WO1998022073A2 - Radionuclide production using intense electron beams - Google Patents
Radionuclide production using intense electron beams Download PDFInfo
- Publication number
- WO1998022073A2 WO1998022073A2 PCT/US1997/020921 US9720921W WO9822073A2 WO 1998022073 A2 WO1998022073 A2 WO 1998022073A2 US 9720921 W US9720921 W US 9720921W WO 9822073 A2 WO9822073 A2 WO 9822073A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- target material
- target
- electron beam
- cartridge
- electron
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1001—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy using radiation sources introduced into or applied onto the body; brachytherapy
- A61N5/1002—Intraluminal radiation therapy
Definitions
- the present invention relates generally to the point-of-use production of radionuclides by irradiation with intense electron beams so as to form radioactive materials suitable for therapeutic and/or diagnostic medical purposes and/or industrial applications.
- Radioactive materials have been used extensively for many years for therapeutic and/or diagnostic medical purposes.
- radioisotopes are used to kill large volumes of cancer cells directly using large quantities of radioactive material.
- small amounts of radioisotopes are injected into the body or bloodstream and their position in the body is determined by observing the gamma rays emitted when they decay.
- Radioisotopes may also be bound to some chemical which is selected for its ability to localize at a problem area in the body thereby aiding in the diagnosis of disease.
- Relatively newer therapies propose the use of small amounts of radioactivity to treat small tissue volumes, namely intravascular walls.
- the radioactive stent releases radiation so as to decrease the rate of proliferative cell growth of the traumatized arterial wall (i.e., to decrease intimal hyperplasia).
- restenosis after stent implantation is expected to be significantly reduced.
- U.S. Patent No. 5,199,939 to Dake et al the entire content of which is expressly incorporated hereinto by reference).
- Radioisotopes While radiating tissue for medical diagnostic and/or therapeutic purposes is advantageous, there are several real and nontrivial problems associated with such Anuclear medicine®, primarily in the availability and/or accessability of the physician to a source of suitable radioactive devices and materials.
- radioisotopes whose properties are such that they have potential value in nuclear medicine, but which cannot conventionally be produced easily in sufficiently large quantities for distribution.
- a radioisotope has a relatively short half life (e.g., on the order of less than 24 hours), then it cannot be produced at a nuclear reactor (of which there are only a handful in the United States), verified, and shipped to an end user before the produced radioactivity has ceased.
- Radioisotopes are therefore quite useful, but the ability to cost-effectively generate them at the Apoint-of-use@ does not presently exist, except for those facilities in sufficiently close proximity to a nuclear reactor or cyclotron. However, for those radioisotopes having a relatively long half life (e.g., greater than one week), then practically every medical site in the United States can avail themselves to such materials.
- Radionuclides are well known and are used successfully in the medical field for purposes of cancer therapy, imaging and diagnosis of disease, as well as in assorted industrial testing and sterilization applications.
- the conventional wisdom in the art is that nuclear reactors and cyclotrons are again necessary for production of useful radionuclides.
- high-energy photons i.e., greater than 10 MeV
- the present invention is directed to the methods and systems for producing radionuclides by colliding a focussed electron beam with a target material capable of being radioactivated by the electron beam.
- the target material is translated relative to the electron beam along at least two (2) axes.
- a target cartridge is provided according to the present invention which includes a tubular shell formed of a material which is minimally (if at all) activated by the electron beam or, if activated, has radioactivity that is very short lived in terms of minutes or less (e.g., aluminum).
- the tubular shell defines an interior hollow space which houses the target material to be irradiated, e.g. an intraluminal stent.
- the interior space may optionally be filled with a heat transfer fluid (e.g., water, air, an oxygen-less gas or an inert gas).
- a heat transfer fluid e.g., water, air, an oxygen-less gas or an inert gas.
- End caps close each end of the tubular shell and are preferably one-piece solid structures formed of the same material as that of the tubular shell. The end caps therefore most preferably serve the purposes of allowing the target cartridge to be mechanically coupled to a translator assembly and provide a path of heat transfer to a heat-transfer fluid (e.g., liquid and/or gas) in contact therewith.
- a heat transfer fluid e.g., water, air, an oxygen-less gas or an inert gas
- the translator assembly most preferably holds the target cartridge longitudinally so that it is positioned substantially transversely relative to the path of the electron beam.
- the entire target cartridge may be linearly translated simultaneously or periodically sequentially parallel and perpendicular to the electron beam path.
- the target cartridge may be rotated about its axis. In such a manner, the target cartridge exposes the target material therewithin uniformly to the electron beam.
- FIGURE 1 is a schematic view of a preferred exemplary system according to the present invention employed for the on-site production of radionuclides
- FIGURE 2 is a schematic perspective view, partly in section, of one embodiment of a cartridge holder for holding a desired target material to be irradiated by the electron beam generated in the system of FIGURE 1 ;
- FIGURE 3 is a schematic view, partly in section, of another embodiment of a cartridge holder for the target material.
- FIGURE 1 A presently preferred system 10 for obtaining radionuclides at the point-of-use is depicted schematically in accompanying FIGURE 1 as including an electron generator 12, a target translator assembly 14, a beam dump 16 and a cooling assembly 18.
- the electron generator 12 is one part of a linear accelerator system that is conventionally employed in the medical arts for the treatment of cancer. Suitable linear accelerators that may be modified according to the present invention to form the electron generator 12 include ClinacJ Model Nos. 2100 and 1800 commercially available from Varian Corporation of Palo Alto, California.
- the electron generator 12 is provided internally with a DC power supply 12a to provide DC power to the modulator 12b.
- the modulator 12b is operatively connected to the electron gun 12c which injects electrons into the accelerator tube 12d and wave guide system 12e.
- the klystron 12f is connected operatively to the accelerator 12d via the wave guide system 12e to deliver high power to the latter.
- a magnetic steering system 12g is provided so as to focus the electron beam exiting the accelerator tube 12d into a relatively small cross-sectional area focus (e.g., an effective electron beam diameter of between about 1.0 to about 3.0 mm, and preferably between about 1.0 to about 1.5 mm).
- the electron beam most preferably has substantially the same cross-sectional geometry as the target material which it is irradiating.
- Circular cross-sectional geometry for the electron beam is standard, but non-circular geometries may also be employed by subjecting the beam to controllable magnetic fields (e.g., by Arelaxing@ the magnetic field along one of the beam axes relative to the magnetic field acting along the other of the beam axes).
- the electron beam that is produced need not be continuous, and may in fact be in the form of electron beam cycles or Apackets@ per unit time. For a given number of electrons per unit time produced, however, it is preferred that more pulses per unit time of lesser intensity (i.e., greater number of electrons in each pulse) be produced.
- the electron generator is capable of generating an electron beam energy of between about 10 MeV to about 50 MeV. More specifically, for relatively heavier isotopes, the preferred electron energy is in the range of about 15 MeV to about 20 MeV, while relatively lighter isotopes may require electron energies of about 30 MeV or greater.
- the electron generator 12 need not have a precise or exact energy spread as may be the case for therapeutic electron generators. Instead, electron energy spreads of about "10% are acceptable for purposes of the present invention.
- the target translator assembly 14 is positioned downstream (i.e., relative to the electron beam path shown by arrows A e in FIGURE 1) and includes a linear rail assembly 14a which carries a support table 14b for reciprocal transverse movements generally horizontally perpendicular to the electron beam path A e (i.e., into and out of the plane as shown schematically by the depiction of arrow A 1 in FIGURE 1).
- the support table 14b is moved reciprocally relative to the rail assembly 14a via a precision DC electric motor 14c.
- the support table 14b carries an upright support column 14d laterally of the electron beam path A e and includes an adjustment shaft 14e which is linearly telescopically moveable relative to the support column 14d (i.e., in the direction of arrow A 2 shown in FIGURE 1 generally perpendicularly relative to the electron beam path A e ).
- Motive force to the support column 14d to enable it to move reciprocally in the direction of arrow A 2 is provided via a precision reversible DC motor 14f.
- the adjustment shaft 14e carries a precision DC electric motor 14g for concurrent movements therewith.
- the motor 14g includes an output/drive shaft 14h depending therefrom to which is coaxially attached a target cartridge 20.
- the motor 14g causes the shaft 14h to rotate about the shaft axis in a desired direction (e.g., in the direction of arrow A 3 in FIGURE 1) which in turn rotates the cartridge 20 relative to the impinging electron beam.
- the target cartridge 20 contains the target material to be irradiated by the electron beam emitted by the generator 12 in a manner to be described in greater detail below.
- the target translator 14 is thus capable of moving the target cartridge 20 along at least two axes relative to the electron beam and rotating the cartridge 20 about one of the axes. Namely, the translator 14 is capable of controlled linear movements of the target cartridge 20 into and out of the electron beam generally horizontally transverse to the electron beam path A e . The target cartridge 20 is also capable of being moved into and out of the electron beam in the direction of arrow A 2 generally vertically perpendicular relative to the beam path A e . Simultaneously with such linear movements, the translator 14 is capable of rotating the target cartridge 20 about the axis of shaft 14h. Other degrees of movement can be provided, however.
- a further precision motor could be provided so as to oscillate the shaft 14h at an angle relative to vertical and/or relative to the beam path A e .
- the translator 14 may be programmed to move the target cartridge 20 in precise relationship to the electron beam provided by the electron generator 12 so as to uniformly and reliably irradiate the target material within the cartridge 12 for the desired period of time. Furthermore, it can be used to selectively non-uniformly irradiate the target - e.g., make the ends of the target material more radioactive per unit length than the center.
- the beam dump 16 is most preferably a relatively large mass of material which stops the electron beam without producing radioactivity in dangerous amounts and minimizes the photon generation from Bremsstrahlung processes. It also absorbs heat and disperses absorbed heat due to conduction.
- the beam dump 16 is most advantageously includes a forward section 16a (i.e., disposed toward the electron generator 12) formed of a solid material having a relatively low atomic number (e.g., aluminum) so as to be insubstantially affected by the electron beam.
- Alow atomic number® is meant a material having an atomic number (Z) less than about 30, and more preferably less than about 13.
- a heat sump 16b is mounted rearwardly of the forward section of the beam dump 16 and is most preferably formed of a highly heat conductive solid material, e.g., copper.
- the beam dump 16 may be in the form of a water-holding container having an ion chamber 16c submersed therein to measure radiation by recording ionization in the chamber with an electrometer (not shown).
- the thickness of the beam dump depends on the electron energy and material. For example, the thickness of a small water beam dump is 15 cm for a 20 MeV beam, but is 6 cm for an aluminum beam dump.
- cooling fluid e.g., a thermally conductive liquid (water) or gas (refrigerant)
- the cooling fluid within the bath 18a is fluid-connected to a heat-transfer system (e.g., a chiller) 18b via conduit 18c.
- the heat-transfer system 18b is also fluid connected to the electron beam dump 16 via conduit 18d. More particularly, if the beam dump 16 includes a highly heat conductive rearward heat sump 16b, then the chilled water is most preferably jacketed therearound so as to control the temperature of the beam dump 16.
- the beam dump 16 is in the form of a water-containing chamber, then the water in the chamber is circulated to the heat-transfer system 18b via the conduit 18d. In such a manner, the target cartridge 20 and the beam dump 16 are maintained at appropriate operating temperature levels.
- the operation of the system 10 is controlled by a conventional programmable controller 30.
- the controller receives as one input, a signal from a coil or torroid system 32 positioned at the output of the electron beam generator 12, which is indicative of the number of electrons in the generated beam (i.e., beam current).
- the beam dump 16 supplies the controller 30 with an electron current result which is obtained from the ion chamber 16c.
- signals indicative of the relative positions of support table 12b and shafts 14e, 14h are supplied as inputs to the controller 30.
- the target cartridge 20 may be removed and brought into relatively close proximity to a remotely located (e.g., relative to the accelerator 12) sodium iodide detector 34 which records the photons emitted by the radioactive nature of the material in a fixed unit of time of counting.
- the controller 30 includes a multichannel analyzer which sorts the photon energies according to their energy. The controller 30 thus is capable of identifying the pattern of photon energy emission as the particular radioactive element via comparison to standard patterns. The controller 30 quantifies the obtained activity or strength of the radiation relative to previous calibrations and stores the result and history of the irradiation.
- the information may then be used to plan for another irradiation at a later time so as to take the target material within the cartridge 20 to an exact level of custom activity in as short of period of time as possible.
- This control enables uniform or a particular pattern of non-uniform activation of a target material.
- the controller 30 is interfaced to the electron beam generator 12 and the motors 14c, 14f and 14g so that precise control may be exercised 7 7
- the entire system is most preferably enclosed within a shield structure (not shown) so as to shield adjacent persons from the inevitable inadvertent production of photons and neutrons.
- the shield structure is most preferably lead, tungsten, depleted uranium and/or concrete which are fabricated according to known techniques.
- the target cartridge 20 includes a central tubular body shell 20a having an exterior wall 20a ! which defines an interior space 20a 2 .
- the material from which the tubular shell 20a is fabricated is preferentially a low atomic number material and a good heat conductor. Aluminum is particularly preferred since it does not activate at electron beam energies under 15 MeV and is a satisfactory heat conductor.
- Other materials which can be used to form the tubular shell 20a include copper, stainless steel, quartz and titanium.
- the wall 20a ! of the tubular shell 20 must also be sufficiently thin to allow electrons to pass into the interior space 20a 2 , but be sufficiently thick to impart structural rigidity and integrity to the shell 20.
- thicker (e.g., in terms of g/cm 2 ) walls of the shell 20 will result in relatively longer activation times for the target material and vice versa.
- a balance between the thickness of wall 20a ! and the activation time of the target material contained therewithin must be made.
- the thickness of wall 20a should not exceed about 1.50 mm, and preferably should be between about 0.10 and about 0.50 mm.
- Each end of the tubular shell 20a is closed by a solid end cap 20b.
- the end caps 20b, 20c can be fabricated from any material which has sufficient mass and conducts heat well, but preferably the end caps 20b, 20c are fabricated from the same material as the tubular shell 20a, namely, aluminum.
- the end caps 20b, 20c serve to close each end of the tubular shell 20a and allow the entire target cartridge 20 to be mechanically coupled longitudinally to the shaft 14h (see FIGURE 1) via threads, clamp structures, bolts and the like.
- At least one of the end caps 20c carries a coaxially positioned rigid core element 20d around which a length of the target material 22 to be irradiated by the electron beam may be helically wrapped.
- the core element 20d provides support for the target material 22 carried thereby and most preferably is formed of a high-melting point material so it is unaffected by the heat generated during irradiation, e.g., tungsten.
- the target material 22 may be in virtually any desired structural shape.
- the target material 22 may be in the form of a helical stent without a core 20d and/or may be in the form of a wire mesh wrapped around the core 20d to thereby allow for the creation of intricate radioactive structures.
- At least one, and more preferably both, of the end caps 20b, 20c are removably coupled to the tubular shell 20a, preferably by threaded interengagement, to allow access to the interior space 20a 2 (e.g., so as to allow removal of the irradiated target material 22).
- the interior space 20a 2 of the tubular shell 20a may optionally be 73
- a circulating fluid medium which is chemically compatible with the target material under electron beam irradiation conditions (e.g., water, air, oxygen-less gas, or inert gas) which facilitates thermal contact between the target material wire 22 and the tubular shell 20a and end caps 20b, 20c and serves to dissipate heat therefrom.
- the fluid medium may be introduced into and withdrawn from the shell 20 via suitable coolant inlet/outlet ports. If the shell 20 is sealed - e.g., if a circulating fluid medium is not employed -- then it is preferred that the interior space within the shell 20 be evacuated or be filled with an inert gas.
- tubular shell 20a Although a right cylindrical configuration is depicted in FIGURE 2 for the tubular shell 20a, virtually any tubular cross-sectional geometries may be employed as the shell 20a in the practice of this invention. Thus, tubular shells having a rectangular, pentagonal, hexagonal and the like geometry may be employed. Also, a tubular shell having an elliptical cross-section may be employed, in which case it is preferred that the major axis of the shell be presented to the electron beam. In addition, the tubular shell need not have a linear central axis, but instead may be bent or curved. The only real constraint is a shape that has a thin wall. In certain modifications, there is no wall at all.
- target cartridge 20' is depicted in FIGURE 3 and is structurally similar to target cartridge 20 depicted in FIGURE 2, except that no core element 20d is provided.
- the target cartridge 20' is especially adapted to accept target material 24 in the form of straight wires, shells, meshes, relatively short lengths of random or regular wire, particulate material (e.g., powders) and the like.
- the target material may be loaded into the interior space 20a 2 ' in a regular pattern as shown in FIGURE 3, or may be randomly positioned therewithin.
- the target material may be virtually any material which produces a radioactive isotope when bombarded by an electron beam having a beam energy between about 10 to about 50 MeV.
- Exemplary elements that may be used as target materials in the target cartridges described above include Br, Lu, Ta, Re, Ir, C, F, P, Sc, Cu, Zn, Pt, Ga, Ni, Te, Pm, Ho, Yb, Ta and Au. If the target material is in the form of an intraluminal stent, then nickel, tantalum, platinum and rhenium are particularly preferred.
- radioisotopes which can be formed according to the present invention include 83 Br , 179 Lu, 183 Ta, 189 Re, 194 lr, 195 lr, 11 C, 18 F, 30 P, 44 Sc, 62 Cu, 64 Cu, 63 Zn, 68 Ga, 57 Ni, 127 Te, 129 Te, 140 Pm, 16 Ho, 175 Yb, 179 Lu, 180 Ta, 184 Re, 186 Re, and 196 Au.
- a wire mesh of tantalum (Ta) as the target material was wrapped around an aluminum core of a target cartridge depicted in FIGURE 2 having a 1.0 mm diameter x 15 mm length so that the mesh had a nominal diameter of about 1.2 mm.
- the wire diameter of the Ta mesh was such that the mesh size was about 0.1 mm.
- the tubular shell which contained the core and wire mesh was formed from aluminum and had an 75
- the end caps of the tubular shell were made of one piece solid aluminum with a diameter of about 12.5 mm and lengths of 25 mm and 38 mm, respectively.
- the larger diameter and greater length of the end caps relative to the tubular shell added thermal mass to the target cartridge thereby reducing the heat requirements.
- the target cartridges in accordance with the present invention may include a tubular shell with end caps that serve to provide nominal closure to the interior space of the shell.
- the target cartridge may therefore be designed to be placed or loaded within a cartridge holder having the appropriate mass and structural integrity at its ends to serve the purpose of the end caps described above (e.g., for mounting and thermal transfer purposes).
Abstract
Description
Claims
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU54408/98A AU5440898A (en) | 1996-11-05 | 1997-11-04 | Radionuclide production using intense electron beams |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US60/030,282 | 1996-11-04 | ||
US3028296P | 1996-11-05 | 1996-11-05 | |
US96306897A | 1997-11-03 | 1997-11-03 | |
US08/963,068 | 1997-11-03 |
Publications (2)
Publication Number | Publication Date |
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WO1998022073A2 true WO1998022073A2 (en) | 1998-05-28 |
WO1998022073A3 WO1998022073A3 (en) | 1999-02-25 |
Family
ID=26705862
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1997/020921 WO1998022073A2 (en) | 1996-11-05 | 1997-11-04 | Radionuclide production using intense electron beams |
Country Status (2)
Country | Link |
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AU (1) | AU5440898A (en) |
WO (1) | WO1998022073A2 (en) |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7704275B2 (en) | 2007-01-26 | 2010-04-27 | Reva Medical, Inc. | Circumferentially nested expandable device |
US7722662B2 (en) | 1998-02-17 | 2010-05-25 | Reva Medical, Inc. | Expandable stent with sliding and locking radial elements |
US7763065B2 (en) | 2004-07-21 | 2010-07-27 | Reva Medical, Inc. | Balloon expandable crush-recoverable stent device |
US7914574B2 (en) | 2005-08-02 | 2011-03-29 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US7947071B2 (en) | 2008-10-10 | 2011-05-24 | Reva Medical, Inc. | Expandable slide and lock stent |
US7988721B2 (en) | 2007-11-30 | 2011-08-02 | Reva Medical, Inc. | Axially-radially nested expandable device |
US8277500B2 (en) | 2004-12-17 | 2012-10-02 | Reva Medical, Inc. | Slide-and-lock stent |
US8523936B2 (en) | 2010-04-10 | 2013-09-03 | Reva Medical, Inc. | Expandable slide and lock stent |
US9149378B2 (en) | 2005-08-02 | 2015-10-06 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US9408732B2 (en) | 2013-03-14 | 2016-08-09 | Reva Medical, Inc. | Reduced-profile slide and lock stent |
Citations (4)
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US2975113A (en) * | 1956-11-28 | 1961-03-14 | Gordon Carroll Maret | Method of fabrication of an irradiation transmutation capsule |
US3324540A (en) * | 1963-06-17 | 1967-06-13 | Adolphus L Lotts | Method for making porous target pellets for a nuclear reactor |
US3594275A (en) * | 1968-05-14 | 1971-07-20 | Neutron Products Inc | Method for the production of cobalt-60 sources and elongated hollow coiled wire target therefor |
WO1991015857A1 (en) * | 1990-04-03 | 1991-10-17 | Teleki Peter | Method of utilizing the k capture process by the means of high energy electrons |
-
1997
- 1997-11-04 AU AU54408/98A patent/AU5440898A/en not_active Abandoned
- 1997-11-04 WO PCT/US1997/020921 patent/WO1998022073A2/en active Application Filing
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2975113A (en) * | 1956-11-28 | 1961-03-14 | Gordon Carroll Maret | Method of fabrication of an irradiation transmutation capsule |
US3324540A (en) * | 1963-06-17 | 1967-06-13 | Adolphus L Lotts | Method for making porous target pellets for a nuclear reactor |
US3594275A (en) * | 1968-05-14 | 1971-07-20 | Neutron Products Inc | Method for the production of cobalt-60 sources and elongated hollow coiled wire target therefor |
WO1991015857A1 (en) * | 1990-04-03 | 1991-10-17 | Teleki Peter | Method of utilizing the k capture process by the means of high energy electrons |
Cited By (21)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7722662B2 (en) | 1998-02-17 | 2010-05-25 | Reva Medical, Inc. | Expandable stent with sliding and locking radial elements |
US7763065B2 (en) | 2004-07-21 | 2010-07-27 | Reva Medical, Inc. | Balloon expandable crush-recoverable stent device |
US8512394B2 (en) | 2004-07-21 | 2013-08-20 | Reva Medical Inc. | Balloon expandable crush-recoverable stent device |
US9173751B2 (en) | 2004-12-17 | 2015-11-03 | Reva Medical, Inc. | Slide-and-lock stent |
US8277500B2 (en) | 2004-12-17 | 2012-10-02 | Reva Medical, Inc. | Slide-and-lock stent |
US8292944B2 (en) | 2004-12-17 | 2012-10-23 | Reva Medical, Inc. | Slide-and-lock stent |
US7914574B2 (en) | 2005-08-02 | 2011-03-29 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US9149378B2 (en) | 2005-08-02 | 2015-10-06 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US8617235B2 (en) | 2005-08-02 | 2013-12-31 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US8540762B2 (en) | 2007-01-26 | 2013-09-24 | Reva Medical, Inc. | Circumferentially nested expandable device |
US7704275B2 (en) | 2007-01-26 | 2010-04-27 | Reva Medical, Inc. | Circumferentially nested expandable device |
US8172894B2 (en) | 2007-01-26 | 2012-05-08 | Reva Medical, Inc. | Circumferentially nested expandable device |
US7988721B2 (en) | 2007-11-30 | 2011-08-02 | Reva Medical, Inc. | Axially-radially nested expandable device |
US8460363B2 (en) | 2007-11-30 | 2013-06-11 | Reva Medical, Inc. | Axially-radially nested expandable device |
US9314354B2 (en) | 2007-11-30 | 2016-04-19 | Reva Medical, Inc. | Axially-radially nested expandable device |
US8545547B2 (en) | 2008-10-10 | 2013-10-01 | Reva Medical Inc. | Expandable slide and lock stent |
US9066827B2 (en) | 2008-10-10 | 2015-06-30 | Reva Medical, Inc. | Expandable slide and lock stent |
US7947071B2 (en) | 2008-10-10 | 2011-05-24 | Reva Medical, Inc. | Expandable slide and lock stent |
US8523936B2 (en) | 2010-04-10 | 2013-09-03 | Reva Medical, Inc. | Expandable slide and lock stent |
US9452068B2 (en) | 2010-04-10 | 2016-09-27 | Reva Medical, Inc. | Expandable slide and lock stent |
US9408732B2 (en) | 2013-03-14 | 2016-08-09 | Reva Medical, Inc. | Reduced-profile slide and lock stent |
Also Published As
Publication number | Publication date |
---|---|
WO1998022073A3 (en) | 1999-02-25 |
AU5440898A (en) | 1998-06-10 |
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