US20030010718A1 - Hemodilution cap and methods of use in blood-processing procedures - Google Patents

Hemodilution cap and methods of use in blood-processing procedures Download PDF

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Publication number
US20030010718A1
US20030010718A1 US09/904,709 US90470901A US2003010718A1 US 20030010718 A1 US20030010718 A1 US 20030010718A1 US 90470901 A US90470901 A US 90470901A US 2003010718 A1 US2003010718 A1 US 2003010718A1
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United States
Prior art keywords
blood
outlet
inlet
filter
housing
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Abandoned
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US09/904,709
Inventor
Jeffrey Burbank
Martin Stillig
James Brugger
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NxStage Medical Inc
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NxStage Medical Inc
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Priority to US09/904,709 priority Critical patent/US20030010718A1/en
Assigned to NXSTAGE MEDICAL, INC. reassignment NXSTAGE MEDICAL, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: BRUGGER, JAMES M., BURBANK, JEFFREY H., STILLIG, MARTIN
Publication of US20030010718A1 publication Critical patent/US20030010718A1/en
Priority to US10/774,127 priority patent/US20050000882A1/en
Priority to US12/015,420 priority patent/US7776219B2/en
Abandoned legal-status Critical Current

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    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D63/00Apparatus in general for separation processes using semi-permeable membranes
    • B01D63/02Hollow fibre modules
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D63/00Apparatus in general for separation processes using semi-permeable membranes
    • B01D63/02Hollow fibre modules
    • B01D63/034Lumen open in more than two directions
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342Adding solutions to the blood, e.g. substitution solutions
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342Adding solutions to the blood, e.g. substitution solutions
    • A61M1/3424Substitution fluid path
    • A61M1/3431Substitution fluid path upstream of the filter
    • A61M1/3434Substitution fluid path upstream of the filter with pre-dilution and post-dilution
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/34Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342Adding solutions to the blood, e.g. substitution solutions
    • A61M1/3424Substitution fluid path
    • A61M1/3437Substitution fluid path downstream of the filter, e.g. post-dilution with filtrate
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M1/00Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3672Means preventing coagulation
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D61/00Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
    • B01D61/14Ultrafiltration; Microfiltration
    • B01D61/20Accessories; Auxiliary operations
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D61/00Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
    • B01D61/24Dialysis ; Membrane extraction
    • B01D61/30Accessories; Auxiliary operation
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D2313/00Details relating to membrane modules or apparatus
    • B01D2313/21Specific headers, end caps

Definitions

  • the present invention relates generally to devices and methods useful in preventing coagulation in filtered blood during hemofiltration. More specifically, the devices and methods provide a cap having a port, the cap adapted for attachment to a blood filter housing to provide hemodilution of blood as it enters and/or exits the filter.
  • the intrinsic system There are two separate coagulation pathways that activate factor X—the intrinsic system and the extrinsic system. Activation of the extrinsic system requires tissue thromboplastin (factor III), which is released from damaged tissue into the circulating blood to activate clotting.
  • the intrinsic system has all the factors necessary for coagulation contained in the circulating blood. The intrinsic system is, for example, partially responsible for clotting of blood in a test tube. Aggregation of platelets caused by stagnation of blood also facilitates blood coagulation.
  • the present invention provides devices and methods that prevent clotting of blood during blood-processing procedures, such as hemofiltration, hemodialysis, and hemodiafiltration. More particularly, blood is diluted by replacement fluid, such as saline, Ringer's lactate, or other physiological solutions, as it enters and/or exits the filter.
  • the device also known as a filter, is comprised of a bundle of hollow fiber membrane made of resins such as polysulfone that is fixed in a cylindrical housing with a potting material. The interior of the fibers is the blood flow path. The exterior of the fibers is the dialysate and/or waste space.
  • the potting material is typically a polyurethane material.
  • the cylindrical housing may have one or two access ports.
  • One port is for the hemofiltration filter, and two ports allow dialysate to flow through the housing contacting the exterior surface of the membrane for hemodialysis or hemodiafiltration.
  • the open fibers at the end of the cylindrical housing are covered at both ends with a cap.
  • One cap is the blood entry cap, the other is the blood exit cap.
  • the housing includes end plates at one or both ends, the end plates integral with the housing.
  • the exit cap is attached to the housing, in some cases removably attached, and generally at a position opposite the inlet cap.
  • the exit cap has an outlet for blood and a port adjacent the outlet for receiving replacement fluid.
  • the blood outlet, the replacement fluid port, the blood inlet, and/or the waste outlet of the filter assembly communicate with bond sockets adapted to receive flexible tubing.
  • the filter has an outlet or exit cap for blood at one end and an inlet or inlet cap at the other end, the cap having an inlet for blood and a port adjacent to the inlet for receiving dilution fluid, such as saline, Ringer's lactate, or other physiological solutions.
  • the housing also includes access ports for waste and ultrafiltrate.
  • the housing includes first and second caps at opposite ends and an outlet for waste and ultrafiltrate.
  • the first cap has an inlet for blood and a port adjacent to the inlet for receiving dilution fluid.
  • the second cap has an outlet for blood and a port adjacent to the outlet for receiving dilution fluid.
  • blood is passed through the blood inlet of the entry cap, through the filter membrane fibers, and through the blood outlet of the exit cap.
  • Replacement fluid or dilution fluid such as saline, Ringer's lactate, or other physiological solutions, is infused into the port adjacent the blood outlet to produce hemodilution at the blood outlet.
  • the fluid is infused into the port adjacent the blood inlet of the entry cap to produce hemodilution at the inlet.
  • fluid is infused into the port adjacent the blood inlet of the entry cap and into the port adjacent the blood outlet of the exit cap to produce hemodilution as blood enters and exits the filter housing.
  • the replacement fluid swirls in a circular pattern in a headspace that is defined by the gap between the filter and the cap. Swirling of the replacement fluid facilitates mixing of the fluid and the blood, thereby preventing hemoconcentration and stasis of blood, and sweeping any particles of thrombus away from the filter.
  • the advantages associated with the hemodilution cap described herein include (1) preventing coagulation during blood processing procedures, (2) manufacturing efficiency, i.e., reducing plastic used in disposable components, (3) eliminating up to two bonds and up to two components, (4) less expense in materials costs and manufacturing costs, (5) more robust system, not subject to tolerances like bonding two rigid parts, and (6) integration of parts saves labor, materials, and precious resources.
  • FIG. 1A depicts a filter within a housing for hemofiltration.
  • FIG. 1B depicts a filter within a housing having a replacement fluid port adjacent the blood outlet port for hemofiltration.
  • FIG. 1C depicts a filter within a housing having a replacement fluid port adjacent the blood inlet port for hemofiltration.
  • FIG. 1D depicts a filter within a housing having replacement fluid ports adjacent both the blood inlet port and the blood outlet port for hemofiltration.
  • FIG. 1E depicts a filter within a housing for hemodiafiltration having dialysate inlet and outlet ports.
  • FIG. 1F depicts a filter within a housing for hemodiafiltration having a replacement fluid port adjacent the blood outlet port.
  • FIG. 2 depicts a filter-housing cap having a replacement fluid port adjacent the blood outlet port for hemofiltration.
  • FIG. 3A depicts a cross-sectional view of a filter housing cap having a replacement fluid port adjacent the blood outlet port for hemofiltration.
  • FIG. 3B depicts another cross-sectional view of a filter housing cap having a replacement fluid port adjacent the blood outlet port for hemofiltration.
  • FIG. 3C depicts another cross-sectional view of a filter housing cap having a replacement fluid port adjacent the blood outlet port and a headspace for hemofiltration.
  • FIG. 4A depicts a fluid bond socket communicating with the blood outlet.
  • FIG. 4B depicts a fluid bond socket communicating with the replacement fluid port.
  • FIG. 5 depicts a filter-housing cap removably mounted on a filter housing for hemofiltration.
  • FIG. 6 depicts a filter-housing cap for hemofiltration, the cap being made of flexible PVC and having ribs for stability.
  • the hemofiltration device includes cylindrical housing 10 which contains filter fibers 20 that remove waste from blood passing through the fibers. It will be understood that any other suitable shape can be used for the housing. Housing 10 is equipped with entry cap 13 having blood inlet 11 . Waste and ultrafiltrate that are removed from the blood exits the housing through waste outlet 12 . Exit cap 30 is mounted on housing 10 opposite blood entry cap 13 . Headspace 31 is formed in the gap between filter fibers 20 and cap 30 and between filters 20 and cap 13 . Headspace 31 communicates with blood outlet 32 . Each of the inlet 11 waste outlet 12 and blood outlet 32 are adapted for attachment to flexible tubing sections that connect with a blood processing system.
  • cap 30 further includes replacement fluid inlet port 33 that communicates with headspace 31 .
  • Replacement fluid is infused through port 33 to effect hemodilution of blood exiting filter 20 .
  • the system thereby reconstitutes blood as close as possible to the exit from the filter fibers. In this way hemodilution is accomplished with one part (cap 30 ) and two bonds (one between tubing and port 32 , and another between tubing and port 33 ).
  • housing 10 includes cap 13 having blood inlet 11 and dilution fluid inlet port 15 that communicates with headspace 31 . Blood is diluted as it enters housing 10 , thereby helping to prevent coagulation.
  • housing 10 includes cap 13 having blood inlet and dilution fluid inlet port 15 that communicates with headspace 31 .
  • the housing also includes cap 30 having blood outlet 32 and fluid inlet port 33 that communicates with headspace 31 .
  • Dilution fluid is infused through port 33 and port 15 to effect hemodilution of blood entering and exiting filter 20 .
  • FIG. 1E shows a housing 10 designed for hemodiafiltration.
  • Housing 10 includes dialysate inlet 16 and dialysate outlet 12 to establish countercurrent dialysate flow.
  • Filter fiber membrane 20 is mounted within potting material 21 at both ends, where the potting material typically is a polyurethane material.
  • cap 30 further includes replacement fluid inlet port 33 that communicates with headspace 31 .
  • Replacement fluid is infused through port 33 to effect hemodilution of blood exiting filter 20 as described for other embodiments above. It will be understood that for hemodiafiltration, a hemodilution cap may be included alternatively on the inlet to effect pre-dilution of blood, and/or on both the inlet and outlet.
  • FIG. 2 shows a top view of cap 30 having blood outlet 32 and replacement fluid infusion port 33 .
  • replacement fluid such as saline, Ringer's lactate, sterile filtered dialysate, or other physiological solutions
  • Inlet blood flow rate will typically be 50-1000 mL/min, preferably 350-600 mL/min.
  • Infusion of dilution fluid at the exit cap will generally be 1-50% of inlet blood flow, preferably 20-30% in order to establish swirling.
  • Infusion port 33 includes bond socket 34
  • outlet 32 includes bond socket 35 .
  • Each bond socket is adapted to receive flexible tubing.
  • the tubing is generally constructed of PVC and the bond socket is constructed of any one of a number of thermoplastic resins including PVC, polycarbonate, ABS, etc., PVC being preferable as it is solvent bonded to the housing, the tubing may be fused to the bond socket by brief immersion in cyclohexanone or other suitable organic solvent before inserting the tubing in the bond socket.
  • Soft PVC is flexible, allowing the cap to have an interference fit when solvent bonded. This makes it less susceptible to tolerance problems.
  • FIG. 3A depicts a side view of an embodiment of cap 30 with blood outlet 32 and bond socket 35 .
  • FIG. 3B depicts a side view of another embodiment of cap 30 having blood outlet 32 and bond socket 35 .
  • FIG. 3C depicts a side view of still another embodiment of cap 30 having blood outlet 32 and bond socket 35 .
  • Filter housing 10 is slideably received within the opening in cap 30 when fully inserted, housing 10 rests against annular ridge 36 .
  • Headspace 31 is defined by the gap between filter 20 and cap 30 .
  • FIG. 4A shows the details of bond socket 35 communicating with the blood outlet designed for interference fit with appropriately sized tubing.
  • Passage 41 has a dimension of approximately 0.185 inches in diameter.
  • Surface 43 is approximately 0.248 inches in diameter.
  • Annular member 42 has a height of approximately 0.35 inches.
  • Surface 45 is approximately 0.252 inches in diameter.
  • blood outlet 32 communicates with a quarter inch bond socket.
  • Replacement fluid infusion port 33 communicates with bond socket 34 shown in details in FIG. 4B.
  • Passage 41 has a dimension of approximately 0.098 inches in diameter.
  • Surface 43 is approximately 0.142 inches in diameter.
  • Annular member 42 has a height of approximately 0.31 inches.
  • Surface 45 is approximately 0.147 inches in diameter.
  • FIG. 5 depicts housing 10 inserted within cap 30 .
  • Headspace 31 communicates with outlet 32 , which in turn communicates with bond socket 35 .
  • Headspace 31 ranges from approximately 1.5 mm at the outer edge to approximately 3 mm in the center of the dome-like region.
  • the pressure in headspace 31 can reach 40 PSI (2000 mmHg), resulting in 25 lbs force pushing the cap off.
  • the cap 30 may therefore need to be bonded, threaded, or snapped on, or attached by other suitable means, to withstand pressure. Solvent bonding and use of a threaded cap are two suitable means to accomplish attachment. It will again be understood that these device dimension are merely illustrative as stated above.
  • FIG. 6 depicts a top view of another embodiment of cap 30 having ribs 37 .

Abstract

Devices and methods that prevent clotting of blood during blood-processing procedures such as hemofiltration, hemodialysis, hemodiafiltration, and peritoneal dialysis are described. The device comprises a cap and a housing that is shaped to receive a blood filter. The housing has an inlet for blood and may have an outlet for waste and ultrafiltrate. The cap is attached to the housing. The cap has an outlet for blood and a port adjacent the outlet for receiving dilution fluid. Methods of use during blood-processing procedures to provide immediate hemodilution to blood exiting a filter are also described.

Description

    FIELD OF THE INVENTION
  • The present invention relates generally to devices and methods useful in preventing coagulation in filtered blood during hemofiltration. More specifically, the devices and methods provide a cap having a port, the cap adapted for attachment to a blood filter housing to provide hemodilution of blood as it enters and/or exits the filter. [0001]
  • BACKGROUND OF THE INVENTION
  • Undesired coagulation of blood often complicates blood-processing procedures such as hemofiltration, hemodialysis, and hemodiafiltration, particularly where a filter is used. Blood generally coagulates by transforming soluble fibrinogen into insoluble fibrin by activation of numerous circulating proteins that interact in a cascading series of limited proteolytic reactions. At each step of reaction, a clotting factor undergoes limited proteolysis and becomes an active protease that in turn activates the next clotting factor until finally a solid fibrin clot is formed. Fibrinogen (factor I) is activated by thrombin (factor IIa), which is converted from prothrombin by activated factor X. There are two separate coagulation pathways that activate factor X—the intrinsic system and the extrinsic system. Activation of the extrinsic system requires tissue thromboplastin (factor III), which is released from damaged tissue into the circulating blood to activate clotting. The intrinsic system, on the other hand, has all the factors necessary for coagulation contained in the circulating blood. The intrinsic system is, for example, partially responsible for clotting of blood in a test tube. Aggregation of platelets caused by stagnation of blood also facilitates blood coagulation. [0002]
  • During hemofiltration, for example, blood is removed from the patient, filtered through a filtering column to remove waste products, and returned to the patient's circulation. However, during removal of waste products, fluid is also removed, causing concentration of blood leaving the outflow tubing. As a result of hemoconcentration, hematocrit rises, and the intrinsic coagulation pathway and platelets are activated causing clotting of blood around the outlet of the filtering column, thereby compromising the hemofiltrating process. [0003]
  • What is needed are devices and methods that can be used with a filtering column during blood-processing procedures, such as hemofiltration, hemodialysis, hemodiafiltration, and peritoneal dialysis, to prevent clotting. Existing devices are inadequate for this purpose. [0004]
  • SUMMARY OF THE INVENTION
  • The present invention provides devices and methods that prevent clotting of blood during blood-processing procedures, such as hemofiltration, hemodialysis, and hemodiafiltration. More particularly, blood is diluted by replacement fluid, such as saline, Ringer's lactate, or other physiological solutions, as it enters and/or exits the filter. In a first embodiment, the device, also known as a filter, is comprised of a bundle of hollow fiber membrane made of resins such as polysulfone that is fixed in a cylindrical housing with a potting material. The interior of the fibers is the blood flow path. The exterior of the fibers is the dialysate and/or waste space. The potting material is typically a polyurethane material. The cylindrical housing may have one or two access ports. One port is for the hemofiltration filter, and two ports allow dialysate to flow through the housing contacting the exterior surface of the membrane for hemodialysis or hemodiafiltration. In one embodiment, the open fibers at the end of the cylindrical housing are covered at both ends with a cap. One cap is the blood entry cap, the other is the blood exit cap. In other embodiments, the housing includes end plates at one or both ends, the end plates integral with the housing. [0005]
  • The exit cap is attached to the housing, in some cases removably attached, and generally at a position opposite the inlet cap. The exit cap has an outlet for blood and a port adjacent the outlet for receiving replacement fluid. In certain embodiments, the blood outlet, the replacement fluid port, the blood inlet, and/or the waste outlet of the filter assembly communicate with bond sockets adapted to receive flexible tubing. [0006]
  • In another embodiment, the filter has an outlet or exit cap for blood at one end and an inlet or inlet cap at the other end, the cap having an inlet for blood and a port adjacent to the inlet for receiving dilution fluid, such as saline, Ringer's lactate, or other physiological solutions. The housing also includes access ports for waste and ultrafiltrate. [0007]
  • In still another embodiment, the housing includes first and second caps at opposite ends and an outlet for waste and ultrafiltrate. The first cap has an inlet for blood and a port adjacent to the inlet for receiving dilution fluid. The second cap has an outlet for blood and a port adjacent to the outlet for receiving dilution fluid. [0008]
  • In use, blood is passed through the blood inlet of the entry cap, through the filter membrane fibers, and through the blood outlet of the exit cap. Replacement fluid or dilution fluid, such as saline, Ringer's lactate, or other physiological solutions, is infused into the port adjacent the blood outlet to produce hemodilution at the blood outlet. Alternatively, the fluid is infused into the port adjacent the blood inlet of the entry cap to produce hemodilution at the inlet. In still another alternative method, fluid is infused into the port adjacent the blood inlet of the entry cap and into the port adjacent the blood outlet of the exit cap to produce hemodilution as blood enters and exits the filter housing. In certain constructions the replacement fluid swirls in a circular pattern in a headspace that is defined by the gap between the filter and the cap. Swirling of the replacement fluid facilitates mixing of the fluid and the blood, thereby preventing hemoconcentration and stasis of blood, and sweeping any particles of thrombus away from the filter. [0009]
  • The advantages associated with the hemodilution cap described herein include (1) preventing coagulation during blood processing procedures, (2) manufacturing efficiency, i.e., reducing plastic used in disposable components, (3) eliminating up to two bonds and up to two components, (4) less expense in materials costs and manufacturing costs, (5) more robust system, not subject to tolerances like bonding two rigid parts, and (6) integration of parts saves labor, materials, and precious resources.[0010]
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1A depicts a filter within a housing for hemofiltration. [0011]
  • FIG. 1B depicts a filter within a housing having a replacement fluid port adjacent the blood outlet port for hemofiltration. [0012]
  • FIG. 1C depicts a filter within a housing having a replacement fluid port adjacent the blood inlet port for hemofiltration. [0013]
  • FIG. 1D depicts a filter within a housing having replacement fluid ports adjacent both the blood inlet port and the blood outlet port for hemofiltration. [0014]
  • FIG. 1E depicts a filter within a housing for hemodiafiltration having dialysate inlet and outlet ports. [0015]
  • FIG. 1F depicts a filter within a housing for hemodiafiltration having a replacement fluid port adjacent the blood outlet port. [0016]
  • FIG. 2 depicts a filter-housing cap having a replacement fluid port adjacent the blood outlet port for hemofiltration. [0017]
  • FIG. 3A depicts a cross-sectional view of a filter housing cap having a replacement fluid port adjacent the blood outlet port for hemofiltration. [0018]
  • FIG. 3B depicts another cross-sectional view of a filter housing cap having a replacement fluid port adjacent the blood outlet port for hemofiltration. [0019]
  • FIG. 3C depicts another cross-sectional view of a filter housing cap having a replacement fluid port adjacent the blood outlet port and a headspace for hemofiltration. [0020]
  • FIG. 4A depicts a fluid bond socket communicating with the blood outlet. [0021]
  • FIG. 4B depicts a fluid bond socket communicating with the replacement fluid port. [0022]
  • FIG. 5 depicts a filter-housing cap removably mounted on a filter housing for hemofiltration. [0023]
  • FIG. 6 depicts a filter-housing cap for hemofiltration, the cap being made of flexible PVC and having ribs for stability.[0024]
  • DETAILED DESCRIPTION
  • During blood-processing procedures, such as hemofiltration, hemodialysis, and hemodiafiltration, blood has a tendency to clot as it passes through processing equipment, particularly where it exits the outlet of a filter, due to hemoconcentration. In FIG. 1A, the hemofiltration device includes [0025] cylindrical housing 10 which contains filter fibers 20 that remove waste from blood passing through the fibers. It will be understood that any other suitable shape can be used for the housing. Housing 10 is equipped with entry cap 13 having blood inlet 11. Waste and ultrafiltrate that are removed from the blood exits the housing through waste outlet 12. Exit cap 30 is mounted on housing 10 opposite blood entry cap 13. Headspace 31 is formed in the gap between filter fibers 20 and cap 30 and between filters 20 and cap 13. Headspace 31 communicates with blood outlet 32. Each of the inlet 11 waste outlet 12 and blood outlet 32 are adapted for attachment to flexible tubing sections that connect with a blood processing system.
  • In FIG. 1B, [0026] cap 30 further includes replacement fluid inlet port 33 that communicates with headspace 31. Replacement fluid is infused through port 33 to effect hemodilution of blood exiting filter 20. The system thereby reconstitutes blood as close as possible to the exit from the filter fibers. In this way hemodilution is accomplished with one part (cap 30) and two bonds (one between tubing and port 32, and another between tubing and port 33).
  • In FIG. 1C, [0027] housing 10 includes cap 13 having blood inlet 11 and dilution fluid inlet port 15 that communicates with headspace 31. Blood is diluted as it enters housing 10, thereby helping to prevent coagulation.
  • In FIG. 1D, [0028] housing 10 includes cap 13 having blood inlet and dilution fluid inlet port 15 that communicates with headspace 31. The housing also includes cap 30 having blood outlet 32 and fluid inlet port 33 that communicates with headspace 31. Dilution fluid is infused through port 33 and port 15 to effect hemodilution of blood entering and exiting filter 20.
  • FIG. 1E shows a [0029] housing 10 designed for hemodiafiltration. Housing 10 includes dialysate inlet 16 and dialysate outlet 12 to establish countercurrent dialysate flow. Filter fiber membrane 20 is mounted within potting material 21 at both ends, where the potting material typically is a polyurethane material. In FIG. 1F, cap 30 further includes replacement fluid inlet port 33 that communicates with headspace 31. Replacement fluid is infused through port 33 to effect hemodilution of blood exiting filter 20 as described for other embodiments above. It will be understood that for hemodiafiltration, a hemodilution cap may be included alternatively on the inlet to effect pre-dilution of blood, and/or on both the inlet and outlet.
  • FIG. 2 shows a top view of [0030] cap 30 having blood outlet 32 and replacement fluid infusion port 33. In use, replacement fluid, such as saline, Ringer's lactate, sterile filtered dialysate, or other physiological solutions, enters through port 33 and establishes a swirling current within headspace 31. This current has the beneficial effect of sweeping thrombus particles that may have accumulated in the headspace and flushing the particle through outlet 32. Inlet blood flow rate will typically be 50-1000 mL/min, preferably 350-600 mL/min. Infusion of dilution fluid at the exit cap will generally be 1-50% of inlet blood flow, preferably 20-30% in order to establish swirling. The foregoing ranges are set forth solely for the purpose of illustrating typical operating parameters. The actual parameters for operation of a device constructed according to the principles of the present invention may obviously vary outside of the listed ranges without departing from those basic principles.
  • [0031] Infusion port 33 includes bond socket 34, and outlet 32 includes bond socket 35. Each bond socket is adapted to receive flexible tubing. Where the tubing is generally constructed of PVC and the bond socket is constructed of any one of a number of thermoplastic resins including PVC, polycarbonate, ABS, etc., PVC being preferable as it is solvent bonded to the housing, the tubing may be fused to the bond socket by brief immersion in cyclohexanone or other suitable organic solvent before inserting the tubing in the bond socket. Soft PVC is flexible, allowing the cap to have an interference fit when solvent bonded. This makes it less susceptible to tolerance problems.
  • FIG. 3A depicts a side view of an embodiment of [0032] cap 30 with blood outlet 32 and bond socket 35. FIG. 3B depicts a side view of another embodiment of cap 30 having blood outlet 32 and bond socket 35. FIG. 3C depicts a side view of still another embodiment of cap 30 having blood outlet 32 and bond socket 35. Filter housing 10 is slideably received within the opening in cap 30 when fully inserted, housing 10 rests against annular ridge 36. Headspace 31 is defined by the gap between filter 20 and cap 30.
  • FIG. 4A shows the details of [0033] bond socket 35 communicating with the blood outlet designed for interference fit with appropriately sized tubing. Passage 41 has a dimension of approximately 0.185 inches in diameter. Surface 43 is approximately 0.248 inches in diameter. Annular member 42 has a height of approximately 0.35 inches. Surface 45 is approximately 0.252 inches in diameter. Thus, blood outlet 32 communicates with a quarter inch bond socket. Replacement fluid infusion port 33 communicates with bond socket 34 shown in details in FIG. 4B. Passage 41 has a dimension of approximately 0.098 inches in diameter. Surface 43 is approximately 0.142 inches in diameter. Annular member 42 has a height of approximately 0.31 inches. Surface 45 is approximately 0.147 inches in diameter. The foregoing ranges are set forth solely for the purpose of illustrating typical device dimensions. The actual dimensions of a device constructed according to the principles of the present invention may obviously vary outside of the listed ranges without departing from those basic principles.
  • FIG. 5 depicts [0034] housing 10 inserted within cap 30. Headspace 31 communicates with outlet 32, which in turn communicates with bond socket 35. Headspace 31 ranges from approximately 1.5 mm at the outer edge to approximately 3 mm in the center of the dome-like region. In use, the pressure in headspace 31 can reach 40 PSI (2000 mmHg), resulting in 25 lbs force pushing the cap off. The cap 30 may therefore need to be bonded, threaded, or snapped on, or attached by other suitable means, to withstand pressure. Solvent bonding and use of a threaded cap are two suitable means to accomplish attachment. It will again be understood that these device dimension are merely illustrative as stated above. FIG. 6 depicts a top view of another embodiment of cap 30 having ribs 37.
  • Although the foregoing invention has, for the purposes of clarity and understanding, been described in some detail by way of illustration and example, it will be obvious that certain changes and modifications may be practiced which will still fall within the scope of the appended claims. For example, it will be understood that any feature of any device or method disclosed herein can be used with any of the other devices or methods, even though any given figure might depict only a particular combination. [0035]

Claims (57)

What is claimed is:
1. An extracorporeal filter, comprising:
a housing having an inlet for blood and an outlet for waste and ultrafiltrate;
a cap attached to the housing opposite the inlet, the cap having an outlet port for blood and an infusion port; and
a filter media received within the housing.
2. The filter of claim 1, wherein the infusion port is radially adjacent the outlet port for blood.
3. The filter of claim 1, wherein the cap is solvent bonded to the housing.
4. The filter of claim 1, wherein the cap is removably attached to the housing.
5. The filter of claim 1, wherein the port is adapted to receive replacement fluid.
6. The filter of claim 1, wherein the housing has a second cap that carries the inlet.
7. The filter of claim 1, further comprising a second port adapted to receive dilution fluid radially adjacent the inlet.
8. The filter of claim 1, wherein a gap between the filter and the cap defines a headspace.
9. The filter of claim 1, wherein the cap is molded of flexible PVC and is solvent bonded to the housing.
10. The filter of claim 1, wherein the blood outlet communicates with a bond socket adapted to receive a flexible tubing.
11. The filter of claim 1, wherein the housing is generally cylindrical.
12. The filter of claim 1, wherein the replacement fluid port communicates with a bond socket adapted to receive a flexible tubing.
13. The filter of claim 1, wherein the blood inlet communicates with a bond socket adapted to receive a flexible tubing.
14. The filter of claim 1, wherein the waste outlet communicates with a bond socket adapted to receive a flexible tubing.
15. The filter of claim 1, further comprising a second outlet for waste and ultrafiltrate.
16. The filter of claim 1, further comprising a second inlet for blood.
17. A method for filtering blood, comprising the steps of:
providing a housing having a filter, an inlet for blood, an outlet for blood, a headspace between the filter and the outlet, and an infusion port communicating with the headspace;
passing blood through the inlet;
passing blood through the filter;
passing blood through the outlet; and
infusing dilution fluid into the infusion port to produce hemodilution at the outlet.
18. The method of claim 17, further comprising the step of infusing dilution fluid into a port adjacent the inlet to produce hemodilution at the inlet.
19. The method of claim 17, wherein the housing is cylindrical.
20. The method of claim 17, wherein the dilution fluid swirls in a circular pattern in a gap between the filter and the outlet.
21. The method of claim 17, wherein the housing has an outlet for waste and ultrafiltrate.
22. The method of claim 17, wherein the blood outlet is mounted on a cap that is solvent bonded on the housing.
23. The method of claim 17, wherein the step of passing blood through the filter produces hemoconcentration at the outlet.
24. The method of claim 17, wherein the step of passing blood through the filter removes waste and ultrafiltrate.
25. The method of claim 17, wherein the dilution fluid is a physiologic replacement fluid.
26. The method of claim 17, wherein the dilution fluid is saline.
27. The method of claim 17, wherein the dilution fluid is sterile filtered dialysate.
28. The method of claim 17, wherein the dilution fluid is Ringer's lactate.
29. A method for filtering blood, comprising the steps of:
providing a housing having an inlet for blood, an outlet for blood, and an infusion port adjacent the outlet, the housing having a filter,;
passing blood through the inlet;
passing blood through the filter;
passing blood through the outlet; and
infusing dilution fluid into the infusion port adjacent the outlet to produce hemodilution at the outlet.
30. The method of claim 29, further comprising the step of infusing dilution fluid into a port adjacent the inlet to produce hemodilution at the inlet.
31. The method of claim 29, wherein the housing is cylindrical.
32. The method of claim 29, wherein the dilution fluid swirls in a circular pattern in a gap between the filter and the outlet.
33. The method of claim 29, wherein the housing has an outlet for waste and ultrafiltrate.
34. The method of claim 29, wherein the blood outlet is mounted on a cap that is solvent bonded on the housing.
35. The method of claim 29, wherein the step of passing blood through the filter produces hemoconcentration at the outlet.
36. The method of claim 29, wherein the step of passing blood through the filter removes waste and ultrafiltrate.
37. The method of claim 29, wherein the dilution fluid is a physiologic replacement fluid.
38. The method of claim 29, wherein the dilution fluid is saline.
39. The method of claim 29, wherein the dilution fluid is sterile filtered dialysate.
40. The method of claim 29, wherein the dilution fluid is Ringer's lactate.
41. The method of claim 29, wherein there is a headspace between the filter and the outlet.
42. The method of claim 41, wherein the dilution port communicates with the headspace.
43. A blood-processing device, comprising:
a housing having an inlet for blood and an outlet for waste;
a fiber membrane received within the housing; and
a cap attached to the housing opposite the inlet, the cap having an outlet for blood, a headspace between the fiber membrane and the cap, and an infusion port communicating with the headspace.
44. The blood-processing device of claim 43, further comprising an inlet for dialysate.
45. The blood-processing device of claim 43, further comprising a second port adapted to receive dilution fluid radially adjacent the inlet.
46. A blood-processing device, comprising:
a housing having an outlet for blood and an outlet for waste;
a fiber membrane received within the housing; and
a cap attached to the housing opposite the outlet, the cap having an inlet for blood, a headspace between the fiber membrane and the cap, and an infusion port communicating with the headspace.
47. The blood-processing device of claim 46, further comprising an inlet for dialysate.
48. The blood-processing device of claim 46, further comprising a second port adapted to receive dilution fluid radially adjacent the outlet.
49. The blood-processing device of claim 46, wherein the infusion port is radially adjacent the inlet for blood.
50. A method for processing blood, comprising the steps of:
providing a housing having a fiber membrane, an inlet for blood, an outlet for blood, a headspace between the fiber membrane and the outlet, and an infusion port communicating with the headspace;
passing blood through the inlet;
passing blood into contact with the fiber membrane;
passing blood through the outlet; and
infusing dilution fluid into the infusion port to produce hemodilution at the outlet.
51. The method of claim 50, wherein the housing further comprises an inlet for dialysate.
52. The method of claim 50, wherein the housing further comprises a second port adapted to receive dilution fluid radially adjacent the inlet.
53. The method of claim 50, wherein the infusion port is radially adjacent the outlet for blood.
54. A method for processing blood, comprising the steps of:
providing a housing having a fiber membrane, an inlet for blood, an outlet for blood, a headspace between the fiber membrane and the inlet, and an infusion port communicating with the headspace;
passing blood through the inlet;
infusing dilution fluid into the infusion port to produce hemodilution at the inlet;
passing blood into contact with the fiber membrane; and
passing blood through the outlet.
55. The method of claim 54, wherein the housing further comprises an inlet for dialysate.
56. The method of claim 54, wherein the housing further comprises a second port adapted to receive dilution fluid radially adjacent the outlet.
57. The method of claim 54, wherein the infusion port is radially adjacent the inlet for blood.
US09/904,709 2001-07-12 2001-07-12 Hemodilution cap and methods of use in blood-processing procedures Abandoned US20030010718A1 (en)

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US12/015,420 US7776219B2 (en) 2001-07-12 2008-01-16 Methods, devices, and systems for hemodilution

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Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040193171A1 (en) * 2003-03-31 2004-09-30 Depuy Acromed, Inc. Remotely-activated vertebroplasty injection device
US20040195165A1 (en) * 2003-04-04 2004-10-07 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US20050131332A1 (en) * 2003-11-05 2005-06-16 Thomas Kelly High convection home hemodialysis/hemofiltration and sorbent system
EP1944077A1 (en) * 2006-11-27 2008-07-16 Bucher Vaslin Device for preventing the formation of deposits at the entrance of tubular or capillary membranes of a tangential filtration module
US20080177215A1 (en) * 2001-07-12 2008-07-24 Nxstage Medical Inc. Methods, devices, and systems for hemodilution
US20090012456A1 (en) * 2007-07-05 2009-01-08 Baxter International Inc. Dialysis system having disposable cassette
US20090107902A1 (en) * 2007-10-24 2009-04-30 Baxter International Inc. Personal hemodialysis system
US20090124963A1 (en) * 2007-11-09 2009-05-14 Baxter International Inc. Balanced flow dialysis machine
US20090229466A1 (en) * 2004-10-28 2009-09-17 Brugger James M Blood treatment dialyzer/filter for permitting gas removal
US20110046535A1 (en) * 2008-04-15 2011-02-24 Joensson Lennart Blood treatment apparatus
US8038639B2 (en) 2004-11-04 2011-10-18 Baxter International Inc. Medical fluid system with flexible sheeting disposable unit
EP2735358A1 (en) * 2012-11-22 2014-05-28 Gambro Lundia AB Capillary dialyzers
US9764074B1 (en) 2002-07-19 2017-09-19 Baxter International Inc. Systems and methods for performing dialysis
WO2017171064A1 (en) * 2016-03-31 2017-10-05 旭化成メディカル株式会社 Blood purification system and method for priming of same
JP2017185232A (en) * 2016-03-31 2017-10-12 旭化成メディカル株式会社 Blood purifier
US10232103B1 (en) 2001-11-13 2019-03-19 Baxter International Inc. System, method, and composition for removing uremic toxins in dialysis processes
US10596236B2 (en) 2016-03-10 2020-03-24 Arthrex, Inc. Systems and methods for preparing a thrombin serum
US10960026B2 (en) 2016-03-10 2021-03-30 Arthrex, Inc. Systems and methods for preparing protein enhanced serums
JP7085800B2 (en) 2016-03-31 2022-06-17 旭化成メディカル株式会社 Blood purifier, blood purification kit, and blood purification system
US11931492B2 (en) 2021-06-30 2024-03-19 Baxter International Inc. Balanced flow dialysis machine

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8753515B2 (en) 2009-12-05 2014-06-17 Home Dialysis Plus, Ltd. Dialysis system with ultrafiltration control
US8501009B2 (en) 2010-06-07 2013-08-06 State Of Oregon Acting By And Through The State Board Of Higher Education On Behalf Of Oregon State University Fluid purification system
US20120157905A1 (en) * 2010-12-15 2012-06-21 Biovec Transfusion, Llc Methods for treating carbon monoxide poisoning by tangential flow filtration of blood
WO2013052680A2 (en) 2011-10-07 2013-04-11 Home Dialysis Plus, Ltd. Heat exchange fluid purification for dialysis system
EP3131663A2 (en) 2014-03-29 2017-02-22 Princeton Trade and Technology Inc. Blood processing cartridges and systems, and methods for extracorporeal blood therapies
ES2864727T3 (en) 2014-04-29 2021-10-14 Outset Medical Inc Dialysis system and methods
US10426884B2 (en) 2015-06-26 2019-10-01 Novaflux Inc. Cartridges and systems for outside-in flow in membrane-based therapies
EP3352888B8 (en) 2015-09-24 2022-01-12 Princeton Trade and Technology Inc. Cartridges for hollow fibre membrane-based therapies
RU167888U1 (en) * 2015-10-13 2017-01-11 федеральное государственное бюджетное образовательное учреждение высшего образования "Казанский национальный исследовательский технологический университет" (ФГБОУ ВО "КНИТУ") Dialyzer
EP3500317B1 (en) 2016-08-19 2022-02-23 Outset Medical, Inc. Peritoneal dialysis system and methods
DE102018100568A1 (en) 2018-01-11 2019-07-11 B. Braun Avitum Ag Blood treatment machine with a hollow fiber filter module for horizontal arrangement and a hollow fiber filter module and its use

Family Cites Families (34)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4047563A (en) * 1976-01-27 1977-09-13 Japan Medical Supply Co., Ltd. Heat exchanger for artificial heart and lung devices
US4201673A (en) * 1977-07-04 1980-05-06 Terumo Corporation Apparatus for dialysis of solution
ZA8680B (en) * 1985-01-08 1987-08-26 Mcneilab Inc Mass transfer device having a microporous,spirally wound hollow fiber membrane
US4828543A (en) * 1986-04-03 1989-05-09 Weiss Paul I Extracorporeal circulation apparatus
DE3709432A1 (en) * 1987-03-21 1988-10-06 Fresenius Ag CAPILLARY FILTER ARRANGEMENT FOR THE STERILIZATION OF LIQUID MEDIA
JPH0614965B2 (en) * 1989-01-10 1994-03-02 テルモ株式会社 Oxygenator
US5051113A (en) 1990-06-13 1991-09-24 Du Pont Canada Inc. Air-intake system for mobile engines
SE502103C2 (en) * 1991-08-01 1995-08-14 Gambro Dialysatoren Filter unit for transfer of pulp and / or heat containing cavity fibers
US5264171A (en) * 1991-12-31 1993-11-23 Hoechst Celanese Corporation Method of making spiral-wound hollow fiber membrane fabric cartridges and modules having flow-directing baffles
US5480552A (en) * 1992-01-10 1996-01-02 Baxter International Inc. Method for concentrating a solute with an oscillating filtration device
DE19607162C2 (en) * 1996-02-26 1998-01-15 Fresenius Ag Use of a two module dialyzer to perform a method of filtering and immediately using substituate fluid in a hemodial filtration device
US5762869A (en) * 1996-07-24 1998-06-09 Gish Biomedical, Inc. Blood oxygenator
US5820767A (en) * 1996-07-29 1998-10-13 Pall Corporation Method for quantitation of microorganism contamination of liquids
US5916647A (en) * 1996-09-25 1999-06-29 Celgard Llc Pressure vessel: overmolding a polyolefin onto a polyolefin
ES2208806T3 (en) * 1996-11-21 2004-06-16 Fresenius Medical Care Deutschland Gmbh HIBLE FIBER MEMBRANE SEPARATOR DEVICE.
US6582385B2 (en) 1998-02-19 2003-06-24 Nstage Medical, Inc. Hemofiltration system including ultrafiltrate purification and re-infusion system
US6303036B1 (en) 1998-07-31 2001-10-16 Nephros, Inc. Method and apparatus for efficient hemodiafiltration
US6050278A (en) * 1998-09-24 2000-04-18 Minntech Corporation Dialyzer precleaning system
SE523122C2 (en) 1999-03-05 2004-03-30 Gambro Dialysatoren Filters with hollow fiber membrane
US6406631B1 (en) 1999-07-30 2002-06-18 Nephros, Inc. Two stage diafiltration method and apparatus
US6387324B1 (en) * 1999-09-30 2002-05-14 Therox, Inc. Apparatus and method for blood oxygenation
JP2003511103A (en) 1999-10-06 2003-03-25 メムブラーナ ゲゼルシャフト ミット ベシュレンクテル ハフツング Membrane module for hemodiafiltration with integrated pre-dilution or post-dilution of blood
US6776912B2 (en) * 1999-12-23 2004-08-17 Membrana Gmbh Hemodiafiltration system and method
US6315895B1 (en) 1999-12-30 2001-11-13 Nephros, Inc. Dual-stage hemodiafiltration cartridge
IT1320024B1 (en) 2000-04-07 2003-11-12 Gambro Dasco Spa METHOD FOR ADJUSTING THE INFUSION IN A DIALYSIS MACHINE AND DIALYSIS MACHINE FOR THE APPLICATION OF THE MENTIONED METHOD.
ES2344140T3 (en) 2000-10-30 2010-08-19 Nephros Inc TWO STAGE FILTRATION CARTRIDGE.
MXPA03005225A (en) * 2000-12-11 2004-12-02 Nephros Inc Hemodiafiltration / hemofiltration cartridges.
US20030010718A1 (en) * 2001-07-12 2003-01-16 Nxstage Medical, Inc. Hemodilution cap and methods of use in blood-processing procedures
US6702561B2 (en) * 2001-07-12 2004-03-09 Nxstage Medical, Inc. Devices for potting a filter for blood processing
US7125396B2 (en) * 2002-12-30 2006-10-24 Cardinal Health 303, Inc. Safety catheter system and method
US7297270B2 (en) 2003-04-04 2007-11-20 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US7744553B2 (en) 2003-12-16 2010-06-29 Baxter International Inc. Medical fluid therapy flow control systems and methods
US7534349B2 (en) 2005-09-02 2009-05-19 Nephros, Inc. Dual stage ultrafilter devices in the form of portable filter devices, shower devices, and hydration packs
US8281937B2 (en) 2007-02-16 2012-10-09 Nephros, Inc. Compact fluid purification device with manual pumping mechanism

Cited By (86)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080177215A1 (en) * 2001-07-12 2008-07-24 Nxstage Medical Inc. Methods, devices, and systems for hemodilution
US7776219B2 (en) 2001-07-12 2010-08-17 Nxstage Medical, Inc. Methods, devices, and systems for hemodilution
US10232103B1 (en) 2001-11-13 2019-03-19 Baxter International Inc. System, method, and composition for removing uremic toxins in dialysis processes
US10980931B2 (en) 2001-11-13 2021-04-20 Baxter International Inc. System, method, and composition for removing uremic toxins in dialysis processes
US9764074B1 (en) 2002-07-19 2017-09-19 Baxter International Inc. Systems and methods for performing dialysis
US20040193171A1 (en) * 2003-03-31 2004-09-30 Depuy Acromed, Inc. Remotely-activated vertebroplasty injection device
US20040195165A1 (en) * 2003-04-04 2004-10-07 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US7297270B2 (en) * 2003-04-04 2007-11-20 Chf Solutions, Inc. Hollow fiber filter for extracorporeal blood circuit
US20080060990A1 (en) * 2003-04-04 2008-03-13 Chf Solutions Inc. Hollow fiber filter for extracorporeal blood circuit
US7410582B2 (en) 2003-04-04 2008-08-12 Chf Solutions Inc. Hollow fiber filter for extracorporeal blood circuit
US9872950B2 (en) 2003-11-05 2018-01-23 Baxter International Inc. Renal therapy system having pump reversing fluid control
US9480784B2 (en) 2003-11-05 2016-11-01 Baxter International Inc. Dialysis system with balance chamber prime and rinseback
US10155080B2 (en) 2003-11-05 2018-12-18 Baxter International Inc. Renal therapy system with cassette-based blood and dialysate pumping
US10245370B2 (en) 2003-11-05 2019-04-02 Baxter International Inc. Renal failure therapy machines and methods including convective and diffusive clearance
US20110004351A1 (en) * 2003-11-05 2011-01-06 Baxter International Inc. Dialysis system including downloaded prescription entry
US20110000832A1 (en) * 2003-11-05 2011-01-06 Baxter International Inc. Dialysis system with enhanced features
US20110009798A1 (en) * 2003-11-05 2011-01-13 Baxter International Inc. Renal therapy system having pump reversing fluid control
US20110005992A1 (en) * 2003-11-05 2011-01-13 Baxter International Inc. Dialysis system with balance chamber prime and rinseback
US9889243B2 (en) 2003-11-05 2018-02-13 Baxter International Inc. Dialysis system including automatic priming
US9884144B2 (en) 2003-11-05 2018-02-06 Baxter International Inc. Hemodialysis system with cassette-based blood and dialysate pumping
US10293096B2 (en) 2003-11-05 2019-05-21 Baxter International Inc. Dialysis system including cassette with pumping tubes
US8029454B2 (en) 2003-11-05 2011-10-04 Baxter International Inc. High convection home hemodialysis/hemofiltration and sorbent system
US9072831B2 (en) 2003-11-05 2015-07-07 Baxter International Inc. Medical fluid pump valve integrity test methods and systems
US20050131332A1 (en) * 2003-11-05 2005-06-16 Thomas Kelly High convection home hemodialysis/hemofiltration and sorbent system
US9642961B2 (en) 2003-11-05 2017-05-09 Baxter International Inc. Renal failure therapy machines and methods including convective and diffusive clearance
US9572919B2 (en) 2003-11-05 2017-02-21 Baxter International Inc. Dialysis system with cassette based balance chambers and volumetric pumps
US9550020B2 (en) 2003-11-05 2017-01-24 Baxter International Inc. Dialysis system with a varying rate ultrafiltration profile
US10183109B2 (en) 2003-11-05 2019-01-22 Baxter International Inc. Hemodialysis system including a disposable cassette
US9421313B2 (en) 2003-11-05 2016-08-23 Baxter International Inc. Hemodialysis system with horizontal cassette roller pumps
US9387286B2 (en) 2003-11-05 2016-07-12 Baxter International Inc. Dialysis system including peristaltic tubing pumping cassette
US9302039B2 (en) 2003-11-05 2016-04-05 Baxter International Inc. Hemodialysis system including a disposable cassette
US9216246B2 (en) 2003-11-05 2015-12-22 Baxter International Inc. Renal failure therapy machines and methods including conductive and convective clearance
US9168333B2 (en) 2003-11-05 2015-10-27 Baxter International Inc. Dialysis system including disposable cassette
US8858488B2 (en) 2003-11-05 2014-10-14 Baxter International Inc. Dialysis system including blood and dialysate cassette
US8882692B2 (en) 2003-11-05 2014-11-11 Baxter International Inc. Hemodialysis system with multiple cassette interference
US8894600B2 (en) 2003-11-05 2014-11-25 Baxter International Inc. Hemodialysis system including on-line dialysate generation
US9155825B2 (en) 2003-11-05 2015-10-13 Baxter International Inc. Hemodialysis system using sorbent and reservoir
US8926540B2 (en) 2003-11-05 2015-01-06 Baxter Healthcare Inc. Hemodialysis system with separate dialysate cassette
US9144641B2 (en) 2003-11-05 2015-09-29 Baxter International Inc. Dialysis system with balance chamber prime and rinseback
US9072830B2 (en) 2003-11-05 2015-07-07 Baxter International Inc. Systems and methods for priming sorbent-based hemodialysis
US9072843B2 (en) 2003-11-05 2015-07-07 Baxter International Inc. Renal therapy system having pump reversing fluid control
US9005152B2 (en) 2003-11-05 2015-04-14 Baxter International Inc. Dialysis system with cassette based balance chambers and volumetric pumps
US9028436B2 (en) 2003-11-05 2015-05-12 Baxter International Inc. Hemodialysis system with cassette-based blood and dialyste pumping
US9039648B2 (en) 2003-11-05 2015-05-26 Baxter International Inc. Dialysis system with enhanced features
US9050411B2 (en) 2003-11-05 2015-06-09 Baxter International Inc. Dialysis system including downloaded prescription entry
US20110126714A1 (en) * 2004-10-28 2011-06-02 Nxstage Medical, Inc. Blood treatment dialyzer/filter for permitting gas removal
US20090229466A1 (en) * 2004-10-28 2009-09-17 Brugger James M Blood treatment dialyzer/filter for permitting gas removal
US20100096311A1 (en) * 2004-10-28 2010-04-22 Nxstage Medical, Inc Blood treatment dialyzer/filter design to trap entrained air in a fluid circuit
US7901579B2 (en) 2004-10-28 2011-03-08 Nxstage Medical, Inc. Blood treatment dialyzer/filter for permitting gas removal
US8038639B2 (en) 2004-11-04 2011-10-18 Baxter International Inc. Medical fluid system with flexible sheeting disposable unit
EP2508248A1 (en) * 2006-11-27 2012-10-10 Bucher Vaslin (Société Anonyme) Device for preventing the formation of deposits at the entrance of tubular or capillary membranes of a tangential filtration module
EP1944077A1 (en) * 2006-11-27 2008-07-16 Bucher Vaslin Device for preventing the formation of deposits at the entrance of tubular or capillary membranes of a tangential filtration module
US20090012456A1 (en) * 2007-07-05 2009-01-08 Baxter International Inc. Dialysis system having disposable cassette
US8920362B2 (en) 2007-07-05 2014-12-30 Baxter International Inc. Dialysis system having disposable cassette
US8057423B2 (en) 2007-07-05 2011-11-15 Baxter International Inc. Dialysis system having disposable cassette
US8337449B2 (en) 2007-07-05 2012-12-25 Baxter International Inc. Dialysis system having disposable cassette
US10695479B2 (en) 2007-10-24 2020-06-30 Baxter International Inc. Renal therapy machine and method including a priming sequence
US8932469B2 (en) 2007-10-24 2015-01-13 Baxter International Inc. Personal hemodialysis system including priming sequence and methods of same
US8329030B2 (en) 2007-10-24 2012-12-11 Baxter International Inc. Hemodialysis system with cassette and pinch clamp
US8114276B2 (en) 2007-10-24 2012-02-14 Baxter International Inc. Personal hemodialysis system
US20090107902A1 (en) * 2007-10-24 2009-04-30 Baxter International Inc. Personal hemodialysis system
US11291752B2 (en) 2007-10-24 2022-04-05 Baxter International Inc. Hemodialysis system including a disposable set and a dialysis instrument
US9925320B2 (en) 2007-10-24 2018-03-27 Baxter International Inc. Renal therapy machine and system including a priming sequence
US9855377B2 (en) 2007-10-24 2018-01-02 Baxter International Inc. Dialysis system including heparin injection
US8323492B2 (en) 2007-10-24 2012-12-04 Baxter International Inc. Hemodialysis system having clamping mechanism for peristaltic pumping
US8834719B2 (en) 2007-10-24 2014-09-16 Baxter International Inc. Personal hemodialysis system
US8992463B2 (en) 2007-11-09 2015-03-31 Baxter International Inc. Balanced flow dialysis machine
US11052180B2 (en) 2007-11-09 2021-07-06 Baxter International Inc. Balanced flow dialysis machine
US9415150B2 (en) 2007-11-09 2016-08-16 Baxter Healthcare S.A. Balanced flow dialysis machine
US20090124963A1 (en) * 2007-11-09 2009-05-14 Baxter International Inc. Balanced flow dialysis machine
US8652082B2 (en) * 2008-04-15 2014-02-18 Gambro Lundia Ab Blood treatment apparatus
US20110046535A1 (en) * 2008-04-15 2011-02-24 Joensson Lennart Blood treatment apparatus
EP2735358A1 (en) * 2012-11-22 2014-05-28 Gambro Lundia AB Capillary dialyzers
WO2014079991A1 (en) * 2012-11-22 2014-05-30 Gambro Lundia Ab Capillary dialyzers
CN104349833A (en) * 2012-11-22 2015-02-11 甘布罗伦迪亚股份公司 Capillary dialyzers
US10960026B2 (en) 2016-03-10 2021-03-30 Arthrex, Inc. Systems and methods for preparing protein enhanced serums
US10596236B2 (en) 2016-03-10 2020-03-24 Arthrex, Inc. Systems and methods for preparing a thrombin serum
US11045526B2 (en) 2016-03-10 2021-06-29 Arthrex, Inc. Systems and methods for preparing a thrombin serum
US11617784B2 (en) 2016-03-10 2023-04-04 Arthrex, Inc. Systems and methods for preparing a thrombin serum
CN109069723A (en) * 2016-03-31 2018-12-21 旭化成医疗株式会社 Blood purification system and its starting charging method
JPWO2017171064A1 (en) * 2016-03-31 2018-11-22 旭化成メディカル株式会社 Blood purification system and priming method thereof
JP2017185232A (en) * 2016-03-31 2017-10-12 旭化成メディカル株式会社 Blood purifier
CN113304341A (en) * 2016-03-31 2021-08-27 旭化成医疗株式会社 Blood purification system and priming method thereof
WO2017171064A1 (en) * 2016-03-31 2017-10-05 旭化成メディカル株式会社 Blood purification system and method for priming of same
JP7085800B2 (en) 2016-03-31 2022-06-17 旭化成メディカル株式会社 Blood purifier, blood purification kit, and blood purification system
US11931492B2 (en) 2021-06-30 2024-03-19 Baxter International Inc. Balanced flow dialysis machine

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