CA2503052A1 - Mixing and delivery medical syringe system for therapeutic compositions - Google Patents
Mixing and delivery medical syringe system for therapeutic compositions Download PDFInfo
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- CA2503052A1 CA2503052A1 CA002503052A CA2503052A CA2503052A1 CA 2503052 A1 CA2503052 A1 CA 2503052A1 CA 002503052 A CA002503052 A CA 002503052A CA 2503052 A CA2503052 A CA 2503052A CA 2503052 A1 CA2503052 A1 CA 2503052A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/178—Syringes
- A61M5/28—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle
- A61M5/284—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle comprising means for injection of two or more media, e.g. by mixing
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/178—Syringes
- A61M5/19—Syringes having more than one chamber, e.g. including a manifold coupling two parallelly aligned syringes through separate channels to a common discharge assembly
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/178—Syringes
- A61M5/28—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle
- A61M5/285—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle with sealing means to be broken or opened
- A61M5/286—Syringe ampoules or carpules, i.e. ampoules or carpules provided with a needle with sealing means to be broken or opened upon internal pressure increase, e.g. pierced or burst
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- Health & Medical Sciences (AREA)
- Vascular Medicine (AREA)
- Engineering & Computer Science (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- Medicines Containing Antibodies Or Antigens For Use As Internal Diagnostic Agents (AREA)
Abstract
In one aspect the invention features a mixing and delivery medical syringe system including a barrel with first and second detachable sections, and fir st and second compartments communicable through a conduit. In another aspect th e invention feature a mixing and delivery medical syringe system including a barrel having first and second compartments arranged in aprallel along the barrel, the compartments communicable through a pressure activated conduit. In still another aspect, the ivention features a kit for medicant mixing and delivery, including a syringe system, which includes a barrel assembled from multiple sections, including a first section having a first chamber, and a second section having a second chamber. The syringe system includes a condui t between the first and second chambers through which flow can be controlled. The kit further includes a first container containing a first composition, a nd a second container containing a second composition.
Description
MIXING AND DELIVERY OF THERAPEUTIC COMPOSITIONS
TECHNICAL FIELD
This invention relates to mixing and delivery of therapeutic compositions.
BACKGROUND
Therapeutic vascular occlusions (embolizations) are induced by the introduction of various substances (embolic material, such as embolic particles) into a patient's circulatory system for the purpose of occluding vessels, either to arrest or to prevent hemorrhaging or to defunctionalize a structure or an organ. Typically, the components of an embolic composition - embolic particles in hydrating material (such as saline) and contrast agent (used for tracking the path of the embolic particles inside the body) are stored separately and mixed together at the time of injection into the body by the physician.
SUMMARY
Tn one aspect the invention features a mixing and delivery medical syringe system. The medical syringe system includes a barrel including first and second detachable sections, and first and second compartments communicable through a conduit.
In another aspect the invention feature a mixing and delivery medical syringe system. The medical syringe system includes a barrel having first and second compartments arranged in parallel along the barrel, the compartments communicable through a pressure-activated conduit.
In another aspect, the invention features a kit for medicant mixing and delivery, including a syringe system, which includes a barrel assembled from multiple sections, including a first section having a first chamber, and a second section having a second chamber. The syringe system includes a conduit between the first and second chambers through which flow can be controlled. The kit further includes a first container containing a first composition, and a second container containing a second composition.
In another aspect, the invention features a method for delivering injectable polymer particles by providing a syringe. The syringe includes a first compartment and a second compartment. A first component including injectable particles is loaded into at least one compartment, and the syringe is actuated to deliver the particles.
Embodiments can include one or more of the following. The conduit can include a pressure-activated separator. The separator can include a failure membrane.
The failure membrane can include a weakened region. The weakened region preferentially effects rupture about a central region of the membrane. The weakened region preferentially affects rupture such that an attachment portion is not ruptured.
The pressure-activated conduit can include a valve.
The first and the second compartments can be arranged serially along the syringe barrel. The barrel can include a vent valve. The barrel can include a fluid outlet and the outlet can include a valve. The first section can include the first chamber and the second section can include the second chamber. The conduit can be in one of the first or second sections.
The first composition can include injectable polymer particles. The particles can be embolic particles. The second composition can be a contrast agent.
Alternatively, the second composition can include an anticancer agent.
The syringe can include a conduit between the compartments. A first component including injectable particles is loaded into at least one compartment and a second component is loaded into the second compartment. The first component and the second component are mixed in the syringe by flowing at least one of the components through the conduit. The second component can include a contrast agent. The second component can include a drug.
The method can include loading a second composition in the second compartment. The second composition can include polymer particles. The first component and second component can be delivered sequentially.
The first component and the second component can include polymer particles of different sizes or alternatively, of different shapes. The first component can include particles that are substantially spherical.
Embodiments may include one or more advantages. For example, pre-mixing the components may be undesirable because the shelf life of the mixed composition may be reduced for e.g., due to chemical interactions between a contrast agent and embolic particles.
TECHNICAL FIELD
This invention relates to mixing and delivery of therapeutic compositions.
BACKGROUND
Therapeutic vascular occlusions (embolizations) are induced by the introduction of various substances (embolic material, such as embolic particles) into a patient's circulatory system for the purpose of occluding vessels, either to arrest or to prevent hemorrhaging or to defunctionalize a structure or an organ. Typically, the components of an embolic composition - embolic particles in hydrating material (such as saline) and contrast agent (used for tracking the path of the embolic particles inside the body) are stored separately and mixed together at the time of injection into the body by the physician.
SUMMARY
Tn one aspect the invention features a mixing and delivery medical syringe system. The medical syringe system includes a barrel including first and second detachable sections, and first and second compartments communicable through a conduit.
In another aspect the invention feature a mixing and delivery medical syringe system. The medical syringe system includes a barrel having first and second compartments arranged in parallel along the barrel, the compartments communicable through a pressure-activated conduit.
In another aspect, the invention features a kit for medicant mixing and delivery, including a syringe system, which includes a barrel assembled from multiple sections, including a first section having a first chamber, and a second section having a second chamber. The syringe system includes a conduit between the first and second chambers through which flow can be controlled. The kit further includes a first container containing a first composition, and a second container containing a second composition.
In another aspect, the invention features a method for delivering injectable polymer particles by providing a syringe. The syringe includes a first compartment and a second compartment. A first component including injectable particles is loaded into at least one compartment, and the syringe is actuated to deliver the particles.
Embodiments can include one or more of the following. The conduit can include a pressure-activated separator. The separator can include a failure membrane.
The failure membrane can include a weakened region. The weakened region preferentially effects rupture about a central region of the membrane. The weakened region preferentially affects rupture such that an attachment portion is not ruptured.
The pressure-activated conduit can include a valve.
The first and the second compartments can be arranged serially along the syringe barrel. The barrel can include a vent valve. The barrel can include a fluid outlet and the outlet can include a valve. The first section can include the first chamber and the second section can include the second chamber. The conduit can be in one of the first or second sections.
The first composition can include injectable polymer particles. The particles can be embolic particles. The second composition can be a contrast agent.
Alternatively, the second composition can include an anticancer agent.
The syringe can include a conduit between the compartments. A first component including injectable particles is loaded into at least one compartment and a second component is loaded into the second compartment. The first component and the second component are mixed in the syringe by flowing at least one of the components through the conduit. The second component can include a contrast agent. The second component can include a drug.
The method can include loading a second composition in the second compartment. The second composition can include polymer particles. The first component and second component can be delivered sequentially.
The first component and the second component can include polymer particles of different sizes or alternatively, of different shapes. The first component can include particles that are substantially spherical.
Embodiments may include one or more advantages. For example, pre-mixing the components may be undesirable because the shelf life of the mixed composition may be reduced for e.g., due to chemical interactions between a contrast agent and embolic particles.
The details of one or more embodiments of the invention are set forth in the accompanying drawings and the description below. Other features, aspects, and advantages of the invention will be apparent from the description and drawings, and from the claims.
DESCRIPTION OF DRAWINGS
FIG lA is a cross-sectional schematic of a syringe apparatus for mixing and delivery of a composition into the body.
FIG 1B is an enlarged cross-sectional view showing a failure membrane of the syringeofFIG lA.
FIG IC is a top view of the failure membrane of the syringe of FIG lA.
FIG 1D illustrates mixing of the components using the syringe of FIG lA.
FIG lE illustrates delivery of a mixture through a catheter using the syringe of FIG lA.
FIG 2 is a schematic of a kit for mixing and delivery of a composition.
FIG 3A is a cross-sectional schematic of a syringe apparatus for mixing and delivery of a composition into the body.
FIG 3B is a top view of a failure membrane of the syringe of FIG 3A.
FIGS. 3C and 3D illustrate mixing of the components of a composition using the syringe system of FIG 3A.
FIG 3E illustrates delivery of a mixture through a catheter using the syringe of FIG 3A.
FIG 4A is a cross-sectional schematic of a syringe apparatus for mixing and delivery of a composition into the body.
FIG 4B illustrates mixing of the components of a composition using the syringe of FIG 4A
FIG 4C illustrates delivery of a composition through a catheter using the syringe of FIG 4A.
FIG 4D is a top view of a plunger lock of the syringe of FIG 4A.
FIG SA is a cross-sectional schematic of a syringe apparatus for mixing and delivery of particles of different sizes.
FIG 5B is a cross-sectional schematic of a syringe apparatus for mixing and delivery of particles of different shapes.
Like reference symbols in the various drawings indicate like elements.
DETAILED DESCRIPTION
Referring to FIG lA, a syringe apparatus 1 includes a body with an upper compartment 2, a lower compartment 3, a plunger 4 with a plunger base 1 l, a membrane 5, and a connector 9, which could be a luer connector, fitted with a stopcock 10. The lower compartment 3 contains a contrast agent 6 and the upper compartment 2 contains a combination of particles such as embolic particles 7 and a hydrating fluid such as saline 8. The upper compartment 2 and lower compartment 3 are fitted together at junction 19. The membrane 5 can be made of a polymer material or of cellulose based materials, such as cellulose acetate, that provides a liquid-tight seal between the upper and lower compartments so that the contrast agent may be isolated from interaction with the embolic material and saline mixture until the time of injection into the body.
Referring to FIGS. 1B and 1C, expanded views of the membrane 5 are illustrated. The membrane 5 has a failure region 13 and a hinge region 14. In one embodiment, the failure and hinge regions can be regions of reduced thickness.
The thickness of the failure region 13 is less than the thickness of the hinge region 14 such that the membrane will fail preferentially at the failure region 13 and bend preferentially at the hinge region 14, in response to pressure increase in the upper compartment 2. Referring to FIG 1C, a top view of the membrane 5 is illustrated showing the failure region 13 extending substantially around most of the circumference of the membrane, and the hinge region 14 extending along a short segment of the circumference. The reduced thickness regions of the membrane can be formed by heating, scoring or laser ablation.
Refernng to FIG 1D, with the stopcock 10 closed, pressure is applied in the upper compartment by depressing the plunger. The applied pressure on the failure membrane 5 causes it to rupture at the failure region 13 and to bend at the hinge region 14. The embolic particles and saline in the upper compartment 2 travel to the lower compartment 3 and mix with the contrast agent to form the mixed embolic composition 15. Because the embolic particles are initially located in the upper compartment and the contrast in the lower compartment, the particles fall into the contrast solution in a turbulent manner which enhances mixing and the creation of a uniform suspension of the particles in the mixture.
Referring to FIG lE, the stopcock 10 is opened to allow the mixed embolic composition 15 to pass via the connector 9, through a catheter 16 for injection into the body (not shown). The plunger can be further lowered to apply pressure for injecting the mixture into the body. In other embodiments, the stopcock 10 can be eliminated where the flow resistance of the syringe outlet and any attached delivery apparatus, such as a catheter, is sufficient to retard flow of solution in response to the pressure in the syringe after rupturing the membrane. The plunger base 11, particularly its circumference, may be made of a flexible rubbery material, such as an elastomeric polymeric material, that can deflect or bend when it engages the membrane so that the plunger can be lowered beyond the membrane into the lower compartment for injection of the mixture into the body.
Referring to FIG 2, a syringe kit is illustrated. The kit includes a syringe barrel made of two detachable sections, 20 and 22, defining the upper compartment 2 and the lower compartment 3, a plunger 4 with a base 11, a vial 24 of embolic material 7 in saline 8, and a vial 26 of contrast agent 6. The upper section 20 of the syringe apparatus has a female-type connector 21 at its bottom end to fit with a male-type connector 23 at the top of the lower section 22. The connection between the upper and lower sections can be, for example, a pressfit, threaded or luer type connection. The lower section 22 has a connector 9 fitted with a stopcock 10. Failure membrane 5 can be placed between the upper and lower sections or can be preattached to one of the sections; in FIG 2 the membrane is attached to the upper section. For use, the syringe apparatus is assembled as follows: Stopcock 10 is closed and contrast solution 6 from vial 26 is placed in the lower compartment 3 and the upper section is assembled with the lower section. Embolic material 7 along with saline solution 8 is placed in the upper compartment from vial 24. The plunger 4 is then placed in the upper compartment to complete the syringe assembly. The syringe can be provided commercially as a kit with the compartments preloaded with the appropriate components.
Referring to FIGS. 3A-3E, another embodiment of the syringe apparatus is illustrated. Here the failure membrane 30 is weakened across the center 31, as illustrated in FICz 3B, for rupture on application of pressure. The rest of the syringe apparatus is as in the first embodiment illustrated in FIG 1. Refernng to FIG
3C, the stopcock 10 is closed, and when pressure is applied to the upper compartment by depressing the plunger 4, the base 11 of the plunger conveys the applied pressure onto the failure membrane 30 causing its rupture at the weakened regions 31 (to form leaflets). The contents of the upper compartment 2 travel to the lower compartment 3 and mix with it to form the mixed embolic composition 1 S. Because the embolic particles are initially located in the upper compartment and the contrast in the lower compartment, the particles fall into the contrast solution in a turbulent manner which enhances mixing and the creation of a uniform suspension of the particles in the mixture. Referring to FIG 3D, the plunger 4 is withdrawn, which causes the embolic composition 15 to backfill the upper compartment. This causes further mixing of the components of the embolic mixture and also prepares the apparatus for delivery of the embolic composition 15. Referring to FIG 3E, stopcock 10 is opened and the plunger 4 is depressed to allow the embolic composition 1 S to pass through the connector 9 to the catheter 16 for injection into the body (not shown). In other embodiments, the upper or lower compartments, or both upper and lower compartments can include a vent valve on the sidewall, (upper vent valve 33 shown in phantom in FIG 3A) to enable pressure control within the syringe apparatus.
Referring to FIG 4A, in another embodiment, a syringe barrel 40 is provided that has parallel compartments, including a left compartment 41 with a plunger 42, and a right compartment 43, with a plunger 44, both plungers 42 and 44 are fitted with a plunger lock 50. The plunger locks 50 prevent accidental deployment of the plungers.
An expanded view of the plunger lock is illustrated in FIG 4D. The plunger lock 50 includes a frame 54 consisting of a stationary vertical strip 56 placed towards one end of the frame and a movable vertical strip 57 placed towards the other end of the frame, with a threaded hole 58 at the center of the strip 57, through which a screw 59 is passed. The space between the two strips 56 and 57 houses the stem of the plunger. In use, to lock the plunger and prevent its deployment, the strip 57 is moved until the stem of the plunger is tightly held between strips 56 and 57. Counterclockwise movement of the screw 59 further secures the plunger tightly between the two strips 56 and 57. To unlock the plunger for deployment, the screw 59 is turned clockwise and the strip 57 is moved away from the plunger which loosens the grip of the two strips 57 and 58 on the stem of the plunger and unlocks the plunger for deployment. The plunger locks can be made of a metallic or polymeric material. To place the plunger lock 50 on the stem of the plunger, the plunger lock 50 is unlocked, the strip 57 is moved towards the frame, and the lock is slid onto the stem of the plunger from the top and is placed in any desired position on the stem of the plunger.
The compartments are divided by a central divider 45 with a pressure-activated two-way valve 46 at the end of the central divider 45, connecting the two compartments. The pressure-activated valve can include a polymer membrane 47 that can flex into either compartment based on the pressure differential between the compartments. A connector 48, at the bottom of the syringe assembly communicates with both compartments of the syringe and is fitted with a stopcock 49. The left compartment 41 contains the contrast solution 6, and the right compartment 43 contains a mixture of embolic particles 7 and saline solution 8.
Referring to FIG 4B, the stopcock 49 is closed, the two plunger locks 50 on the left and right plungers 42 and 44 are unlocked, and the right plunger 44 is lowered causing the membrane 47 to flex into the left compartment and the valve 46 to open.
Embolic particles and saline travel to the left compartment (arrow) and mix with the contrast solution to form the embolic mixture 15. Further thorough mixing may be achieved by repeated alternate operation of the two plungers, 42 and 44.
Referring to Fig 4C, the stopcock 49 is opened, the two plungers 42 and 44 are simultaneously depressed such that the embolic mixture 15 passes via the connector 48 through the catheter 16 for injection into the body (not shown). (Alternatively, the plungers can be depressed sequentially.) In other embodiments, the valve membrane can be a failure membrane.
Referring to FIG. SA and FIG. SB, another embodiment of the syringe apparatus is illustrated. In this embodiment, there is no two-way valve connecting the two compartments. The central divider 45 extends up to the connector 48 at the bottom of the syringe assembly. Referring to FIG. SA, the left and right compartments 41 and 43 contain two different sizes of embolic particles, a smaller size 60, and a larger size 62, mixed with saline and/or contrast agent. Refernng to FIG. SB, the left and right compartments 41 and 43 contain two different shapes, a spherical shape 64, and an irregular shape 66, of embolic particles mixed with saline and or contrast agent. The rest of the syringe apparatus is as in the embodiment described in FIG. 4.
The arrangement allows delivery of two different sizes of embolic particles sequentially or simultaneously by sequential or simultaneous operation of the plungers.
For example, smaller particles can be delivered first to travel to smaller diameter vessels, followed by larger particles to occlude vessels of larger diameter, upstream of the small diameter vessels. Alternatively, two different shapes of embolic particles can be delivered sequentially (or simultaneously). For example, spherical particles may be delivered first to aggregate and occlude distal regions and the irregular particles may be delivered second for more proximal aggregation.
In use, embolic particles in saline are disposed in the compartments from the top of the syringe, after removing the plungers. Contrast agent is drawn into each compartment from a supply in communication with the connector 48 by releasing the appropriate plunger lock and withdrawing the appropriate plunger. The syringe can be provided commercially as a kit with the compartments preloaded with the appropriate components. For injection into the body, the embolic composition with the desired embolic particle size and shape is injected into the body by release of the appropriate plunger lock, opening the stopcock 49, and depressing the appropriate plunger.
The mixing and delivery system discussed above can be used to deliver a number of compositions. Suitable embolic particles are polymer particles.
Preferred particles are spherical particles formed of polyvinyl alcohol, as discussed in "Embolization", USSN 10/215,594, filed August 9, 2002, the entire contents of which is incorporated herein by reference. A suitable contrast agent is Omnipaque (Nycomed, Buckinghamshire, UK). (Omnipaque is an aqueous solution of iohexol, N.N.-Bis (2,3-dihydroxypropyl)-T-[N-(2,3-dihydroxypropyl)-acetamide]-2,4,6-trilodo-isophthalamide; Omnipaque 300 contains 647 mg of iohexol equivalent to 300 mg of organic iodine per ml). The syringe system can be used to premix and deliver other agents. For example, the systems can be used for mixing of drug agents, such as anti-cancer agents, with polymer particles as described in USSN 10/232,265, filed August 30, 2002. The system can be used to premix compositions without particles. A
valve, such as in Fig. 4A can be used instead of the failure membrane in Fig. lA. A
membrane can be used that is not pressure-activated. For example, the membrane can be deflected by a control lever operable from outside of the syringe barrel.
In another example, a sharpened member can be located on the plunger head that pierces the membrane.
Still further embodiments are in the following claims.
DESCRIPTION OF DRAWINGS
FIG lA is a cross-sectional schematic of a syringe apparatus for mixing and delivery of a composition into the body.
FIG 1B is an enlarged cross-sectional view showing a failure membrane of the syringeofFIG lA.
FIG IC is a top view of the failure membrane of the syringe of FIG lA.
FIG 1D illustrates mixing of the components using the syringe of FIG lA.
FIG lE illustrates delivery of a mixture through a catheter using the syringe of FIG lA.
FIG 2 is a schematic of a kit for mixing and delivery of a composition.
FIG 3A is a cross-sectional schematic of a syringe apparatus for mixing and delivery of a composition into the body.
FIG 3B is a top view of a failure membrane of the syringe of FIG 3A.
FIGS. 3C and 3D illustrate mixing of the components of a composition using the syringe system of FIG 3A.
FIG 3E illustrates delivery of a mixture through a catheter using the syringe of FIG 3A.
FIG 4A is a cross-sectional schematic of a syringe apparatus for mixing and delivery of a composition into the body.
FIG 4B illustrates mixing of the components of a composition using the syringe of FIG 4A
FIG 4C illustrates delivery of a composition through a catheter using the syringe of FIG 4A.
FIG 4D is a top view of a plunger lock of the syringe of FIG 4A.
FIG SA is a cross-sectional schematic of a syringe apparatus for mixing and delivery of particles of different sizes.
FIG 5B is a cross-sectional schematic of a syringe apparatus for mixing and delivery of particles of different shapes.
Like reference symbols in the various drawings indicate like elements.
DETAILED DESCRIPTION
Referring to FIG lA, a syringe apparatus 1 includes a body with an upper compartment 2, a lower compartment 3, a plunger 4 with a plunger base 1 l, a membrane 5, and a connector 9, which could be a luer connector, fitted with a stopcock 10. The lower compartment 3 contains a contrast agent 6 and the upper compartment 2 contains a combination of particles such as embolic particles 7 and a hydrating fluid such as saline 8. The upper compartment 2 and lower compartment 3 are fitted together at junction 19. The membrane 5 can be made of a polymer material or of cellulose based materials, such as cellulose acetate, that provides a liquid-tight seal between the upper and lower compartments so that the contrast agent may be isolated from interaction with the embolic material and saline mixture until the time of injection into the body.
Referring to FIGS. 1B and 1C, expanded views of the membrane 5 are illustrated. The membrane 5 has a failure region 13 and a hinge region 14. In one embodiment, the failure and hinge regions can be regions of reduced thickness.
The thickness of the failure region 13 is less than the thickness of the hinge region 14 such that the membrane will fail preferentially at the failure region 13 and bend preferentially at the hinge region 14, in response to pressure increase in the upper compartment 2. Referring to FIG 1C, a top view of the membrane 5 is illustrated showing the failure region 13 extending substantially around most of the circumference of the membrane, and the hinge region 14 extending along a short segment of the circumference. The reduced thickness regions of the membrane can be formed by heating, scoring or laser ablation.
Refernng to FIG 1D, with the stopcock 10 closed, pressure is applied in the upper compartment by depressing the plunger. The applied pressure on the failure membrane 5 causes it to rupture at the failure region 13 and to bend at the hinge region 14. The embolic particles and saline in the upper compartment 2 travel to the lower compartment 3 and mix with the contrast agent to form the mixed embolic composition 15. Because the embolic particles are initially located in the upper compartment and the contrast in the lower compartment, the particles fall into the contrast solution in a turbulent manner which enhances mixing and the creation of a uniform suspension of the particles in the mixture.
Referring to FIG lE, the stopcock 10 is opened to allow the mixed embolic composition 15 to pass via the connector 9, through a catheter 16 for injection into the body (not shown). The plunger can be further lowered to apply pressure for injecting the mixture into the body. In other embodiments, the stopcock 10 can be eliminated where the flow resistance of the syringe outlet and any attached delivery apparatus, such as a catheter, is sufficient to retard flow of solution in response to the pressure in the syringe after rupturing the membrane. The plunger base 11, particularly its circumference, may be made of a flexible rubbery material, such as an elastomeric polymeric material, that can deflect or bend when it engages the membrane so that the plunger can be lowered beyond the membrane into the lower compartment for injection of the mixture into the body.
Referring to FIG 2, a syringe kit is illustrated. The kit includes a syringe barrel made of two detachable sections, 20 and 22, defining the upper compartment 2 and the lower compartment 3, a plunger 4 with a base 11, a vial 24 of embolic material 7 in saline 8, and a vial 26 of contrast agent 6. The upper section 20 of the syringe apparatus has a female-type connector 21 at its bottom end to fit with a male-type connector 23 at the top of the lower section 22. The connection between the upper and lower sections can be, for example, a pressfit, threaded or luer type connection. The lower section 22 has a connector 9 fitted with a stopcock 10. Failure membrane 5 can be placed between the upper and lower sections or can be preattached to one of the sections; in FIG 2 the membrane is attached to the upper section. For use, the syringe apparatus is assembled as follows: Stopcock 10 is closed and contrast solution 6 from vial 26 is placed in the lower compartment 3 and the upper section is assembled with the lower section. Embolic material 7 along with saline solution 8 is placed in the upper compartment from vial 24. The plunger 4 is then placed in the upper compartment to complete the syringe assembly. The syringe can be provided commercially as a kit with the compartments preloaded with the appropriate components.
Referring to FIGS. 3A-3E, another embodiment of the syringe apparatus is illustrated. Here the failure membrane 30 is weakened across the center 31, as illustrated in FICz 3B, for rupture on application of pressure. The rest of the syringe apparatus is as in the first embodiment illustrated in FIG 1. Refernng to FIG
3C, the stopcock 10 is closed, and when pressure is applied to the upper compartment by depressing the plunger 4, the base 11 of the plunger conveys the applied pressure onto the failure membrane 30 causing its rupture at the weakened regions 31 (to form leaflets). The contents of the upper compartment 2 travel to the lower compartment 3 and mix with it to form the mixed embolic composition 1 S. Because the embolic particles are initially located in the upper compartment and the contrast in the lower compartment, the particles fall into the contrast solution in a turbulent manner which enhances mixing and the creation of a uniform suspension of the particles in the mixture. Referring to FIG 3D, the plunger 4 is withdrawn, which causes the embolic composition 15 to backfill the upper compartment. This causes further mixing of the components of the embolic mixture and also prepares the apparatus for delivery of the embolic composition 15. Referring to FIG 3E, stopcock 10 is opened and the plunger 4 is depressed to allow the embolic composition 1 S to pass through the connector 9 to the catheter 16 for injection into the body (not shown). In other embodiments, the upper or lower compartments, or both upper and lower compartments can include a vent valve on the sidewall, (upper vent valve 33 shown in phantom in FIG 3A) to enable pressure control within the syringe apparatus.
Referring to FIG 4A, in another embodiment, a syringe barrel 40 is provided that has parallel compartments, including a left compartment 41 with a plunger 42, and a right compartment 43, with a plunger 44, both plungers 42 and 44 are fitted with a plunger lock 50. The plunger locks 50 prevent accidental deployment of the plungers.
An expanded view of the plunger lock is illustrated in FIG 4D. The plunger lock 50 includes a frame 54 consisting of a stationary vertical strip 56 placed towards one end of the frame and a movable vertical strip 57 placed towards the other end of the frame, with a threaded hole 58 at the center of the strip 57, through which a screw 59 is passed. The space between the two strips 56 and 57 houses the stem of the plunger. In use, to lock the plunger and prevent its deployment, the strip 57 is moved until the stem of the plunger is tightly held between strips 56 and 57. Counterclockwise movement of the screw 59 further secures the plunger tightly between the two strips 56 and 57. To unlock the plunger for deployment, the screw 59 is turned clockwise and the strip 57 is moved away from the plunger which loosens the grip of the two strips 57 and 58 on the stem of the plunger and unlocks the plunger for deployment. The plunger locks can be made of a metallic or polymeric material. To place the plunger lock 50 on the stem of the plunger, the plunger lock 50 is unlocked, the strip 57 is moved towards the frame, and the lock is slid onto the stem of the plunger from the top and is placed in any desired position on the stem of the plunger.
The compartments are divided by a central divider 45 with a pressure-activated two-way valve 46 at the end of the central divider 45, connecting the two compartments. The pressure-activated valve can include a polymer membrane 47 that can flex into either compartment based on the pressure differential between the compartments. A connector 48, at the bottom of the syringe assembly communicates with both compartments of the syringe and is fitted with a stopcock 49. The left compartment 41 contains the contrast solution 6, and the right compartment 43 contains a mixture of embolic particles 7 and saline solution 8.
Referring to FIG 4B, the stopcock 49 is closed, the two plunger locks 50 on the left and right plungers 42 and 44 are unlocked, and the right plunger 44 is lowered causing the membrane 47 to flex into the left compartment and the valve 46 to open.
Embolic particles and saline travel to the left compartment (arrow) and mix with the contrast solution to form the embolic mixture 15. Further thorough mixing may be achieved by repeated alternate operation of the two plungers, 42 and 44.
Referring to Fig 4C, the stopcock 49 is opened, the two plungers 42 and 44 are simultaneously depressed such that the embolic mixture 15 passes via the connector 48 through the catheter 16 for injection into the body (not shown). (Alternatively, the plungers can be depressed sequentially.) In other embodiments, the valve membrane can be a failure membrane.
Referring to FIG. SA and FIG. SB, another embodiment of the syringe apparatus is illustrated. In this embodiment, there is no two-way valve connecting the two compartments. The central divider 45 extends up to the connector 48 at the bottom of the syringe assembly. Referring to FIG. SA, the left and right compartments 41 and 43 contain two different sizes of embolic particles, a smaller size 60, and a larger size 62, mixed with saline and/or contrast agent. Refernng to FIG. SB, the left and right compartments 41 and 43 contain two different shapes, a spherical shape 64, and an irregular shape 66, of embolic particles mixed with saline and or contrast agent. The rest of the syringe apparatus is as in the embodiment described in FIG. 4.
The arrangement allows delivery of two different sizes of embolic particles sequentially or simultaneously by sequential or simultaneous operation of the plungers.
For example, smaller particles can be delivered first to travel to smaller diameter vessels, followed by larger particles to occlude vessels of larger diameter, upstream of the small diameter vessels. Alternatively, two different shapes of embolic particles can be delivered sequentially (or simultaneously). For example, spherical particles may be delivered first to aggregate and occlude distal regions and the irregular particles may be delivered second for more proximal aggregation.
In use, embolic particles in saline are disposed in the compartments from the top of the syringe, after removing the plungers. Contrast agent is drawn into each compartment from a supply in communication with the connector 48 by releasing the appropriate plunger lock and withdrawing the appropriate plunger. The syringe can be provided commercially as a kit with the compartments preloaded with the appropriate components. For injection into the body, the embolic composition with the desired embolic particle size and shape is injected into the body by release of the appropriate plunger lock, opening the stopcock 49, and depressing the appropriate plunger.
The mixing and delivery system discussed above can be used to deliver a number of compositions. Suitable embolic particles are polymer particles.
Preferred particles are spherical particles formed of polyvinyl alcohol, as discussed in "Embolization", USSN 10/215,594, filed August 9, 2002, the entire contents of which is incorporated herein by reference. A suitable contrast agent is Omnipaque (Nycomed, Buckinghamshire, UK). (Omnipaque is an aqueous solution of iohexol, N.N.-Bis (2,3-dihydroxypropyl)-T-[N-(2,3-dihydroxypropyl)-acetamide]-2,4,6-trilodo-isophthalamide; Omnipaque 300 contains 647 mg of iohexol equivalent to 300 mg of organic iodine per ml). The syringe system can be used to premix and deliver other agents. For example, the systems can be used for mixing of drug agents, such as anti-cancer agents, with polymer particles as described in USSN 10/232,265, filed August 30, 2002. The system can be used to premix compositions without particles. A
valve, such as in Fig. 4A can be used instead of the failure membrane in Fig. lA. A
membrane can be used that is not pressure-activated. For example, the membrane can be deflected by a control lever operable from outside of the syringe barrel.
In another example, a sharpened member can be located on the plunger head that pierces the membrane.
Still further embodiments are in the following claims.
Claims (27)
1. A mixing and delivery medical syringe system, comprising:
a barrel including first and second detachable sections, and first and second compartments communicable through a conduit.
a barrel including first and second detachable sections, and first and second compartments communicable through a conduit.
2. The system of claim 1, wherein the conduit includes a pressure-activated separator.
3. The system of claim 2, wherein the separator includes a failure membrane.
4. The system of claim 3, wherein the failure membrane includes a weakened region.
5. The system of claim 4, wherein the weakened region preferentially effects rupture about a center region of the membrane.
6. The system of claim 4 wherein the weakened region preferentially affects rupture such that an attachment portion is not ruptured.
7. The system of claim 1, wherein the pressure-activated conduit includes a valve.
8. The system of claim 1, wherein the first compartment and the second compartment are arranged serially along the barrel.
9. The system of claim 1, wherein the barrel includes a vent valve.
10. The system of claim 1, wherein the barrel includes a fluid outlet and the outlet includes a valve.
11. The system of claim 1, wherein the first section includes the first chamber and the second section includes the second chamber.
12. The system or claim 11, wherein the conduit is in one or the first or second sections.
13. A mixing and delivery medical syringe system including a barrel having first and second compartments arranged in parallel along the barrel, the compartments communicable through a pressure-activated conduit.
14. The system of claim 13 wherein the conduit includes a valve.
15. A kit for medicant mixing and delivery, comprising:
a syringe system including a barrel assembled from multiple sections, including a first section having a first chamber, and a second section having a second chamber, the syringe system including a conduit between the first and second chambers through which flow can be controlled, and a first container of a first composition, and a second container of a second composition.
a syringe system including a barrel assembled from multiple sections, including a first section having a first chamber, and a second section having a second chamber, the syringe system including a conduit between the first and second chambers through which flow can be controlled, and a first container of a first composition, and a second container of a second composition.
16. The kit of claim 15 wherein the first composition includes injectable polymer particles.
17. The kit of claim 16 wherein the particles are embolic particles.
18. The kit of claims 15 or 16 wherein the second composition is a contrast agent.
19. The kit of claims 15 or 16 wherein the second composition is an anticancer agent.
20. A method for delivering injectable polymer particles, the method comprising:
providing a syringe including a first compartment and a second compartment, loading a first component including injectable particles into at least one compartment, and actuating the syringe to deliver said particles.
providing a syringe including a first compartment and a second compartment, loading a first component including injectable particles into at least one compartment, and actuating the syringe to deliver said particles.
21. The method of claim 20, the method comprising:
providing a syringe including a conduit between said compartments, and loading a second component into said second compartment, and mixing said first component and said second component in the syringe by flowing at least one of said components through said conduit.
providing a syringe including a conduit between said compartments, and loading a second component into said second compartment, and mixing said first component and said second component in the syringe by flowing at least one of said components through said conduit.
22. The method of claim 21, wherein said second component includes contrast agent.
23. The method of claim 21, wherein said second component includes a drug.
24. The method of claim 20, the method comprising loading a second composition in said second compartment, said second composition including polymer particles and delivering said first component and second component sequentially.
25. The method of claim 24, wherein the first and second components include polymer particles of different sizes.
26. The method of claim 24, wherein the first and second components include polymer particles of different shapes.
27. The method of claim 26, wherein the first component includes particles that are substantially spherical.
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US10/278,248 | 2002-10-23 | ||
PCT/US2003/033674 WO2004037326A2 (en) | 2002-10-23 | 2003-10-22 | Mixing and delivery medical syringe system for therapeutic compositions |
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CA2503052A1 true CA2503052A1 (en) | 2004-05-06 |
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CA002503052A Abandoned CA2503052A1 (en) | 2002-10-23 | 2003-10-22 | Mixing and delivery medical syringe system for therapeutic compositions |
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EP (1) | EP1553999A2 (en) |
AU (1) | AU2003286639A1 (en) |
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Families Citing this family (56)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030212022A1 (en) * | 2001-03-23 | 2003-11-13 | Jean-Marie Vogel | Compositions and methods for gene therapy |
WO2001072281A2 (en) * | 2000-03-24 | 2001-10-04 | Biosphere Medical Inc. | Microspheres for active embolization |
US7462366B2 (en) | 2002-03-29 | 2008-12-09 | Boston Scientific Scimed, Inc. | Drug delivery particle |
US7053134B2 (en) * | 2002-04-04 | 2006-05-30 | Scimed Life Systems, Inc. | Forming a chemically cross-linked particle of a desired shape and diameter |
US7842377B2 (en) * | 2003-08-08 | 2010-11-30 | Boston Scientific Scimed, Inc. | Porous polymeric particle comprising polyvinyl alcohol and having interior to surface porosity-gradient |
US8012454B2 (en) * | 2002-08-30 | 2011-09-06 | Boston Scientific Scimed, Inc. | Embolization |
US7976823B2 (en) | 2003-08-29 | 2011-07-12 | Boston Scientific Scimed, Inc. | Ferromagnetic particles and methods |
US7901770B2 (en) | 2003-11-04 | 2011-03-08 | Boston Scientific Scimed, Inc. | Embolic compositions |
US7736671B2 (en) | 2004-03-02 | 2010-06-15 | Boston Scientific Scimed, Inc. | Embolization |
US8173176B2 (en) | 2004-03-30 | 2012-05-08 | Boston Scientific Scimed, Inc. | Embolization |
US7998106B2 (en) | 2004-05-03 | 2011-08-16 | Thorne Jr Gale H | Safety dispensing system for hazardous substances |
US7311861B2 (en) | 2004-06-01 | 2007-12-25 | Boston Scientific Scimed, Inc. | Embolization |
GB2409162B (en) * | 2004-10-06 | 2005-12-14 | Bhk Holding Ltd | Materials,methods,and apparatus for treating a body cavity |
US7581899B2 (en) * | 2004-11-30 | 2009-09-01 | James Alexander Corporation | Dispenser and process |
US8425550B2 (en) | 2004-12-01 | 2013-04-23 | Boston Scientific Scimed, Inc. | Embolic coils |
US7858183B2 (en) | 2005-03-02 | 2010-12-28 | Boston Scientific Scimed, Inc. | Particles |
US7727555B2 (en) | 2005-03-02 | 2010-06-01 | Boston Scientific Scimed, Inc. | Particles |
US7963287B2 (en) | 2005-04-28 | 2011-06-21 | Boston Scientific Scimed, Inc. | Tissue-treatment methods |
CN104815331A (en) | 2005-05-09 | 2015-08-05 | 生物领域医疗公司 | Compositions and methods using microspheres and non-ionic contrast agents |
US9463426B2 (en) | 2005-06-24 | 2016-10-11 | Boston Scientific Scimed, Inc. | Methods and systems for coating particles |
US8007509B2 (en) | 2005-10-12 | 2011-08-30 | Boston Scientific Scimed, Inc. | Coil assemblies, components and methods |
US8152839B2 (en) | 2005-12-19 | 2012-04-10 | Boston Scientific Scimed, Inc. | Embolic coils |
US8101197B2 (en) | 2005-12-19 | 2012-01-24 | Stryker Corporation | Forming coils |
US7947368B2 (en) | 2005-12-21 | 2011-05-24 | Boston Scientific Scimed, Inc. | Block copolymer particles |
US20080033366A1 (en) * | 2006-01-30 | 2008-02-07 | Surgica Corporation | Compressible intravascular embolization particles and related methods and delivery systems |
EP2368581B1 (en) * | 2006-01-30 | 2018-08-29 | Biosphere Medical, Inc. | Porous intravascular embolization particles and related methods |
DE102006015238A1 (en) * | 2006-03-30 | 2007-10-04 | S&C Polymer Silicon- und Composite-Spezialitäten GmbH | Disposable packaging for storage, mixing and extraction of multi-component materials for e.g. medicinal and dental applications, includes membrane ruptured by pointed object to permit mixing |
US7976234B2 (en) | 2006-04-28 | 2011-07-12 | James Alexander Corporation | Multi-chambered dispenser and process |
US8414927B2 (en) | 2006-11-03 | 2013-04-09 | Boston Scientific Scimed, Inc. | Cross-linked polymer particles |
US8382704B2 (en) * | 2006-12-29 | 2013-02-26 | Medrad, Inc. | Systems and methods of delivering a dilated slurry to a patient |
US8910830B2 (en) | 2007-12-18 | 2014-12-16 | James Alexander Corporation | Container assembly |
US8403178B2 (en) | 2007-12-18 | 2013-03-26 | James Alexander Corporation | Container assembly |
US8100294B2 (en) | 2007-12-18 | 2012-01-24 | James Alexander Corporation | Container assembly |
EP2234897B1 (en) | 2008-01-29 | 2012-03-07 | James Alexander Corporation | Dispenser |
US8834014B2 (en) * | 2008-03-24 | 2014-09-16 | Sashco, Inc. | System for providing custom colored sealing compound |
US8800816B2 (en) * | 2009-03-24 | 2014-08-12 | Sashco, Inc. | System and method of providing individual quantities of custom colored sealing compound |
US9107668B2 (en) * | 2008-03-25 | 2015-08-18 | Cook Medical Technologies Llc | Embolic particle mixing syringe |
EP2344578A2 (en) * | 2008-10-30 | 2011-07-20 | David Liu | Micro-spherical porous biocompatible scaffolds and methods and apparatus for fabricating same |
US20100256646A1 (en) * | 2009-04-01 | 2010-10-07 | Frank Pinal | Orthobiologics delivery tool |
US8657481B2 (en) * | 2010-01-15 | 2014-02-25 | Spine Wave, Inc. | Systems and methods for mixing fluids |
JP5960148B2 (en) * | 2010-11-08 | 2016-08-02 | アクティヴパック, インコーポレイテッド | Beneficial medicine distributor |
WO2012063825A1 (en) * | 2010-11-10 | 2012-05-18 | オリンパスメディカルシステムズ株式会社 | Surgical device and ultrasonic treatment method |
AU2010101255B4 (en) * | 2010-11-15 | 2011-09-22 | Lumsden, Andrew | A prefilled syringe for administering buffered lignocaine |
EP2508219B1 (en) * | 2011-04-05 | 2018-06-06 | Kpr U.S., Llc | Buffering agent delivery system for anesthetic syringe |
US8834449B2 (en) * | 2012-01-23 | 2014-09-16 | Ikomed Technologies, Inc. | Mixing syringe |
US9751056B2 (en) | 2012-01-23 | 2017-09-05 | Merit Medical Systems, Inc. | Mixing syringe |
US9744303B2 (en) | 2013-07-10 | 2017-08-29 | Merit Medical Systems, Inc. | Pre-loaded syringes and methods related thereto |
US11260177B1 (en) * | 2014-03-18 | 2022-03-01 | Yasser Sadek | Dental anesthetic buffer system |
WO2017089280A1 (en) * | 2015-11-27 | 2017-06-01 | Sanofi-Aventis Deutschland Gmbh | Injection apparatus |
US20180085555A1 (en) * | 2016-09-26 | 2018-03-29 | Boston Scientific Scimed, Inc. | Injection catheter |
US11324673B2 (en) | 2016-11-18 | 2022-05-10 | Miraki Innovation Think Tank Llc | Cosmetic appearance of skin |
US11266761B2 (en) * | 2016-12-05 | 2022-03-08 | Cast21, Inc. | System for forming a rigid support |
SG11201909305PA (en) | 2017-04-05 | 2019-11-28 | Miraki Innovation Think Tank Llc | Cold slurry containment |
CN110868968A (en) | 2017-04-05 | 2020-03-06 | 米拉基创新智库有限责任公司 | Delivery point-cooled slurry generation |
US10500342B2 (en) | 2017-08-21 | 2019-12-10 | Miraki Innovation Think Tank Llc | Cold slurry syringe |
WO2021026269A1 (en) * | 2019-08-06 | 2021-02-11 | Microvention, Inc. | Syringe |
Family Cites Families (343)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2275154A (en) * | 1940-07-10 | 1942-03-03 | United Drug Company | Method for making capsules |
US2609347A (en) | 1948-05-27 | 1952-09-02 | Wilson Christopher Lumley | Method of making expanded polyvinyl alcohol-formaldehyde reaction product and product resulting therefrom |
GB743789A (en) | 1953-02-22 | 1956-01-25 | Hubert Percival Schofield | Improvements in or relating to cartridges and the like tubular containers for use in dispensing liquids |
FR1099362A (en) | 1954-04-23 | 1955-09-05 | D Antibiotiques Et De Biolog L | Capsule syringe for drugs that only need to be mixed at the time of use |
DK106395C (en) * | 1965-04-30 | 1967-01-30 | Novo Terapeutisk Labor As | Syringe with two coaxial cylindrical chambers. |
JPS4820019B1 (en) | 1969-06-05 | 1973-06-18 | ||
US3737398A (en) | 1969-11-13 | 1973-06-05 | D Yamaguchi | Method of making a polyvinyl acetal sponge buff |
CS179075B1 (en) | 1974-11-26 | 1977-10-31 | Stoy Vladimir | Mode of manufacture of spherical particles from polymer |
US4076640A (en) * | 1975-02-24 | 1978-02-28 | Xerox Corporation | Preparation of spheroidized particles |
US3957933A (en) | 1975-03-05 | 1976-05-18 | General Atomic Company | Apparatus for producing microspherical particles and method for operating such apparatus |
JPS51135958A (en) | 1975-05-20 | 1976-11-25 | Fuji Photo Film Co Ltd | Method of making fine powder polymer having pores |
US4025686A (en) | 1975-06-26 | 1977-05-24 | Owens-Corning Fiberglas Corporation | Molded composite article and method for making the article |
US4034759A (en) | 1975-08-27 | 1977-07-12 | Xomed, Inc. | Moisture-expandable prosthesis |
US4098728A (en) | 1976-01-02 | 1978-07-04 | Solomon Rosenblatt | Medical surgical sponge and method of making same |
US4055377A (en) | 1976-08-03 | 1977-10-25 | Minnesota Mining And Manufacturing Company | Magnetically orientable retroreflectorization particles |
GB1591924A (en) * | 1976-10-25 | 1981-07-01 | Berger Jenson & Nicholson Ltd | Polymer aggregates |
US4159719A (en) | 1977-05-09 | 1979-07-03 | Xomed, Inc. | Moisture-expandable ear wick |
US4437858A (en) * | 1978-01-16 | 1984-03-20 | Ty Perla J | Separator disc and hypodermic syringe incorporating the same and method |
ES478736A1 (en) | 1978-03-23 | 1979-06-01 | Hoechst Ag | Polyvinyl alcohol pellets containing a plasticizer, and method for their preparation. |
DE2834539A1 (en) | 1978-08-07 | 1980-02-21 | Basf Ag | MACROPOROUS POLYMERS AS CARRIER MATERIAL FOR THE COVALENT BINDING OF PROTEINS |
US4793980A (en) | 1978-09-21 | 1988-12-27 | Torobin Leonard B | Hollow porous microspheres as substrates and containers for catalyst |
US4243794A (en) | 1978-10-10 | 1981-01-06 | Minnesota Mining And Manufacturing Company | Mixture of rough and spheroidized resin particles |
US4198318A (en) * | 1978-11-24 | 1980-04-15 | Conoco, Inc. | Production of high strength alumina spheres by hydrogelling corresponding slurries |
US4268495A (en) | 1979-01-08 | 1981-05-19 | Ethicon, Inc. | Injectable embolization and occlusion solution |
US4246208A (en) * | 1979-03-22 | 1981-01-20 | Xerox Corporation | Dust-free plasma spheroidization |
US4346712A (en) | 1979-04-06 | 1982-08-31 | Kuraray Company, Ltd. | Releasable balloon catheter |
US4412836A (en) * | 1979-04-27 | 1983-11-01 | The West Company, Incorporated | Syringe assembly |
US4246794A (en) * | 1979-07-23 | 1981-01-27 | Huntington Alloys, Inc. | Apparatus and method for ultrasonic inspection of round stock such as tubing, pipe and rod |
US4254768A (en) * | 1979-09-14 | 1981-03-10 | Ty Perla J | Hypodermic syringe |
HU184722B (en) | 1980-02-18 | 1984-10-29 | Laszlo Lazar | Therapeutically suitable silicone rubber mixture and therapeuticaid |
US4271281A (en) | 1980-05-29 | 1981-06-02 | American Hoechst Corporation | Process for preparing styrenic polymer particles |
DE3031737A1 (en) * | 1980-08-22 | 1982-04-01 | Bayer Ag, 5090 Leverkusen | METHOD FOR PRODUCING PEARL POLYMERISATS OF UNIFORM PARTICLE SIZE |
CA1166413A (en) * | 1980-10-30 | 1984-05-01 | Edward E. Timm | Process and apparatus for preparing uniform size polymer beads |
US4657756A (en) * | 1980-11-17 | 1987-04-14 | Schering Aktiengesellschaft | Microbubble precursors and apparatus for their production and use |
US4442843A (en) * | 1980-11-17 | 1984-04-17 | Schering, Ag | Microbubble precursors and methods for their production and use |
US4681119A (en) | 1980-11-17 | 1987-07-21 | Schering Aktiengesellschaft | Method of production and use of microbubble precursors |
NZ199916A (en) | 1981-03-11 | 1985-07-12 | Unilever Plc | Low density polymeric block material for use as carrier for included liquids |
US4622362A (en) | 1981-03-30 | 1986-11-11 | California Institute Of Technology | Polyacrolein microspheres |
US4678814A (en) | 1981-03-30 | 1987-07-07 | California Institute Of Technology | Polyacrolein microspheres |
US4413070A (en) | 1981-03-30 | 1983-11-01 | California Institute Of Technology | Polyacrolein microspheres |
CA1177811A (en) | 1981-04-13 | 1984-11-13 | Theo G. Spek | Process for the preparation of silica particles; silica particles with a narrow pore diameter distribution, catalysts made therefrom and use of these catalysts |
US4428869A (en) * | 1981-08-20 | 1984-01-31 | International Flavors & Fragrances Inc. | Cologne consisting of microcapsule suspension |
DE3270641D1 (en) | 1981-11-11 | 1986-05-22 | Contraves Ag | Syringe for a sequential injection of two fluids into blood vessels of living bodies |
US4456693A (en) | 1982-03-08 | 1984-06-26 | W. R. Grace & Co. | Hydrocracking catalyst |
US4452773A (en) | 1982-04-05 | 1984-06-05 | Canadian Patents And Development Limited | Magnetic iron-dextran microspheres |
US4472552A (en) | 1982-09-27 | 1984-09-18 | W. R. Grace & Co. | Continuous process for making solid, free-flowing water dispersible PVA-aldehyde reaction product |
US4459145A (en) | 1982-09-30 | 1984-07-10 | The United States Of America As Represented By The United States Department Of Energy | Fabrication of glass microspheres with conducting surfaces |
EP0112574A1 (en) | 1982-12-27 | 1984-07-04 | Meditec S.A. | Two-compartment prefilled syringe |
JPS59131355A (en) | 1983-01-17 | 1984-07-28 | 森下仁丹株式会社 | Multiple soft capsule |
DE3313947A1 (en) | 1983-04-15 | 1984-10-18 | Schering AG, 1000 Berlin und 4709 Bergkamen | MICROPARTICLES AND GAS BUBBLES CONTAINING ULTRASONIC CONTRASTING AGENTS |
DE3834705A1 (en) | 1988-10-07 | 1990-04-12 | Schering Ag | ULTRASONIC CONTRASTING AGENTS FROM GAS BUBBLES AND MICROPARTICLES CONTAINING FATTY ACID |
DE3313946A1 (en) | 1983-04-15 | 1984-10-18 | Schering AG, 1000 Berlin und 4709 Bergkamen | MICROPARTICLES AND GAS BUBBLES CONTAINING ULTRASONIC CONTRASTING AGENTS |
CA1225585A (en) * | 1983-06-30 | 1987-08-18 | Maria T. Litvinova | Composition for embolization of blood vessels |
US4492720A (en) * | 1983-11-15 | 1985-01-08 | Benjamin Mosier | Method of preparing microspheres for intravascular delivery |
US4573967A (en) * | 1983-12-06 | 1986-03-04 | Eli Lilly And Company | Vacuum vial infusion system |
US4671954A (en) | 1983-12-13 | 1987-06-09 | University Of Florida | Microspheres for incorporation of therapeutic substances and methods of preparation thereof |
US4597505A (en) * | 1984-04-09 | 1986-07-01 | Continental Disc Corporation | Rupture disc with selectively positioned initial buckling |
US4551436A (en) | 1984-04-11 | 1985-11-05 | General Electric Company | Fabrication of small dense silicon carbide spheres |
DE3414924A1 (en) | 1984-04-19 | 1985-10-31 | Klaus Dr.med. Dr.med.habil. 8000 München Draenert | COATED ANCHORAGE PART FOR IMPLANTS |
US4674480A (en) | 1984-05-25 | 1987-06-23 | Lemelson Jerome H | Drug compositions and methods of applying same |
FR2566384B1 (en) * | 1984-06-21 | 1986-09-05 | Saint Gobain Vitrage | IMPROVEMENTS IN TECHNIQUES FOR THE PRODUCTION OF GLASS MICROSPHERES |
DE3527482A1 (en) | 1984-07-31 | 1986-02-06 | Fuji Spinning Co., Ltd., Tokio/Tokyo | METHOD FOR PRODUCING GRAINY POROUS CHITOSAN |
GB8419708D0 (en) * | 1984-08-02 | 1984-09-05 | Shell Int Research | Preparation of silica spheres |
US4623706A (en) | 1984-08-23 | 1986-11-18 | The Dow Chemical Company | Process for preparing uniformly sized polymer particles by suspension polymerization of vibratorily excited monomers in a gaseous or liquid stream |
JPS61101242A (en) | 1984-10-22 | 1986-05-20 | Showa Denko Kk | Production of coated substance |
US4789501A (en) * | 1984-11-19 | 1988-12-06 | The Curators Of The University Of Missouri | Glass microspheres |
US4675113A (en) | 1984-11-28 | 1987-06-23 | University Patents, Inc. | Affinity chromatography using dried calcium alginate-magnetite separation media in a magnetically stabilized fluidized bed |
EP0184198B1 (en) | 1984-12-06 | 1989-03-01 | Kanegafuchi Kagaku Kogyo Kabushiki Kaisha | A method of preparation of droplets |
US5106903A (en) * | 1984-12-17 | 1992-04-21 | Lehigh University | Preparation of large particle size monodisperse latexes |
US4897255A (en) * | 1985-01-14 | 1990-01-30 | Neorx Corporation | Metal radionuclide labeled proteins for diagnosis and therapy |
JPH0678460B2 (en) | 1985-05-01 | 1994-10-05 | 株式会社バイオマテリアル・ユニバース | Porous transparent polyvinyl alcohol gel |
JPS61293911A (en) * | 1985-06-24 | 1986-12-24 | Teisan Seiyaku Kk | Sustained release preparation |
SE459005B (en) * | 1985-07-12 | 1989-05-29 | Aake Rikard Lindahl | SET TO MANUFACTURE SPHERICAL POLYMER PARTICLES |
USH915H (en) | 1985-07-22 | 1991-05-07 | Gibbs Marylu B | Controlled macroporous copolymer properties by removal of impurities in the diluent |
US4742086A (en) | 1985-11-02 | 1988-05-03 | Lion Corporation | Process for manufacturing porous polymer |
DE3543348A1 (en) | 1985-12-07 | 1987-06-11 | Bayer Ag | PEARL-SHAPED CROSS-NETWORKED MIXED POLYMERS WITH EPOXY AND BASIC AMINO GROUPS, METHOD FOR THE PRODUCTION THEREOF AND THEIR USE |
JPS62169723A (en) * | 1986-01-22 | 1987-07-25 | Teisan Seiyaku Kk | Sustained release preparation |
GB8610024D0 (en) | 1986-04-24 | 1986-05-29 | Unilever Plc | Porous structures |
US4929400A (en) | 1986-04-28 | 1990-05-29 | California Institute Of Technology | Production of monodisperse, polymeric microspheres |
US5262176A (en) | 1986-07-03 | 1993-11-16 | Advanced Magnetics, Inc. | Synthesis of polysaccharide covered superparamagnetic oxide colloids |
JPS6317904A (en) | 1986-07-09 | 1988-01-25 | Mitsubishi Chem Ind Ltd | Production of crosslinked porous polyvinyl alcohol particle |
US4743507A (en) | 1986-09-12 | 1988-05-10 | Franses Elias I | Nonspherical microparticles and method therefor |
US5114421A (en) | 1986-09-22 | 1992-05-19 | Polak Robert B | Medicament container/dispenser assembly |
CA1287459C (en) | 1986-10-01 | 1991-08-13 | Mukesh Jain | Process for the preparation of hollow microspheres |
US4859711A (en) | 1986-10-01 | 1989-08-22 | Alcan International Limited | Hollow microspheres |
US5263992A (en) | 1986-10-17 | 1993-11-23 | Bio-Metric Systems, Inc. | Biocompatible device with covalently bonded biocompatible agent |
DE3787700T3 (en) | 1986-10-29 | 1998-12-24 | Kanegafuchi Chemical Ind | Uniform polymer particles. |
US5292814A (en) * | 1987-04-29 | 1994-03-08 | Ernst Bayer | Process for the preparation of monodispersed polymer beads |
US4795741A (en) * | 1987-05-06 | 1989-01-03 | Biomatrix, Inc. | Compositions for therapeutic percutaneous embolization and the use thereof |
GB8713263D0 (en) | 1987-06-05 | 1987-07-08 | Unilever Plc | Spheroidal silica |
JPH0612993B2 (en) | 1987-08-10 | 1994-02-23 | 株式会社クラレ | Method for producing spherical microbe-immobilized moldings |
US4819637A (en) * | 1987-09-01 | 1989-04-11 | Interventional Therapeutics Corporation | System for artificial vessel embolization and devices for use therewith |
JPH0762054B2 (en) | 1987-10-13 | 1995-07-05 | 倉敷紡績株式会社 | Crosslinked polymer particles |
US4804366A (en) * | 1987-10-29 | 1989-02-14 | Baxter International Inc. | Cartridge and adapter for introducing a beneficial agent into an intravenous delivery system |
US4850978A (en) | 1987-10-29 | 1989-07-25 | Baxter International Inc. | Drug delivery cartridge with protective cover |
US4981625A (en) * | 1988-03-14 | 1991-01-01 | California Institute Of Technology | Monodisperse, polymeric microspheres produced by irradiation of slowly thawing frozen drops |
US4935009A (en) * | 1988-06-10 | 1990-06-19 | Caldwell James B | Emergency drug injection system |
FR2634376B1 (en) * | 1988-07-21 | 1992-04-17 | Farmalyoc | NOVEL SOLID AND POROUS UNIT FORM COMPRISING MICROPARTICLES AND / OR NANOPARTICLES, AS WELL AS ITS PREPARATION |
DE68922497T2 (en) | 1988-08-24 | 1995-09-14 | Marvin J Slepian | ENDOLUMINAL SEAL WITH BISDEGRADABLE POLYMERS. |
DE3829938A1 (en) | 1988-09-02 | 1990-03-29 | Hermann Hofmann | ORGANO-MINERAL DUENGER AND METHOD FOR THE PRODUCTION THEREOF |
US4933372A (en) | 1988-09-26 | 1990-06-12 | Supelco, Inc. | Porous rigid resins and process of preparation |
US5047438A (en) | 1988-09-26 | 1991-09-10 | Supelco, Inc. | Porous rigid resins and process of preparation |
US5681576A (en) | 1988-11-16 | 1997-10-28 | Mdv Technologies, Inc. | Method and composition for post surgical adhesion reduction |
DE3841401A1 (en) | 1988-12-08 | 1990-06-13 | Martin Lemperle | ALLOPLASTIC IMPLANT |
US5258028A (en) | 1988-12-12 | 1993-11-02 | Ersek Robert A | Textured micro implants |
US4946899A (en) | 1988-12-16 | 1990-08-07 | The University Of Akron | Thermoplastic elastomers of isobutylene and process of preparation |
GB8900376D0 (en) | 1989-01-09 | 1989-03-08 | Nycomed As | Iodinated esters |
FR2641692A1 (en) * | 1989-01-17 | 1990-07-20 | Nippon Zeon Co | Plug for closing an opening for a medical application, and device for the closure plug making use thereof |
US5091205A (en) * | 1989-01-17 | 1992-02-25 | Union Carbide Chemicals & Plastics Technology Corporation | Hydrophilic lubricious coatings |
US5032117A (en) | 1989-01-30 | 1991-07-16 | Motta Louis J | Tandem syringe |
GB8905934D0 (en) * | 1989-03-15 | 1989-04-26 | Dow Europ Sa | A process for preparing adsorptive porous resin beads |
US5888930A (en) * | 1989-03-27 | 1999-03-30 | Bend Research, Inc. | Asymmetric microporous beads for controlled release |
US5354290A (en) | 1989-05-31 | 1994-10-11 | Kimberly-Clark Corporation | Porous structure of an absorbent polymer |
CA2017570C (en) * | 1989-05-31 | 2000-12-19 | James R. Gross | Porous structure of an absorbent polymer |
US5158573A (en) | 1989-06-09 | 1992-10-27 | American Medical Systems, Inc. | Injectable polymeric bodies |
US5116387A (en) | 1989-06-09 | 1992-05-26 | American Medical Systems, Inc. | Preparation of injectable polymeric bodies |
US5007940A (en) | 1989-06-09 | 1991-04-16 | American Medical Systems, Inc. | Injectable polymeric bodies |
US5190760A (en) * | 1989-07-08 | 1993-03-02 | Coopers Animal Health Limited | Solid pharmaceutical composition |
US5698271A (en) | 1989-08-22 | 1997-12-16 | Immunivest Corporation | Methods for the manufacture of magnetically responsive particles |
US5253991A (en) | 1989-11-20 | 1993-10-19 | Sumitomo Cement Co., Ltd. | Apparatus for producing spheroidal inorganic particulate material |
US5409125A (en) * | 1989-12-11 | 1995-04-25 | Aktiebolaget Astra | Unit dose container |
US5585112A (en) | 1989-12-22 | 1996-12-17 | Imarx Pharmaceutical Corp. | Method of preparing gas and gaseous precursor-filled microspheres |
US5469854A (en) | 1989-12-22 | 1995-11-28 | Imarx Pharmaceutical Corp. | Methods of preparing gas-filled liposomes |
US5580575A (en) | 1989-12-22 | 1996-12-03 | Imarx Pharmaceutical Corp. | Therapeutic drug delivery systems |
US5542935A (en) | 1989-12-22 | 1996-08-06 | Imarx Pharmaceutical Corp. | Therapeutic delivery systems related applications |
US5922304A (en) | 1989-12-22 | 1999-07-13 | Imarx Pharmaceutical Corp. | Gaseous precursor filled microspheres as magnetic resonance imaging contrast agents |
US6306427B1 (en) | 1989-12-28 | 2001-10-23 | Rhone-Poulenc Nutrition Animale | Pellets containing active ingredients protected against degradation in the rumen of ruminants |
US5435645A (en) | 1989-12-29 | 1995-07-25 | Tecres Spa | Process and apparatus for the mixing and direct emplacement of a two-component bone cement |
US5147937A (en) | 1990-03-22 | 1992-09-15 | Rohm And Haas Company | Process for making controlled, uniform-sized particles in the 1 to 50 micrometer range |
US5556610A (en) | 1992-01-24 | 1996-09-17 | Bracco Research S.A. | Gas mixtures useful as ultrasound contrast media, contrast agents containing the media and method |
JPH03297475A (en) | 1990-04-16 | 1991-12-27 | Ken Ishihara | Controlling method for emission of medicine by means of resonance sound wave |
US5514090A (en) | 1990-04-24 | 1996-05-07 | Science Incorporated | Closed drug delivery system |
US5137928A (en) | 1990-04-26 | 1992-08-11 | Hoechst Aktiengesellschaft | Ultrasonic contrast agents, processes for their preparation and the use thereof as diagnostic and therapeutic agents |
CA2016870C (en) | 1990-05-15 | 1994-03-29 | Arnie Drudik | Dispenser for storing and mixing several components |
AU636481B2 (en) | 1990-05-18 | 1993-04-29 | Bracco International B.V. | Polymeric gas or air filled microballoons usable as suspensions in liquid carriers for ultrasonic echography |
JP2514087Y2 (en) * | 1990-05-25 | 1996-10-16 | 幸三 牧田 | Balloon with detachable double-sided check valve |
US6291605B1 (en) | 1990-06-06 | 2001-09-18 | Clarence S. Freeman | Polymerization process with spraying step |
JP3286315B2 (en) | 1990-06-20 | 2002-05-27 | アドバンスト ポリマー システムズ,インコーポレイティド | Compositions and methods for controlled release of soluble actives |
US5202352A (en) * | 1990-08-08 | 1993-04-13 | Takeda Chemical Industries, Ltd. | Intravascular embolizing agent containing angiogenesis-inhibiting substance |
US5484584A (en) * | 1990-10-02 | 1996-01-16 | Board Of Regents, The University Of Texas System | Therapeutic and diagnostic use of modified polymeric microcapsules |
US5149543A (en) * | 1990-10-05 | 1992-09-22 | Massachusetts Institute Of Technology | Ionically cross-linked polymeric microcapsules |
US5120349A (en) | 1990-12-07 | 1992-06-09 | Landec Labs, Inc. | Microcapsule having temperature-dependent permeability profile |
US5171214A (en) | 1990-12-26 | 1992-12-15 | Abbott Laboratories | Drug storage and delivery system |
US5171217A (en) | 1991-02-28 | 1992-12-15 | Indiana University Foundation | Method for delivery of smooth muscle cell inhibitors |
US5147631A (en) | 1991-04-30 | 1992-09-15 | Du Pont Merck Pharmaceutical Company | Porous inorganic ultrasound contrast agents |
FR2676927B1 (en) | 1991-05-29 | 1995-06-23 | Ibf | MICROSPHERES FOR USE IN THERAPEUTIC VASCULAR OCCLUSIONS AND INJECTABLE SOLUTIONS CONTAINING THEM. |
DE69219331T3 (en) | 1991-06-03 | 2001-06-07 | Nycomed Imaging As | IMPROVEMENTS REGARDING CONTRAST AGENTS |
GB9116610D0 (en) | 1991-08-01 | 1991-09-18 | Danbiosyst Uk | Preparation of microparticles |
US5216096A (en) | 1991-09-24 | 1993-06-01 | Japan Synthetic Rubber Co., Ltd. | Process for the preparation of cross-linked polymer particles |
US5811447A (en) * | 1993-01-28 | 1998-09-22 | Neorx Corporation | Therapeutic inhibitor of vascular smooth muscle cells |
EP0535937B2 (en) * | 1991-10-01 | 2008-05-21 | Takeda Chemical Industries, Ltd. | Prolonged release microparticle preparation and production of the same |
JP3356447B2 (en) * | 1991-10-16 | 2002-12-16 | テルモ株式会社 | Vascular lesion embolic material composed of dried polymer gel |
US5258042A (en) | 1991-12-16 | 1993-11-02 | Henry Ford Health System | Intravascular hydrogel implant |
WO1993012877A1 (en) * | 1991-12-20 | 1993-07-08 | Allied-Signal Inc. | Low density materials having high surface areas and articles formed therefrom for use in the recovery of metals |
US5260002A (en) | 1991-12-23 | 1993-11-09 | Vanderbilt University | Method and apparatus for producing uniform polymeric spheres |
WO1993013111A1 (en) | 1991-12-24 | 1993-07-08 | E.I. Du Pont De Nemours And Company | Dual stabilized microparticles |
GB9200391D0 (en) | 1992-01-09 | 1992-02-26 | Nycomed As | Improvements in or relating to contrast agents |
GB9200388D0 (en) | 1992-01-09 | 1992-02-26 | Nycomed As | Improvements in or relating to contrast agents |
US6537574B1 (en) | 1992-02-11 | 2003-03-25 | Bioform, Inc. | Soft tissue augmentation material |
US5480644A (en) * | 1992-02-28 | 1996-01-02 | Jsf Consultants Ltd. | Use of injectable biomaterials for the repair and augmentation of the anal sphincters |
US5795562A (en) | 1992-03-06 | 1998-08-18 | Nycomed Imaging As | Contrast agents comprising gas-containing or gas-generating microparticles or microballoons |
CA2133756C (en) | 1992-04-06 | 2000-02-22 | Robert A. Ersek | Treatment of urological and gastric fluid reflux disorders by injection of micro particles |
DE69306844T2 (en) | 1992-04-10 | 1997-07-10 | Mitsubishi Chem Corp | Process for the preparation of spherical cross-linked acrylonitrile copolymers |
US6235313B1 (en) | 1992-04-24 | 2001-05-22 | Brown University Research Foundation | Bioadhesive microspheres and their use as drug delivery and imaging systems |
AU4198793A (en) | 1992-07-24 | 1994-01-27 | Takeda Chemical Industries Ltd. | Microparticle preparation and production thereof |
US5807323A (en) * | 1992-08-13 | 1998-09-15 | Science Incorporated | Mixing and delivery syringe assembly |
US6592859B1 (en) | 1992-08-20 | 2003-07-15 | Ethicon, Inc. | Controlled expansion sphincter augmentation media |
US5512604A (en) * | 1992-08-28 | 1996-04-30 | The Dow Chemical Company | Porous copolymers having a cellular polymeric structure suitable for preparing ion-exchange resins and adsorbents |
CA2144749A1 (en) * | 1992-09-16 | 1994-03-31 | Jo Klaveness | Improvements in or relating to contrast agents |
WO1994006460A1 (en) | 1992-09-21 | 1994-03-31 | Vitaphore Corporation | Embolization plugs for blood vessels |
DE4232755A1 (en) | 1992-09-26 | 1994-03-31 | Schering Ag | Microparticle preparations made from biodegradable copolymers |
KR960001417B1 (en) | 1992-09-26 | 1996-01-27 | 한국과학기술원 | Method for preparing an improved porous polymer bead |
GB9221329D0 (en) * | 1992-10-10 | 1992-11-25 | Delta Biotechnology Ltd | Preparation of further diagnostic agents |
US5382260A (en) | 1992-10-30 | 1995-01-17 | Interventional Therapeutics Corp. | Embolization device and apparatus including an introducer cartridge and method for delivering the same |
US5369163A (en) | 1992-11-13 | 1994-11-29 | Rohm And Haas Company | Process for preparing large dimension emulsion polymer particles, polymer product and uses thereof |
US5690666A (en) | 1992-11-18 | 1997-11-25 | Target Therapeutics, Inc. | Ultrasoft embolism coils and process for using them |
KR0171682B1 (en) * | 1992-12-01 | 1999-02-01 | 데츠로 히가시카와 | Syringe |
US5349957A (en) | 1992-12-02 | 1994-09-27 | Sterling Winthrop Inc. | Preparation and magnetic properties of very small magnetite-dextran particles |
JP3256583B2 (en) | 1992-12-10 | 2002-02-12 | 株式会社リコー | Electrophotographic toner and method for producing the same |
US5288763A (en) * | 1992-12-23 | 1994-02-22 | The Johns Hopkins University School Of Medicine | Porous, polymer beads and process of their preparation |
US6482436B1 (en) | 1993-01-29 | 2002-11-19 | Ferx Incorporated | Magnetically responsive composition |
US5328936A (en) | 1993-02-01 | 1994-07-12 | Rohm And Haas Company | Polymerization process for making porous polymeric particles |
US6090925A (en) | 1993-03-09 | 2000-07-18 | Epic Therapeutics, Inc. | Macromolecular microparticles and methods of production and use |
US5320639A (en) | 1993-03-12 | 1994-06-14 | Meadox Medicals, Inc. | Vascular plug delivery system |
US5701899A (en) | 1993-05-12 | 1997-12-30 | The Board Of Regents Of The University Of Nebraska | Perfluorobutane ultrasound contrast agent and methods for its manufacture and use |
US5695740A (en) | 1993-05-12 | 1997-12-09 | The Board Of Regents Of The University Of Nebraska | Perfluorocarbon ultrasound contrast agent comprising microbubbles containing a filmogenic protein and a saccharide |
US5567415A (en) | 1993-05-12 | 1996-10-22 | The Board Of Regents Of The University Of Nebraska | Ultrasound contrast agents and methods for their manufacture and use |
US5344867A (en) | 1993-06-14 | 1994-09-06 | The Bfgoodrich Company | Vinylidene chloride emulsion interpolymer composition |
US5716346A (en) * | 1993-07-02 | 1998-02-10 | Farris; Barry | Method and apparatus for loading syringes without the need for hypodermic needles |
EP2226085B1 (en) | 1993-07-19 | 2013-11-27 | Angiotech Pharmaceuticals, Inc. | Anti-angiogenic compositions and methods of use |
US5994341A (en) * | 1993-07-19 | 1999-11-30 | Angiogenesis Technologies, Inc. | Anti-angiogenic Compositions and methods for the treatment of arthritis |
US5398851A (en) * | 1993-08-06 | 1995-03-21 | River Medical, Inc. | Liquid delivery device |
US5397303A (en) * | 1993-08-06 | 1995-03-14 | River Medical, Inc. | Liquid delivery device having a vial attachment or adapter incorporated therein |
US5443495A (en) | 1993-09-17 | 1995-08-22 | Scimed Lifesystems Inc. | Polymerization angioplasty balloon implant device |
US5531716A (en) | 1993-09-29 | 1996-07-02 | Hercules Incorporated | Medical devices subject to triggered disintegration |
US5556391A (en) | 1993-10-01 | 1996-09-17 | Merocel Corporation | Surgical sponge device |
US5445614A (en) * | 1993-10-20 | 1995-08-29 | Habley Medical Technology Corporation | Pharmaceutical storage and mixing syringe |
EP0650739B1 (en) * | 1993-10-28 | 2003-02-26 | Medrad, Inc. | Total system for contrast delivery |
CN1068229C (en) | 1993-12-15 | 2001-07-11 | 勃勒柯研究有限公司 | Gas mixtures useful as ultrasound contrast media |
JP3770906B2 (en) | 1994-01-21 | 2006-04-26 | シルテックス、メディカル、リミテッド | Granular material |
US5417982A (en) | 1994-02-17 | 1995-05-23 | Modi; Pankaj | Controlled release of drugs or hormones in biodegradable polymer microspheres |
US5569468A (en) | 1994-02-17 | 1996-10-29 | Modi; Pankaj | Vaccine delivery system for immunization, using biodegradable polymer microspheres |
AU1702395A (en) | 1994-02-17 | 1995-09-04 | Pankaj Modi | Drugs, vaccines and hormones in polylactide coated microspheres |
WO1995025480A1 (en) | 1994-03-18 | 1995-09-28 | Cook Incorporated | Helical embolization coil |
US5431174A (en) | 1994-04-04 | 1995-07-11 | Via Medical Corporation | Method of fluid delivery and collection |
CA2188953A1 (en) | 1994-04-28 | 1995-11-09 | Harry Leibitzki | One-piece dispensing device for the contamination-free administration of medicaments (cytostatica) |
US5534589A (en) * | 1994-05-04 | 1996-07-09 | Minnesota Mining And Manufacturing Company | Repulpable plastic films |
ATE203755T1 (en) | 1994-05-15 | 2001-08-15 | Apbiotech Aktiebolag | METHOD FOR PRODUCING PARTICLES AND PARTICLES THAT CAN BE PRODUCED USING THIS PROCESS |
JP2535785B2 (en) | 1994-06-03 | 1996-09-18 | 工業技術院長 | Vascular embolic agent |
US5583162A (en) | 1994-06-06 | 1996-12-10 | Biopore Corporation | Polymeric microbeads and method of preparation |
US5639710A (en) | 1994-07-06 | 1997-06-17 | Zeneca Limited | Solid microspheres for agriculturally active compounds and process for their production |
ES2096521B1 (en) | 1994-08-10 | 1997-11-16 | Univ La Laguna | BIODEGRADABLE SYNTHETIC POLYMER MICROSPHERES IN THE MANUFACTURE AND ELABORATION OF REACTIVE EQUIPMENT FOR THE PREPARATION OF RADIOPHARMACEUTICAL MEDICINES. |
AU689622B2 (en) * | 1994-08-17 | 1998-04-02 | Boston Scientific Corporation | Implant, and method and device for inserting the implant |
US6099864A (en) | 1994-12-02 | 2000-08-08 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | In situ activation of microcapsules |
US5827531A (en) | 1994-12-02 | 1998-10-27 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Microcapsules and methods for making |
DK175166B1 (en) * | 1995-01-03 | 2004-06-21 | Cook William Europ | Method of manufacturing an assembly for placing an embolization coil in the vascular system and such assembly as well as an apparatus for advancing the assembly |
DE69632392T2 (en) | 1995-01-27 | 2004-09-16 | Scimed Life Systems, Inc., Maple Grove | Embolisation |
US6179817B1 (en) * | 1995-02-22 | 2001-01-30 | Boston Scientific Corporation | Hybrid coating for medical devices |
DE69521025T2 (en) | 1995-03-07 | 2001-10-04 | Menlo Care Inc | Means to improve sphincter function with controlled expansion |
US5569193A (en) | 1995-03-22 | 1996-10-29 | Abbott Laboratories | Syringe system accommodating separately storable prefilled containers for two constituents |
US5876372A (en) * | 1995-03-22 | 1999-03-02 | Abbott Laboratories | Syringe system accomodating seperate prefilled barrels for two constituents |
US5785682A (en) | 1995-03-22 | 1998-07-28 | Abbott Laboratories | Pre-filled syringe drug delivery system |
US5637087A (en) | 1995-03-22 | 1997-06-10 | Abbott Laboratories | Prefilled, two-constituent syringe |
WO1996029998A1 (en) * | 1995-03-28 | 1996-10-03 | Fidia Advanced Biopolymers S.R.L. | Nanospheres comprising a biocompatible polysaccharide |
US5779668A (en) | 1995-03-29 | 1998-07-14 | Abbott Laboratories | Syringe barrel for lyophilization, reconstitution and administration |
US5566729A (en) | 1995-04-06 | 1996-10-22 | Abbott Laboratories | Drug reconstitution and administration system |
US6428771B1 (en) | 1995-05-15 | 2002-08-06 | Pharmaceutical Discovery Corporation | Method for drug delivery to the pulmonary system |
US6312407B1 (en) | 1995-06-05 | 2001-11-06 | Medtronic Percusurge, Inc. | Occlusion of a vessel |
US6214331B1 (en) * | 1995-06-06 | 2001-04-10 | C. R. Bard, Inc. | Process for the preparation of aqueous dispersions of particles of water-soluble polymers and the particles obtained |
US5766147A (en) | 1995-06-07 | 1998-06-16 | Winfield Medical | Vial adaptor for a liquid delivery device |
US5657756A (en) | 1995-06-07 | 1997-08-19 | Ctf Systems Inc. | Method and systems for obtaining higher order gradiometer measurements with lower order gradiometers |
US6143211A (en) | 1995-07-21 | 2000-11-07 | Brown University Foundation | Process for preparing microparticles through phase inversion phenomena |
US6096344A (en) | 1995-07-28 | 2000-08-01 | Advanced Polymer Systems, Inc. | Bioerodible porous compositions |
US5840387A (en) | 1995-07-28 | 1998-11-24 | Aegis Biosciences L.L.C. | Sulfonated multiblock copolymer and uses therefor |
US5877224A (en) * | 1995-07-28 | 1999-03-02 | Rutgers, The State University Of New Jersey | Polymeric drug formulations |
US5558822A (en) | 1995-08-16 | 1996-09-24 | Gas Research Institute | Method for production of spheroidized particles |
US5888546A (en) * | 1995-08-28 | 1999-03-30 | The Regents Of The University Of California | Embolic material for endovascular occlusion of abnormal vasculature and method for using the same |
US5833361A (en) | 1995-09-07 | 1998-11-10 | Funk; James E. | Apparatus for the production of small spherical granules |
CA2161863A1 (en) | 1995-10-31 | 1997-05-01 | Michael Vivian Sefton | Angiogenic material and uses thereof |
US5752974A (en) | 1995-12-18 | 1998-05-19 | Collagen Corporation | Injectable or implantable biomaterials for filling or blocking lumens and voids of the body |
ES2176661T3 (en) | 1996-01-11 | 2002-12-01 | Duoject Inc | SUPPLY SYSTEM FOR PHARMACEUTICAL PRODUCTS PACKAGED IN VIALESPHARMACEUTICALS. |
US5702361A (en) * | 1996-01-31 | 1997-12-30 | Micro Therapeutics, Inc. | Method for embolizing blood vessels |
US5895398A (en) | 1996-02-02 | 1999-04-20 | The Regents Of The University Of California | Method of using a clot capture coil |
US6051247A (en) * | 1996-05-30 | 2000-04-18 | University Of Florida Research Foundation, Inc. | Moldable bioactive compositions |
US5855615A (en) * | 1996-06-07 | 1999-01-05 | Menlo Care, Inc. | Controller expansion sphincter augmentation media |
US5792478A (en) | 1996-07-08 | 1998-08-11 | Advanced Uro Science | Tissue injectable composition and method of use |
US5830178A (en) | 1996-10-11 | 1998-11-03 | Micro Therapeutics, Inc. | Methods for embolizing vascular sites with an emboilizing composition comprising dimethylsulfoxide |
US5695480A (en) | 1996-07-29 | 1997-12-09 | Micro Therapeutics, Inc. | Embolizing compositions |
US5741331A (en) * | 1996-07-29 | 1998-04-21 | Corvita Corporation | Biostable elastomeric polymers having quaternary carbons |
US5823198A (en) | 1996-07-31 | 1998-10-20 | Micro Therapeutics, Inc. | Method and apparatus for intravasculer embolization |
TW421658B (en) | 1996-07-31 | 2001-02-11 | Kanebo Ltd | Porious spherical particles and the preparation process for preparing thereof |
US5902832A (en) | 1996-08-20 | 1999-05-11 | Menlo Care, Inc. | Method of synthesizing swollen hydrogel for sphincter augmentation |
US5813411A (en) | 1996-08-20 | 1998-09-29 | Menlo Care, Inc. | Method of deforming tissue with a swollen hydrogel |
US5785642A (en) | 1996-10-18 | 1998-07-28 | Micro Therapeutics, Inc. | Methods for treating urinary incontinence in mammals |
US5756127A (en) | 1996-10-29 | 1998-05-26 | Wright Medical Technology, Inc. | Implantable bioresorbable string of calcium sulfate beads |
US6139963A (en) | 1996-11-28 | 2000-10-31 | Kuraray Co., Ltd. | Polyvinyl alcohol hydrogel and process for producing the same |
DE29724255U1 (en) | 1996-12-18 | 2000-10-05 | Alpha Bioverfahrenstechnik Gmb | Microcapsules |
US6090800A (en) * | 1997-05-06 | 2000-07-18 | Imarx Pharmaceutical Corp. | Lipid soluble steroid prodrugs |
AU6893898A (en) | 1997-04-10 | 1998-10-30 | Johns Hopkins University, The | Gaz syringe and package therefor |
JP4102459B2 (en) | 1997-05-14 | 2008-06-18 | 森下仁丹株式会社 | Seamless capsule for synthesizing biopolymer and method for producing the same |
US6056844A (en) | 1997-06-06 | 2000-05-02 | Triton Systems, Inc. | Temperature-controlled induction heating of polymeric materials |
AU7953698A (en) * | 1997-06-13 | 1998-12-30 | Micro Therapeutics, Inc. | Contoured syringe and novel luer hub and methods for embolizing blood ve ssels |
US6048908A (en) | 1997-06-27 | 2000-04-11 | Biopore Corporation | Hydrophilic polymeric material |
US5959073A (en) | 1997-07-07 | 1999-09-28 | Southwest Research Institute | Method for preparing polymeric beads |
US6056721A (en) | 1997-08-08 | 2000-05-02 | Sunscope International, Inc. | Balloon catheter and method |
EP1009317A4 (en) | 1997-08-28 | 2001-01-24 | Boston Scient Corp | System for implanting a cross-linked polysaccharide fiber and methods of forming and inserting the fiber |
US6538026B1 (en) | 1997-09-11 | 2003-03-25 | Provasis Therapeutics, Inc. | Compositions useful for remodeling body spaces |
US6476069B2 (en) | 1997-09-11 | 2002-11-05 | Provasis Therapeutics Inc. | Compositions for creating embolic agents and uses thereof |
CA2307764A1 (en) | 1997-11-07 | 1999-05-20 | Salviac Limited | Implantable occluder devices for medical use |
US5951160A (en) | 1997-11-20 | 1999-09-14 | Biomet, Inc. | Method and apparatus for packaging, mixing and delivering bone cement |
DE19752585B4 (en) | 1997-11-27 | 2007-06-28 | Inotech Ag | Device and method for encapsulating microbial, plant and animal cells or of biological and chemical substances |
US6159192A (en) | 1997-12-04 | 2000-12-12 | Fowles; Thomas A. | Sliding reconstitution device with seal |
BR9908339A (en) | 1998-02-23 | 2001-10-02 | Mnemoscience Gmbh | Method for the manufacture of an article with format memory, polymer composition with format memory and respective method of forming the field |
HU222543B1 (en) | 1998-02-23 | 2003-08-28 | Massachusetts Institute Of Technology | Biodegradable shape memory polymers |
US6003566A (en) | 1998-02-26 | 1999-12-21 | Becton Dickinson And Company | Vial transferset and method |
US6059766A (en) | 1998-02-27 | 2000-05-09 | Micro Therapeutics, Inc. | Gynecologic embolotherapy methods |
US6660301B1 (en) | 1998-03-06 | 2003-12-09 | Biosphere Medical, Inc. | Injectable microspheres for dermal augmentation and tissue bulking |
EP1062032B1 (en) | 1998-03-07 | 2004-03-31 | Inotech Ag | Method and device for capsulating microbial, plant and animal cells or biological and chemical substances |
US6047861A (en) * | 1998-04-15 | 2000-04-11 | Vir Engineering, Inc. | Two component fluid dispenser |
US6224794B1 (en) | 1998-05-06 | 2001-05-01 | Angiotech Pharmaceuticals, Inc. | Methods for microsphere production |
US6224630B1 (en) | 1998-05-29 | 2001-05-01 | Advanced Bio Surfaces, Inc. | Implantable tissue repair device |
EP1082072B8 (en) | 1998-06-04 | 2014-03-05 | New York University | Endovascular thin film devices for treating and preventing stroke |
US6267154B1 (en) | 1998-06-05 | 2001-07-31 | Abbott Laboratories | System for storing mixing and administering a drug |
AU4726299A (en) * | 1998-06-29 | 2000-01-17 | Orbon Corporation | Drug dispenser |
US6165193A (en) | 1998-07-06 | 2000-12-26 | Microvention, Inc. | Vascular embolization with an expansible implant |
US6099064A (en) | 1998-07-10 | 2000-08-08 | Lund Industries, Inc. | Windshield visor for motor vehicles |
US6264861B1 (en) | 1998-08-05 | 2001-07-24 | Xeikon Nv | Method for producing rounded polymeric particles |
US6315709B1 (en) | 1998-08-07 | 2001-11-13 | Stereotaxis, Inc. | Magnetic vascular defect treatment system |
US6152943A (en) * | 1998-08-14 | 2000-11-28 | Incept Llc | Methods and apparatus for intraluminal deposition of hydrogels |
CA2248592A1 (en) | 1998-08-31 | 2000-02-29 | Christopher D. Batich | Microspheres for use in the treatment of cancer |
US6296622B1 (en) | 1998-12-21 | 2001-10-02 | Micrus Corporation | Endoluminal device delivery system using axially recovering shape memory material |
FR2784580B1 (en) * | 1998-10-16 | 2004-06-25 | Biosepra Inc | POLYVINYL-ALCOHOL MICROSPHERES AND METHODS OF MAKING THE SAME |
US6238335B1 (en) | 1998-12-11 | 2001-05-29 | Enteric Medical Technologies, Inc. | Method for treating gastroesophageal reflux disease and apparatus for use therewith |
JP2000189511A (en) | 1998-12-25 | 2000-07-11 | Kaneka Medeikkusu:Kk | Embolization material |
US6162377A (en) | 1999-02-23 | 2000-12-19 | Alberta Research Council Inc. | Apparatus and method for the formation of uniform spherical particles |
US6296604B1 (en) | 1999-03-17 | 2001-10-02 | Stereotaxis, Inc. | Methods of and compositions for treating vascular defects |
US6306425B1 (en) | 1999-04-09 | 2001-10-23 | Southern Research Institute | Injectable naltrexone microsphere compositions and their use in reducing consumption of heroin and alcohol |
US6368658B1 (en) * | 1999-04-19 | 2002-04-09 | Scimed Life Systems, Inc. | Coating medical devices using air suspension |
CA2361129A1 (en) | 1999-05-21 | 2000-11-30 | Douglas R. Hayman | Interface needle and method for creating a blunt interface between delivered liquids |
US6280457B1 (en) | 1999-06-04 | 2001-08-28 | Scimed Life Systems, Inc. | Polymer covered vaso-occlusive devices and methods of producing such devices |
NZ517997A (en) | 1999-08-27 | 2002-11-26 | Southern Res Inst | Injectable, slow release partial opioid agonist or antagonist compositions and their use |
FR2797769B1 (en) | 1999-09-01 | 2003-07-25 | Cis Bio Int | RADIOPHARMACEUTICAL PRODUCTS AND THEIR PREPARATION PROCESS |
JP2001079011A (en) | 1999-09-14 | 2001-03-27 | Akira Morimoto | Embolization coil and its manufacture |
US6277392B1 (en) | 1999-09-16 | 2001-08-21 | Carbon Medical Technologies, Inc. | Tissue injectable composition |
US6238403B1 (en) | 1999-10-04 | 2001-05-29 | Microvention, Inc. | Filamentous embolic device with expansible elements |
US6602261B2 (en) | 1999-10-04 | 2003-08-05 | Microvention, Inc. | Filamentous embolic device with expansile elements |
KR100335866B1 (en) * | 2000-01-06 | 2002-05-10 | 박호군 | Microspheric Embolic Materials Having Duel Structure of Poly(Vinyl Acetate) Core/Poly(Vinyl Alcohol) Shell, and Method for Preparing The Same |
US6306419B1 (en) | 2000-02-23 | 2001-10-23 | Aegis Biosciences, Llc | Medical uses of styrene sulfonate polymers |
JP2003525682A (en) | 2000-03-06 | 2003-09-02 | シメッド ライフ システムズ インコーポレイテッド | Embolic agent visible under ultrasound |
JP4871476B2 (en) * | 2000-03-13 | 2012-02-08 | バイオコンパティブルズ ユーケー リミテッド | Embolization composition |
US6652883B2 (en) | 2000-03-13 | 2003-11-25 | Biocure, Inc. | Tissue bulking and coating compositions |
US6423332B1 (en) | 2000-05-26 | 2002-07-23 | Ethicon, Inc. | Method and composition for deforming soft tissues |
DE10026620A1 (en) | 2000-05-29 | 2002-03-07 | Gerhard Quelle | Biocompatible material for cell and tissue implantation, useful e.g. for drug release or cosmetic tissue augmentation, consisting of spherical particles having (semi-)permeable or porous outer shell and internal cavity |
US6355275B1 (en) * | 2000-06-23 | 2002-03-12 | Carbon Medical Technologies, Inc. | Embolization using carbon coated microparticles |
US6764463B1 (en) | 2000-06-27 | 2004-07-20 | Barry Farris | Method and needleless apparatus for the storage of a first substance followed by subsequent mixing with a second substance and transfer without ambient air incursion |
JP2002017848A (en) | 2000-07-12 | 2002-01-22 | Terumo Corp | Intravitally injectable particulate and method for preparing the same |
WO2002011696A2 (en) | 2000-08-08 | 2002-02-14 | Ev & M | Active tissue augmentation materials and method |
DE60140625D1 (en) | 2000-08-15 | 2010-01-07 | Univ Illinois | PROCESS FOR PRODUCING MICROPARTICLES |
US6394965B1 (en) | 2000-08-15 | 2002-05-28 | Carbon Medical Technologies, Inc. | Tissue marking using biocompatible microparticles |
WO2002026911A1 (en) | 2000-09-27 | 2002-04-04 | Microtek Laboratories, Inc. | Macrocapsules containing microencapsulated phase change materials |
AUPR098200A0 (en) | 2000-10-25 | 2000-11-16 | Sirtex Medical Limited | Production of low density radionuclide containing microspheres |
AUPR098300A0 (en) | 2000-10-25 | 2000-11-16 | Sirtex Medical Limited | Polymer based radionuclide containing microspheres |
AUPR098400A0 (en) | 2000-10-25 | 2000-11-16 | Sirtex Medical Limited | Production of radionuclide coated microspheres and seeds |
US6545097B2 (en) * | 2000-12-12 | 2003-04-08 | Scimed Life Systems, Inc. | Drug delivery compositions and medical devices containing block copolymer |
WO2003053325A2 (en) | 2000-12-13 | 2003-07-03 | Purdue Research Foundation | Microencapsulation of drugs by solvent exchange |
US6632531B2 (en) | 2001-02-15 | 2003-10-14 | Rohm And Haas Company | Porous particles, their aqueous dispersions, and method of preparation |
US6887857B2 (en) | 2001-04-27 | 2005-05-03 | Scimed Life Systems, Inc. | Microparticle protection of therapeutic agents |
US6723067B2 (en) * | 2001-07-26 | 2004-04-20 | David H. Nielson | Apparatus for delivering aerosolized fibrin endoscopically to a wound |
US20030032935A1 (en) * | 2001-08-10 | 2003-02-13 | Scimed Life Systems, Inc. | Packages facilitating convenient mixing and delivery of liquids |
US6692515B2 (en) * | 2001-11-07 | 2004-02-17 | Frank H. Boehm, Jr. | Surgical kit for repairing leaks in fluid carrying vessels and organs and method thereof |
US7218962B2 (en) | 2002-03-29 | 2007-05-15 | Boston Scientific Scimed, Inc. | Magnetically enhanced injection catheter |
JP4364649B2 (en) | 2002-03-29 | 2009-11-18 | ボストン サイエンティフィック リミテッド | Polymer particles used as tissue treatment substances |
US7131997B2 (en) * | 2002-03-29 | 2006-11-07 | Scimed Life Systems, Inc. | Tissue treatment |
US7094369B2 (en) | 2002-03-29 | 2006-08-22 | Scimed Life Systems, Inc. | Processes for manufacturing polymeric microspheres |
US7462366B2 (en) | 2002-03-29 | 2008-12-09 | Boston Scientific Scimed, Inc. | Drug delivery particle |
US7053134B2 (en) | 2002-04-04 | 2006-05-30 | Scimed Life Systems, Inc. | Forming a chemically cross-linked particle of a desired shape and diameter |
US7838699B2 (en) | 2002-05-08 | 2010-11-23 | Biosphere Medical | Embolization using degradable crosslinked hydrogels |
US7449236B2 (en) | 2002-08-09 | 2008-11-11 | Boston Scientific Scimed, Inc. | Porous polymeric particle comprising polyvinyl alcohol and having interior to surface porosity-gradient |
US20040076582A1 (en) * | 2002-08-30 | 2004-04-22 | Dimatteo Kristian | Agent delivery particle |
US8012454B2 (en) | 2002-08-30 | 2011-09-06 | Boston Scientific Scimed, Inc. | Embolization |
US7792568B2 (en) | 2003-03-17 | 2010-09-07 | Boston Scientific Scimed, Inc. | MRI-visible medical devices |
US7906148B2 (en) * | 2003-07-31 | 2011-03-15 | Boston Scientific Scimed, Inc. | Latex medical articles for release of antimicrobial agents |
US20050037047A1 (en) * | 2003-08-11 | 2005-02-17 | Young-Ho Song | Medical devices comprising spray dried microparticles |
-
2002
- 2002-10-23 US US10/278,248 patent/US7883490B2/en not_active Expired - Fee Related
-
2003
- 2003-10-22 CA CA002503052A patent/CA2503052A1/en not_active Abandoned
- 2003-10-22 WO PCT/US2003/033674 patent/WO2004037326A2/en not_active Application Discontinuation
- 2003-10-22 AU AU2003286639A patent/AU2003286639A1/en not_active Abandoned
- 2003-10-22 EP EP03777846A patent/EP1553999A2/en not_active Withdrawn
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AU2003286639A1 (en) | 2004-05-13 |
AU2003286639A8 (en) | 2004-05-13 |
WO2004037326A3 (en) | 2004-12-23 |
US20040092883A1 (en) | 2004-05-13 |
US7883490B2 (en) | 2011-02-08 |
EP1553999A2 (en) | 2005-07-20 |
WO2004037326A2 (en) | 2004-05-06 |
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FZDE | Discontinued |