics of the shape memory effect in polymers for biomedical applications. J Biomed Mater Res 2005, 73: 339–48. 10.1002/jbm.a.30296View ArticleGoogle Scholar
- Baer G, Wilson TS, Matthews DL, Maitland DJ: Shape-memory behavior of thermally stimulated polyurethane for medical applications. J Appl Polym Sci 2007, 103: 3882–3892. 10.1002/app.25567View ArticleGoogle Scholar
- Wiskirchen J, Pusich B, Kramer U, Konic C, Trubenbach J, Tepe G, Claussen CD, Duda S: Stent struts and articulations. Their impact on balloon-expandable stents' hoop strength, pushability, and radiopacity in an experimental setting. Invest Radiol 2002, 37: 356–362. 10.1097/00004424-200206000-00008View ArticleGoogle Scholar
- Cabanlit M, Maitland D, Wilson T, Simon S, Wun T, Gershwin ME, Van de Water J: Polyurethane shape memory polymers demonstrate functional biocompatibility in vitro. Macromol Biosci 2007, 7: 48–55. 10.1002/mabi.200600177View ArticleGoogle Scholar
- Venkatraman S, Poh TL, Vinalia T, Mak KH, Boey F: Collapse pressure of biodegradable stents. Biomaterials 2003, 24: 2105–2111. 10.1016/S0142-9612(02)00640-3View ArticleGoogle Scholar
- Maitland DJ, Metzger MF, Schumann DL, Lee A, Wilson TS: Photothermal properties of shape memory polymer micro-actuators for treating stroke. Lasers Surg Med 2002, 30: 1–11. 10.1002/lsm.10007View ArticleGoogle Scholar
- Koerner H, Price G, Pearce NA, Alexander M, Vaia RA: Remotely actuated polymer nanocomposites–stress-recovery of carbon-nanotube-filled thermoplastic elastomers. Nature Mater 2004, 3: 115–120. 10.1038/nmat1059View ArticleGoogle Scholar
- Takahashi T, Hayashi N, Hayashi S: Structure and properties of shape-memory polyurethane block copolymers. J Appl Polym Sci 1996, 60: 1061–1069. Publisher Full Text 10.1002/(SICI)1097-4628(19960516)60:7<1061::AID-APP18>3.0.CO;2-3View ArticleGoogle Scholar
- Zilberman M, Eberhart RC: Drug-eluting bioresorbable stents for various applications. Annu Rev Biomed Eng 2006, 8: 153–180. 10.1146/annurev.bioeng.8.013106.151418View ArticleGoogle Scholar
- Wilson TS, Bearinger JP, Herberg JL, Marion JE III, Wright W, Evans CL, Maitland DJ: Shape memory polymers based on uniform aliphatic urethane networks. J Appl Polym Sci 2007, 106: 540–551. 10.1002/app.26593View ArticleGoogle Scholar
- Schebesch K-M, Simka S, Woertgen C, Brawanski A, Rothoerl RD: Normal values of volume flow in the internal carotid artery measured by a new angle-independent Doppler technique for evaluating cerebral perfusion. Acta Neurochir 2004, 146: 983–987. 10.1007/s00701-004-0324-2View ArticleGoogle Scholar
- Biomaterials Science: An Introduction to Materials in Medicine. Edited by: Ratner BD, Hoffman AS, Schoen FJ, Lemons JE. San Diego: Academic Press; 1996:469.Google Scholar
- Donnelly RJ: Fluid dynamics. In A Physicist's Desk Reference: The Second Edition of Physics Vade Mecum. Edited by: Anderson HL. New York: American Institute of Physics; 1989:196–209.Google Scholar
- Anderson HL, Cohen ER: General section. In A Physicist's Desk Reference: The Second Edition of Physics Vade Mecum. Edited by: Anderson HL. New York: American Institute of Physics; 1989:37–39.Google Scholar
- Orr C-S, Eberhart RC: Overview of Bioheat Transfer. In Optical-Thermal Response of Laser Irradiated Tissue. Welch AJ, van Gemert MJC edition. New York: Plenum Press; 1995:367–384.View ArticleGoogle Scholar
- Lee AJ, Mowbray PI, Lowe GDO, Rumley A, Fowkes FGR, Allan PL: Blood viscosity and elevated carotid intima-media thickness in men and women. Circulation 1998, 97: 1467–1473.View ArticleGoogle Scholar
- Hinghofer-Szalkay H: Volume and density changes of biological fluids with temperature. J Appl Physiol 1985, 59: 1686–1689.Google Scholar
- Raithby GD, Hollands KGT: Natural convection. In Handbook of Heat Transfer Fundamentals. Volume 6. 2nd edition. Edited by: Rohsenow WM, Hartnett JP, Ganic EN. New York: McGraw-Hill; 1985:1–6.Google Scholar
- Chapman AJ: Heat Transfer. 2nd edition. New York: The Macmillan Company; 1967:339.Google Scholar
- Kays WM, Perkins HC: Forced convection, internal flows in ducts. In Handbook of Heat Transfer Fundamentals. Volume 7. 2nd edition. Edited by: Rohsenow WM, Hartnett JP, Ganic EN. New York: McGraw-Hill; 1985:1–7.Google Scholar
- Smith RC, Baker KS: Optical properties of the clearest natural waters (200–800 nm). Appl Opt 1981, 20: 177–184.View ArticleGoogle Scholar
- Schmitt JM: Simple photon diffusion analysis of the effects of multiple scattering on pulse oximetry. IEEE Trans Biomed Eng 1991, 38: 1194–1203. 10.1109/10.137285View ArticleGoogle Scholar
- Steinke JM, Shepherd AP: Diffusion model of the optical absorbance of whole blood. J Opt Soc Am A 1988, 5: 813–822.View ArticleGoogle Scholar
- Small W IV, Wilson TS, Buckley PR, Benett WJ, Loge JM, Hartman J, Maitland DJ: Prototype fabrication and preliminary in vitro testing of a shape memory endovascular thrombectomy device. IEEE Trans Biomed Eng 2007, 54: 1657–1666. 10.1109/TBME.2007.892921View ArticleGoogle Scholar
- Hartman J, Small W IV, Wilson TS, Brock J, Buckley PR, Benett WJ, Loge JM, Maitland DJ: Embolectomy in a rabbit acute arterial occlusion model using a novel electromechanical extraction device. AJNR Am J Neuroradiol 2007, 28: 872–874.Google Scholar
- Buckley PR, McKinley GH, Wilson TS, Small W IV, Benett WJ, Bearinger JP, McElfresh MW, Maitland DJ: Inductively heated shape memory polymer for the magnetic actuation of medical devices. IEEE Trans Biomed Eng 2006, 53: 2075–2083. 10.1109/TBME.2006.877113View ArticleGoogle Scholar
- Yakacki CM, Shandas R, Lanning C, Rech B, Eckstein A, Gall K: Unconstrained recovery characterization of shape-memory polymer networks for cardiovascular applications. Biomaterials 2007, 28: 2255–2263. 10.1016/j.biomaterials.2007.01.030View ArticleGoogle Scholar
- Agah R, Pearce JA, Welch AJ, Motamedi M: Rate process model for arterial tissue thermal damage. Lasers Surg Med 1994, 15: 176–184. 10.1002/lsm.1900150205View ArticleGoogle Scholar
- Rylander MN, Diller KR, Wang S, Aggarwal SJ: Correlation of HSP70 expression and cell viability following thermal stimulation of bovine aortic endothelial cells. J Biomech Eng 2005, 127: 751–757. 10.1115/1.1993661View ArticleGoogle Scholar
- Soltani A, Singhal R, Garcia JL, Raju NR: Absence of biological damage from prolonged exposure to intravascular ultrasound: a swine model. Ultrasonics 2007, 46: 60–67. 10.1016/j.ultras.2006.10.004View ArticleGoogle Scholar
- Oomen A, van Erven L, Vandenbroucke WV, Verdaasdonk RM, Slager CJ, Thomsen SL, Borst C: Early and late arterial healing response to catheter-induced laser, thermal, and mechanical wall damage in the rabbit. Lasers Surg Med 1990, 10: 363–374. 10.1002/lsm.1900100410View ArticleGoogle Scholar
- Buller CE, Culp SC, Sketch MH Jr, Phillips HR, Virmani R, Stack RS: Thermal-perfusion balloon coronary angioplasty: in vivo evaluation. Am Heart J 1993, 125: 226–233. 10.1016/0002-8703(93)90079-OView ArticleGoogle Scholar
- Katz JM, Gobin YP: Merci Retriever in acute stroke treatment. Expert Rev Med Devices 2006, 3: 273–80. 10.1586/174344126.96.36.1993View ArticleGoogle Scholar
This article is published under license to BioMed Central Ltd. This is an Open Access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/2.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.