US20060278581A1 - Shear-Enhanced Systems And Methods For Removing Waste Materials And Liquid From The Blood - Google Patents

Shear-Enhanced Systems And Methods For Removing Waste Materials And Liquid From The Blood Download PDF

Info

Publication number
US20060278581A1
US20060278581A1 US11/465,952 US46595206A US2006278581A1 US 20060278581 A1 US20060278581 A1 US 20060278581A1 US 46595206 A US46595206 A US 46595206A US 2006278581 A1 US2006278581 A1 US 2006278581A1
Authority
US
United States
Prior art keywords
membrane
blood
gap
hemodialysis
hemodialysis membrane
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11/465,952
Inventor
Julie Moriarty
Rohit Vishnoi
Gretchen Kunas
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Priority to US11/465,952 priority Critical patent/US20060278581A1/en
Publication of US20060278581A1 publication Critical patent/US20060278581A1/en
Priority to US11/734,579 priority patent/US7494591B2/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D63/00Apparatus in general for separation processes using semi-permeable membranes
    • B01D63/16Rotary, reciprocated or vibrated modules
    • 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
    • A61M1/14Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • 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
    • A61M1/14Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/26Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes and internal elements which are moving
    • A61M1/262Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes and internal elements which are moving rotating
    • 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
    • A61M1/14Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/26Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes and internal elements which are moving
    • A61M1/262Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes and internal elements which are moving rotating
    • A61M1/265Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes and internal elements which are moving rotating inducing Taylor vortices
    • 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
    • A61M1/3413Diafiltration
    • A61M1/3417Diafiltration using distinct filters for dialysis and ultra-filtration
    • 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
    • A61M1/3437Substitution 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
    • A61M1/34Filtering 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
    • A61M1/3455Substitution fluids
    • A61M1/3458Substitution fluids having electrolytes not present in the dialysate
    • 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
    • B01D61/145Ultrafiltration
    • 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
    • B01D61/18Apparatus therefor
    • 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
    • B01D61/28Apparatus therefor
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D63/00Apparatus in general for separation processes using semi-permeable membranes
    • B01D63/06Tubular membrane modules
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D65/00Accessories or auxiliary operations, in general, for separation processes or apparatus using semi-permeable membranes
    • B01D65/08Prevention of membrane fouling or of concentration polarisation
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D2321/00Details relating to membrane cleaning, regeneration, sterilization or to the prevention of fouling
    • B01D2321/20By influencing the flow
    • B01D2321/2033By influencing the flow dynamically
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D2321/00Details relating to membrane cleaning, regeneration, sterilization or to the prevention of fouling
    • B01D2321/20By influencing the flow
    • B01D2321/2033By influencing the flow dynamically
    • B01D2321/2041Mixers; Agitators
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B01PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01DSEPARATION
    • B01D2321/00Details relating to membrane cleaning, regeneration, sterilization or to the prevention of fouling
    • B01D2321/20By influencing the flow
    • B01D2321/2033By influencing the flow dynamically
    • B01D2321/205Integrated pumps

Definitions

  • This invention relates to systems and methods that remove waste materials and liquid from the blood of an individual whose renal function is impaired or lacking.
  • the invention provides shear-enhanced systems and methods for removing waste materials and liquid from the blood.
  • the systems and methods convey the blood through a gap defined between an inner surface that is located about an axis and an outer surface that is concentric with the inner surface. At least one of the inner and outer surfaces carries a membrane that consists essentially of either a hemofiltration membrane or a hemodialysis membrane.
  • the systems and methods cause relative movement between the inner and outer surfaces about the axis at a selected surface velocity, taking into account the size of the gap. The relative movement between the inner and outer surfaces creates movement of the blood within the gap, which creates a vortical flow condition that induces transport of cellular blood components from the membrane while plasma water and waste material are transported to the membrane for transport across the membrane.
  • the circulatory forces of the vortical flow condition clear the membrane surface of occluding cellular components to maintain efficient operation.
  • the circulatory forces also supplement the shear forces exerted on the blood by viscous drag. Due to the circulatory forces, the concentration of waste materials in the blood plasma water becomes more homogenous. As a result, the transport of waste materials and associated blood plasma water across the membrane is significantly enhanced. Shear-enhanced waste removal makes possible the use of smaller processing devices and/or processing at reduced blood flow rates.
  • FIG. 1 is a schematic view of a system that includes a blood processing unit for removing waste material and plasma water from the blood;
  • FIG. 2 is a side section view of one embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemofiltration;
  • FIG. 3 is a side section view of another embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemodialysis;
  • FIG. 4 is a side section view of another embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemodialysis;
  • FIG. 5 is a side section view of another embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemofiltration and hemodialysis;
  • FIG. 6 is an enlarged and simplified perspective view of a gap formed between a stationary and rotating concentric surfaces, of a type that the blood processing units shown in FIGS. 2 to 5 incorporate, in which vortical flow conditions provide shear-enhanced waste material and plasma water removal;
  • FIG. 7 is an enlarged side sectional view of the vortical flow conditions shown in FIG. 5 that provide shear-enhanced waste material and plasma water removal.
  • FIG. 1 shows a system 10 for removing waste material (e.g., urea, creatinine, and uric acid) and plasma water from the blood of an individual whose renal function is impaired or lacking.
  • the system 10 includes a blood processing unit 12 that receives whole blood from the individual.
  • the individual typically has one or more surgically installed vascular access devices, such as an arterial-venous fistula, to facilitate coupling the blood processing unit 12 to the circulatory system of the individual.
  • arterial whole blood is drawn from the individual through an inlet path 14 .
  • An inlet pump 16 governs the blood inlet flow rate.
  • the blood processing unit 12 includes a membrane 18 , along which the whole blood drawn from the individual is conveyed.
  • the membrane 18 can have different functional and structural characteristics, which affect the manner in which waste material is transported by the membrane 18 .
  • waste material carried in blood plasma water can be separated by the membrane 18 from the whole blood either by convective transport, which is driven by pressure differentials across the membrane (in a process known as hemofiltration), or by diffusion, which is driven by concentration gradients across the membrane (in a process known as hemodialysis).
  • the waste materials and associated blood plasma water are removal from the blood processing unit 12 through a waste path 20 for discard.
  • the pores of the membrane 18 desirably have a molecular weight cut-off that block the passage of cellular blood components and larger peptides and proteins (including albumin) across the membrane. These components are retained in the blood, which is conveyed from the blood processing unit 12 through an outlet path 22 for return to the individual. In the illustrated embodiment, the treated blood is returned to the venous blood circulatory system of the individual.
  • Fresh physiologic fluid is typically supplied from a source 24 to the plasma water and toxin-depleted blood.
  • the replacement fluid restores, at least partially, a normal physiologic fluid and electrolytic balance to the blood returned to the individual.
  • the relative volumes of waste plasma water removed and replacement fluid supplied can be monitored, e.g., by gravimetric means, so that a desired volumetric balance can be achieved.
  • An ultrafiltration function can also be performed by the blood processing unit 12 , by which plasma water is replaced in an amount slightly less than that removed. Ultrafiltration decreases the overall fluid level of the individual undergoing treatment, which typically increases due to normal fluid intake between treatment sessions.
  • the blood processing unit 12 includes a processing cartridge 26 , in which the membrane 18 is housed.
  • the cartridge 26 is desirable disposable and, in one representative embodiment (see FIG. 2 ), includes a generally cylindrical housing 28 , which is sized to be conveniently manipulated by an operator.
  • the housing 28 can be oriented for use either horizontally or vertically, or any intermediate position.
  • An elongated cylindrical rotor 30 (which can also be called a “spinner”) is rotatably supported within the housing 28 between oppositely spaced pivot bearings 32 and 34 .
  • the rotor 30 rotates within the housing 28 , which is held stationary during use. However, other manners of operation are possible, and the housing need not be held stationary.
  • An annular gap 36 is formed between the outer surface of the rotor 30 and the interior wall 38 of the housing 28 .
  • Whole blood in the inlet path 14 is conveyed through a blood inlet port 40 into the gap 36 for processing by the inlet pump 16 .
  • the blood is discharged from the gap 36 through an oppositely spaced outlet port 42 , which communicates with the blood return path 22 .
  • a magnetic drive assembly 44 provides rotation to the rotor 30 .
  • a ring of magnetic material 46 in the rotor 30 is acted upon by a rotating magnetic field generated by an external, rotating magnetic drive member 48 , which releasably engages the adjacent end of the housing 28 for use.
  • the rotor 30 rotates relative to the stationary interior wall 38 of the housing 28 .
  • the magnetic drive member 48 rotates the rotor 30 at a predetermined angular velocity.
  • the membrane 18 comprises an appropriate hemofiltration membrane (as FIG. 2 shows). If hemodialysis is to be performed, the membrane 18 comprises an appropriate hemodialysis membrane (as FIGS. 3 and 4 show). If hemodialysis with hemofiltration is to be performed, the processing cartridge 26 can include both a hemofiltration membrane and a hemodialysis membrane (as FIG. 5 shows)
  • the rotor 30 has an internal cavity 50 bounded by a grooved cylindrical wall 52 forming a network of channels 56 .
  • a hemofiltration membrane 54 covers the outer surface of grooved wall 52 .
  • the hemofiltration membrane 54 can comprise, e.g., a biocompatible synthetic material such as polysulfone, polyacrylonitrile, polymethylmethacrylate, polyvinyl-alcohol, polyamide, polycarbonate, etc., and cellulose derivatives.
  • the pores of hemofiltration membrane 54 desirably allow passage of molecules up to about 30,000 Daltons, and desirably not greater than about 50,000 Daltons, to avoid the passage of albumin (molecular weight of 68,000 Daltons).
  • the network of channels 56 convey blood plasma water passing through the membrane 54 into the cavity 50 .
  • An outlet port 58 communicates with the cavity 50 to convey blood plasma water from the processing cartridge 26 .
  • the pump 16 conveys whole blood into the gap 36 .
  • the whole blood flows within the gap 36 in contact with the hemofiltration membrane 54 .
  • waste material and associated blood plasma water flow from the gap 36 through membrane 54 into the channels 56 . Waste material and associated blood plasma water are discharged from the processing cartridge through the outlet port 58 . Cellular blood components continue to flow within the gap 36 for discharge through the outlet port 42 .
  • the hemofiltration membrane 54 can be mounted on the stationary wall 38 of the housing 28 , instead of being mounted on the spinning rotor 30 , as FIG. 2 shows.
  • the network of channels 56 communicating with the waste outlet port 58 would be formed in the stationary wall 38 , and the membrane 54 would overlay the channels. in the same fashion shown in FIG. 2 .
  • a hemofiltration membrane 54 can be mounted on both the spinning rotor 30 and the stationary wall 28 and used in tandem for waste material and plasma water removal.
  • the interior wall 38 of the housing 28 has a network of channels 60 communicating with an inlet port 62 and an outlet port 64 .
  • a semipermeable hemodialysis membrane 66 overlays the network of channels 60 .
  • the membrane 66 can, e.g., comprise a medium to high flux membrane, for example, a polysulfone, cellulose triacetate or acrylonitrile membrane. Such membranes are typically well suited to fluid and small solute (less the 10,000 Daltons) removal.
  • One side of the membrane 66 faces the annular gap 36 and the rotor 30 , which, in the illustrated embodiment, carries no membrane.
  • the other side of the membrane 66 faces the channels 60 .
  • the pump 16 conveys whole blood into the gap 36 .
  • the whole blood flows within the gap 36 in contact with membrane 66 .
  • Fresh dialysate is circulated by a pump 70 from a source 68 through the channels 60 via the ports 62 and 64 .
  • the dialysate is circulated through the channels 60 in a flow direction opposite to the direction of whole blood flow in the gap 36 .
  • waste materials are also transferred across the membrane 66 by diffusion, due to a difference in concentration of these materials in the blood (high concentrations) and in the fresh dialysate (low concentrations).
  • high concentrations high concentrations
  • low concentrations low concentrations
  • waste materials flow from the gap 36 through the membrane 66 into the dialysate.
  • the waste materials are discharged with the spent dialysate out of the processing cartridge 26 to, e.g., a drain.
  • Cellular blood components continue to flow within the gap 36 for discharge through the outlet port 42 for return to the individual.
  • the rotor 30 can include a network of channels 72 through which dialysate can be circulated in the manner just described.
  • a hemodialysis membrane 74 overlays the network of channels 72 on the rotor 30 .
  • One side of the membrane 74 faces the annular gap 36 .
  • the other side of the membrane faces the channels 72 .
  • the hemodialysis membrane 74 on the rotating rotor 36 can also be used in combination with the hemodialysis membrane 66 on the stationary interior wall 38 of the housing 28 , or by itself (in which case the stationary interior wall 38 of the housing 28 would be free of a membrane.
  • the processing cartridge 26 can include a hemodialysis membrane 66 mounted on either the rotor 30 or the interior housing wall 38 and a hemofiltration membrane 54 mounted on the other location.
  • the processing cartridge 26 accommodates hemdialysis with hemofiltration, a process also called hemodiafiltration.
  • annular gap 36 as just described, which is defined between two concentric surfaces (e.g., the rotor 30 and the interior housing wall 38 )
  • rotation of the inner surface relative to the outer surface can induce vortical flow conditions in the blood residing in the gap 36 .
  • the vortical flow conditions take the form of successive, alternately circulating, annuli TV (see FIG. 6 ) in the gap 36 between the two concentric surfaces.
  • This vortex action can be a type that can be generally classified as “Taylor vortices” (as designated as TV in FIG. 6 ).
  • the nature of the Taylor vortices can vary among laminar stable Taylor vortices, wavy non-stable Taylor vortices, turbulent Taylor vortices, or other intermediate vortical flow conditions.
  • Taylor vortices will develop in the blood occupying the gap 36 , regardless of whether the membrane is mounted on the inner surface or on the outer surface, or both surfaces. Taylor vortices develop in the blood occupying the gap 36 as a result of relative movement between the inner and outer surfaces, regardless of whether one of the surfaces is held stationary while the other rotates, or whether both surfaces are allowed to rotate. To achieve desired vortical flow conditions, it is believed that the inner surface should be rotated relative to the outer surface, and, if the outer surface is allowed to rotate, the rate of rotation of the inner surface should exceed the rate of rotation of the outer surface.
  • the amplitude of the vortex action which is characterized by the Taylor number, is a function of the rate of rotation of the rotating surface and the radial dimension of the gap 36 .
  • increasing the rate of rotation will increase the amplitude of the vortex action, leading to a higher Taylor number.
  • narrowing the radial dimension of the gap 36 will also increase the amplitude vortex action, leading to a higher Taylor number. It is believed that radial dimension of the gap 36 and the rate of rotation should be selected to yield a Taylor number that is greater than the critical Taylor number, at which vortical flow conditions develop.
  • Transmembrane pressure is also desirably monitored and maintained (by controlling operation of the pump 16 ) at a magnitude that maximizes fluid transport across the membrane without driving cellular blood components into the membrane pores, which can cause membrane plugging, hemolysis, and trauma to fragile cellular blood components residing within the gap 36 .
  • the vortical flow conditions provide a sweeping action in the gap 36 (see FIG. 7 ) that transports cellular blood components away from the membrane while blood plasma water carrying the targeted uremic toxins is transported to the membrane for passage through the pores of the operative membrane.
  • the circulation caused by the vortical flow conditions removes adherent cellular blood components from the surface of the operative membrane and replenishes available blood plasma water for transport through the membrane pores.
  • the vortical flow conditions thereby clear the membrane surface of occluding cellular components to maintain efficient operation at desirable transmembrane pressure levels.
  • the circulatory forces also supplement the shear forces exerted on the blood by viscous drag, which is tangential to the spinning membrane surface.
  • the concentration of waste materials in the blood plasma water becomes more homogenous. In all, the transport of waste materials and associated blood plasma water across the membrane is significantly enhanced. Shear-enhanced waste removal makes possible the use of smaller processing devices and/or processing at reduced blood flow rates.
  • ultrafiltration volume can be augmented by placing, either upstream or downstream of the processing cartridge 26 , an auxiliary processing cartridge 76 (shown in phantom lines in FIG. 1 ).
  • the auxiliary processing cartridge 76 subjects the blood to plasma water removal (either by hemodialysis or hemofiltration) in addition to the plasma water removal by the processing cartridge 26 .
  • An auxiliary processing cartridge 76 can also be used in series with the processing cartridge 26 , to provide waste removal by hemofiltration to augment waste removal by hemodialysis conducted by the processing cartridge 26 , or vice versa.

Abstract

Systems and methods convey the blood through a gap defined between an inner surface that is located about an axis and an outer surface that is concentric with the inner surface. At least one of the inner and outer surfaces carries a membrane that consists essentially of either a hemofiltration membrane or a hemodialysis membrane. The systems and methods cause relative movement between the inner and outer surfaces about the axis at a selected surface velocity, taking into account the size of the gap. The relative movement of the two surfaces creates movement of the blood within the gap, which creates vortical flow conditions that induce transport of cellular blood components from the membrane while plasma water and waste material are transported to the membrane for transport across the membrane. Shear-enhanced transport of waste materials and blood plasma water results.

Description

    FIELD OF THE INVENTION
  • This invention relates to systems and methods that remove waste materials and liquid from the blood of an individual whose renal function is impaired or lacking.
  • BACKGROUND OF THE INVENTION
  • For various reasons, including illness, injury or surgery, patients may require replacement or supplementation of their natural renal function in order to remove excess fluid or fluids containing dissolved waste products from their blood. Several procedures known for this purpose are hemodialysis, hemofiltration, hemodiafiltration and ultrafiltration.
  • SUMMARY OF THE INVENTION
  • The invention provides shear-enhanced systems and methods for removing waste materials and liquid from the blood.
  • The systems and methods convey the blood through a gap defined between an inner surface that is located about an axis and an outer surface that is concentric with the inner surface. At least one of the inner and outer surfaces carries a membrane that consists essentially of either a hemofiltration membrane or a hemodialysis membrane. The systems and methods cause relative movement between the inner and outer surfaces about the axis at a selected surface velocity, taking into account the size of the gap. The relative movement between the inner and outer surfaces creates movement of the blood within the gap, which creates a vortical flow condition that induces transport of cellular blood components from the membrane while plasma water and waste material are transported to the membrane for transport across the membrane.
  • The circulatory forces of the vortical flow condition clear the membrane surface of occluding cellular components to maintain efficient operation. The circulatory forces also supplement the shear forces exerted on the blood by viscous drag. Due to the circulatory forces, the concentration of waste materials in the blood plasma water becomes more homogenous. As a result, the transport of waste materials and associated blood plasma water across the membrane is significantly enhanced. Shear-enhanced waste removal makes possible the use of smaller processing devices and/or processing at reduced blood flow rates.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a schematic view of a system that includes a blood processing unit for removing waste material and plasma water from the blood;
  • FIG. 2 is a side section view of one embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemofiltration;
  • FIG. 3 is a side section view of another embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemodialysis;
  • FIG. 4 is a side section view of another embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemodialysis;
  • FIG. 5 is a side section view of another embodiment of a blood processing unit that the system shown in FIG. 1 can incorporate for the purpose of performing shear-enhanced hemofiltration and hemodialysis;
  • FIG. 6 is an enlarged and simplified perspective view of a gap formed between a stationary and rotating concentric surfaces, of a type that the blood processing units shown in FIGS. 2 to 5 incorporate, in which vortical flow conditions provide shear-enhanced waste material and plasma water removal; and
  • FIG. 7 is an enlarged side sectional view of the vortical flow conditions shown in FIG. 5 that provide shear-enhanced waste material and plasma water removal.
  • The invention may be embodied in several forms without departing from its spirit or essential characteristics. The scope of the invention is defined in the appended claims, rather than in the specific description preceding them. All embodiments that fall within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims.
  • DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • FIG. 1 shows a system 10 for removing waste material (e.g., urea, creatinine, and uric acid) and plasma water from the blood of an individual whose renal function is impaired or lacking. The system 10 includes a blood processing unit 12 that receives whole blood from the individual. The individual typically has one or more surgically installed vascular access devices, such as an arterial-venous fistula, to facilitate coupling the blood processing unit 12 to the circulatory system of the individual. In the illustrated embodiment, arterial whole blood is drawn from the individual through an inlet path 14. An inlet pump 16 governs the blood inlet flow rate.
  • The blood processing unit 12 includes a membrane 18, along which the whole blood drawn from the individual is conveyed. The membrane 18 can have different functional and structural characteristics, which affect the manner in which waste material is transported by the membrane 18. Generally speaking, waste material carried in blood plasma water can be separated by the membrane 18 from the whole blood either by convective transport, which is driven by pressure differentials across the membrane (in a process known as hemofiltration), or by diffusion, which is driven by concentration gradients across the membrane (in a process known as hemodialysis). The waste materials and associated blood plasma water are removal from the blood processing unit 12 through a waste path 20 for discard.
  • The pores of the membrane 18 desirably have a molecular weight cut-off that block the passage of cellular blood components and larger peptides and proteins (including albumin) across the membrane. These components are retained in the blood, which is conveyed from the blood processing unit 12 through an outlet path 22 for return to the individual. In the illustrated embodiment, the treated blood is returned to the venous blood circulatory system of the individual.
  • Fresh physiologic fluid, called replacement fluid, is typically supplied from a source 24 to the plasma water and toxin-depleted blood. The replacement fluid restores, at least partially, a normal physiologic fluid and electrolytic balance to the blood returned to the individual.
  • The relative volumes of waste plasma water removed and replacement fluid supplied can be monitored, e.g., by gravimetric means, so that a desired volumetric balance can be achieved. An ultrafiltration function can also be performed by the blood processing unit 12, by which plasma water is replaced in an amount slightly less than that removed. Ultrafiltration decreases the overall fluid level of the individual undergoing treatment, which typically increases due to normal fluid intake between treatment sessions.
  • The blood processing unit 12 includes a processing cartridge 26, in which the membrane 18 is housed. The cartridge 26 is desirable disposable and, in one representative embodiment (see FIG. 2), includes a generally cylindrical housing 28, which is sized to be conveniently manipulated by an operator. The housing 28 can be oriented for use either horizontally or vertically, or any intermediate position.
  • An elongated cylindrical rotor 30 (which can also be called a “spinner”) is rotatably supported within the housing 28 between oppositely spaced pivot bearings 32 and 34. The rotor 30 rotates within the housing 28, which is held stationary during use. However, other manners of operation are possible, and the housing need not be held stationary.
  • An annular gap 36 is formed between the outer surface of the rotor 30 and the interior wall 38 of the housing 28. Whole blood in the inlet path 14 is conveyed through a blood inlet port 40 into the gap 36 for processing by the inlet pump 16. After processing, the blood is discharged from the gap 36 through an oppositely spaced outlet port 42, which communicates with the blood return path 22.
  • In the illustrated embodiment, a magnetic drive assembly 44 provides rotation to the rotor 30. A ring of magnetic material 46 in the rotor 30 is acted upon by a rotating magnetic field generated by an external, rotating magnetic drive member 48, which releasably engages the adjacent end of the housing 28 for use. The rotor 30 rotates relative to the stationary interior wall 38 of the housing 28. The magnetic drive member 48 rotates the rotor 30 at a predetermined angular velocity.
  • Further details regarding devices employing a spinning rotor and a stationary housing for blood filtration can be found in U.S. Pat. No. 5,194,145 and U.S. Pat. No. 4,965,846, which are incorporated herein by reference.
  • Further details of construction and operation of the processing cartridge 26 can differ, depending upon the type of blood processing sought to be performed. If hemofiltration is to be performed, the membrane 18 comprises an appropriate hemofiltration membrane (as FIG. 2 shows). If hemodialysis is to be performed, the membrane 18 comprises an appropriate hemodialysis membrane (as FIGS. 3 and 4 show). If hemodialysis with hemofiltration is to be performed, the processing cartridge 26 can include both a hemofiltration membrane and a hemodialysis membrane (as FIG. 5 shows)
  • A. Hemofiltration
  • In the embodiment shown in FIG. 2, the rotor 30 has an internal cavity 50 bounded by a grooved cylindrical wall 52 forming a network of channels 56. A hemofiltration membrane 54 covers the outer surface of grooved wall 52. The hemofiltration membrane 54 can comprise, e.g., a biocompatible synthetic material such as polysulfone, polyacrylonitrile, polymethylmethacrylate, polyvinyl-alcohol, polyamide, polycarbonate, etc., and cellulose derivatives. The pores of hemofiltration membrane 54 desirably allow passage of molecules up to about 30,000 Daltons, and desirably not greater than about 50,000 Daltons, to avoid the passage of albumin (molecular weight of 68,000 Daltons).
  • The network of channels 56 convey blood plasma water passing through the membrane 54 into the cavity 50. An outlet port 58 communicates with the cavity 50 to convey blood plasma water from the processing cartridge 26.
  • In operation, as the rotor 30 is rotated, the pump 16 conveys whole blood into the gap 36. The whole blood flows within the gap 36 in contact with the hemofiltration membrane 54.
  • In response to the transmembrane pressure created by the pump 16, waste material and associated blood plasma water flow from the gap 36 through membrane 54 into the channels 56. Waste material and associated blood plasma water are discharged from the processing cartridge through the outlet port 58. Cellular blood components continue to flow within the gap 36 for discharge through the outlet port 42.
  • It should be appreciated that, alternatively, the hemofiltration membrane 54 can be mounted on the stationary wall 38 of the housing 28, instead of being mounted on the spinning rotor 30, as FIG. 2 shows. In this arrangement, the network of channels 56 communicating with the waste outlet port 58 would be formed in the stationary wall 38, and the membrane 54 would overlay the channels. in the same fashion shown in FIG. 2. It should also be appreciated that, alternatively, a hemofiltration membrane 54 can be mounted on both the spinning rotor 30 and the stationary wall 28 and used in tandem for waste material and plasma water removal.
  • B. Hemodialysis
  • In the embodiment shown in FIG. 3, the interior wall 38 of the housing 28 has a network of channels 60 communicating with an inlet port 62 and an outlet port 64. A semipermeable hemodialysis membrane 66 overlays the network of channels 60. The membrane 66 can, e.g., comprise a medium to high flux membrane, for example, a polysulfone, cellulose triacetate or acrylonitrile membrane. Such membranes are typically well suited to fluid and small solute (less the 10,000 Daltons) removal. One side of the membrane 66 faces the annular gap 36 and the rotor 30, which, in the illustrated embodiment, carries no membrane. The other side of the membrane 66 faces the channels 60.
  • In operation, as the rotor 30 is rotated, the pump 16 conveys whole blood into the gap 36. The whole blood flows within the gap 36 in contact with membrane 66. Fresh dialysate is circulated by a pump 70 from a source 68 through the channels 60 via the ports 62 and 64. Desirably (as FIG. 3 shows), the dialysate is circulated through the channels 60 in a flow direction opposite to the direction of whole blood flow in the gap 36.
  • As blood flows through the gap 36, plasma water is conveyed across the membrane 66 due to transmembrane pressure created by the pump 16. Targeted waste materials are also transferred across the membrane 66 by diffusion, due to a difference in concentration of these materials in the blood (high concentrations) and in the fresh dialysate (low concentrations). In response to the high-to-low concentration gradient, waste materials flow from the gap 36 through the membrane 66 into the dialysate. The waste materials are discharged with the spent dialysate out of the processing cartridge 26 to, e.g., a drain. Cellular blood components continue to flow within the gap 36 for discharge through the outlet port 42 for return to the individual.
  • As shown in FIG. 4, in an alternative embodiment, the rotor 30 can include a network of channels 72 through which dialysate can be circulated in the manner just described. In this arrangement, a hemodialysis membrane 74 overlays the network of channels 72 on the rotor 30. One side of the membrane 74 faces the annular gap 36. The other side of the membrane faces the channels 72.
  • It should be appreciated that the hemodialysis membrane 74 on the rotating rotor 36 can also be used in combination with the hemodialysis membrane 66 on the stationary interior wall 38 of the housing 28, or by itself (in which case the stationary interior wall 38 of the housing 28 would be free of a membrane.
  • As shown in FIG. 5, the processing cartridge 26 can include a hemodialysis membrane 66 mounted on either the rotor 30 or the interior housing wall 38 and a hemofiltration membrane 54 mounted on the other location. In this arrangement, the processing cartridge 26 accommodates hemdialysis with hemofiltration, a process also called hemodiafiltration.
  • C. Shear-Enhanced Waste Removal
  • In an annular gap 36 as just described, which is defined between two concentric surfaces (e.g., the rotor 30 and the interior housing wall 38), rotation of the inner surface relative to the outer surface can induce vortical flow conditions in the blood residing in the gap 36. The vortical flow conditions take the form of successive, alternately circulating, annuli TV (see FIG. 6) in the gap 36 between the two concentric surfaces. This vortex action can be a type that can be generally classified as “Taylor vortices” (as designated as TV in FIG. 6). The nature of the Taylor vortices can vary among laminar stable Taylor vortices, wavy non-stable Taylor vortices, turbulent Taylor vortices, or other intermediate vortical flow conditions.
  • Taylor vortices will develop in the blood occupying the gap 36, regardless of whether the membrane is mounted on the inner surface or on the outer surface, or both surfaces. Taylor vortices develop in the blood occupying the gap 36 as a result of relative movement between the inner and outer surfaces, regardless of whether one of the surfaces is held stationary while the other rotates, or whether both surfaces are allowed to rotate. To achieve desired vortical flow conditions, it is believed that the inner surface should be rotated relative to the outer surface, and, if the outer surface is allowed to rotate, the rate of rotation of the inner surface should exceed the rate of rotation of the outer surface.
  • The amplitude of the vortex action, which is characterized by the Taylor number, is a function of the rate of rotation of the rotating surface and the radial dimension of the gap 36. At a given radial dimension, increasing the rate of rotation will increase the amplitude of the vortex action, leading to a higher Taylor number. Given a rate of rotation, narrowing the radial dimension of the gap 36 will also increase the amplitude vortex action, leading to a higher Taylor number. It is believed that radial dimension of the gap 36 and the rate of rotation should be selected to yield a Taylor number that is greater than the critical Taylor number, at which vortical flow conditions develop.
  • Transmembrane pressure is also desirably monitored and maintained (by controlling operation of the pump 16) at a magnitude that maximizes fluid transport across the membrane without driving cellular blood components into the membrane pores, which can cause membrane plugging, hemolysis, and trauma to fragile cellular blood components residing within the gap 36.
  • When maintained within desired limits, the vortical flow conditions provide a sweeping action in the gap 36 (see FIG. 7) that transports cellular blood components away from the membrane while blood plasma water carrying the targeted uremic toxins is transported to the membrane for passage through the pores of the operative membrane. The circulation caused by the vortical flow conditions removes adherent cellular blood components from the surface of the operative membrane and replenishes available blood plasma water for transport through the membrane pores. The vortical flow conditions thereby clear the membrane surface of occluding cellular components to maintain efficient operation at desirable transmembrane pressure levels. The circulatory forces also supplement the shear forces exerted on the blood by viscous drag, which is tangential to the spinning membrane surface. Furthermore, due to the circulatory forces, the concentration of waste materials in the blood plasma water becomes more homogenous. In all, the transport of waste materials and associated blood plasma water across the membrane is significantly enhanced. Shear-enhanced waste removal makes possible the use of smaller processing devices and/or processing at reduced blood flow rates.
  • If desired, ultrafiltration volume can be augmented by placing, either upstream or downstream of the processing cartridge 26, an auxiliary processing cartridge 76 (shown in phantom lines in FIG. 1). The auxiliary processing cartridge 76 subjects the blood to plasma water removal (either by hemodialysis or hemofiltration) in addition to the plasma water removal by the processing cartridge 26. An auxiliary processing cartridge 76 can also be used in series with the processing cartridge 26, to provide waste removal by hemofiltration to augment waste removal by hemodialysis conducted by the processing cartridge 26, or vice versa.
  • Various features of the invention are set forth in the following claims.

Claims (11)

1-22. (canceled)
23. A system for removing waste from the blood of an individual comprising:
a blood processing device comprising a gap defined between an inner surface that is located about an axis and an outer surface, an inlet and an outlet communicating with the gap, at least one of the inner and outer surfaces carrying a hemodialysis membrane, wherein the hemodialysis membrane includes a first surface facing toward the gap and a second surface,
the blood processing device including a channel to convey a dialysate along the second surface of the hemodialysis membrane to create a concentration gradient across the hemodialysis membrane to transport waste material from the blood,
a drive mechanism causing relative movement between the inner and outer surfaces at a selected surface velocity, and
a source of dialysate communicating with the channel.
24. A system according to claim 23
wherein the drive mechanism rotates the inner surface while holding the outer surface stationary.
25. A system according to claim 23
wherein the drive mechanism rotates the inner surface at a higher rate of rotation than the outer surface.
26. A system according to claim 23
wherein the other of the inner and outer surfaces carries a hemofiltration membrane or a hemodialysis membrane.
27. A system according to claim 26
wherein the other surface carries a hemodialysis membrane.
28. A method for removing waste from the blood of an individual comprising the steps of:
conveying the blood through a gap defined between an inner surface that is located about an axis and an outer surface, at least one of the inner and outer surfaces carrying a hemodialysis membrane,
causing relative movement between the inner and outer surfaces at a selected surface velocity, and
conveying a dialysate along an opposite side of the hemodialysis membrane to create a concentration gradient across the hemodialysis membrane to transport waste material from the blood.
29. A method according to claim 28
wherein the inner surface is rotated while holding the outer surface stationary.
30. A method according to claim 28
wherein the inner surface is rotated at a higher rate of rotation than the outer surface.
31. A method according to claim 28
wherein the other of the inner and outer surfaces carries a hemofiltration membrane or a hemodialysis membrane.
32. A method according to claim 31
wherein the other surface carries a hemodialysis membrane.
US11/465,952 2002-02-02 2006-08-21 Shear-Enhanced Systems And Methods For Removing Waste Materials And Liquid From The Blood Abandoned US20060278581A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US11/465,952 US20060278581A1 (en) 2002-02-02 2006-08-21 Shear-Enhanced Systems And Methods For Removing Waste Materials And Liquid From The Blood
US11/734,579 US7494591B2 (en) 2002-02-02 2007-04-12 Shear-enhanced systems and methods for removing waste materials and liquid from the blood

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US10/066,311 US6863821B2 (en) 2002-02-02 2002-02-02 Shear-enhanced systems and methods for removing waste materials and liquid from the blood
US11/043,370 US7182867B2 (en) 2002-02-02 2005-01-26 Shear-enhanced systems and methods for removing waste materials and liquid from the blood
US11/465,952 US20060278581A1 (en) 2002-02-02 2006-08-21 Shear-Enhanced Systems And Methods For Removing Waste Materials And Liquid From The Blood

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US11/043,370 Division US7182867B2 (en) 2002-02-02 2005-01-26 Shear-enhanced systems and methods for removing waste materials and liquid from the blood

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US11/734,579 Division US7494591B2 (en) 2002-02-02 2007-04-12 Shear-enhanced systems and methods for removing waste materials and liquid from the blood

Publications (1)

Publication Number Publication Date
US20060278581A1 true US20060278581A1 (en) 2006-12-14

Family

ID=27658662

Family Applications (4)

Application Number Title Priority Date Filing Date
US10/066,311 Expired - Lifetime US6863821B2 (en) 2002-02-02 2002-02-02 Shear-enhanced systems and methods for removing waste materials and liquid from the blood
US11/043,370 Expired - Lifetime US7182867B2 (en) 2002-02-02 2005-01-26 Shear-enhanced systems and methods for removing waste materials and liquid from the blood
US11/465,952 Abandoned US20060278581A1 (en) 2002-02-02 2006-08-21 Shear-Enhanced Systems And Methods For Removing Waste Materials And Liquid From The Blood
US11/734,579 Expired - Lifetime US7494591B2 (en) 2002-02-02 2007-04-12 Shear-enhanced systems and methods for removing waste materials and liquid from the blood

Family Applications Before (2)

Application Number Title Priority Date Filing Date
US10/066,311 Expired - Lifetime US6863821B2 (en) 2002-02-02 2002-02-02 Shear-enhanced systems and methods for removing waste materials and liquid from the blood
US11/043,370 Expired - Lifetime US7182867B2 (en) 2002-02-02 2005-01-26 Shear-enhanced systems and methods for removing waste materials and liquid from the blood

Family Applications After (1)

Application Number Title Priority Date Filing Date
US11/734,579 Expired - Lifetime US7494591B2 (en) 2002-02-02 2007-04-12 Shear-enhanced systems and methods for removing waste materials and liquid from the blood

Country Status (4)

Country Link
US (4) US6863821B2 (en)
AR (1) AR038242A1 (en)
AU (1) AU2003209399A1 (en)
WO (1) WO2003066200A1 (en)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100108606A1 (en) * 2008-10-31 2010-05-06 Baxter International Inc. Systems and methods for performing hemodialysis
CN103463979A (en) * 2013-09-18 2013-12-25 浙江索纳克生物科技有限公司 Environment-friendly and high-efficient blood plasma concentration device
WO2022254018A1 (en) * 2021-06-04 2022-12-08 University College Dublin An annular tubular phase separator

Families Citing this family (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU2003240937C1 (en) 2002-05-30 2008-07-10 Kkj, Inc. Vortex enhanced filtration device and methods
WO2004080510A2 (en) * 2003-03-10 2004-09-23 Don Schoendorfer Vortex-enhanced filtration devices
US7374677B2 (en) * 2004-08-20 2008-05-20 Kkj, Inc. Two stage hemofiltration that generates replacement fluid
AU2004322685B2 (en) * 2004-08-20 2009-04-23 Kkj, Inc. Two stage hemofiltration that generates replacement fluid
WO2006118817A1 (en) * 2005-04-21 2006-11-09 University Of Pittsburgh Of The Commonwealth System Of Higher Education Paracorporeal respiratory assist lung
US8585968B2 (en) * 2006-04-21 2013-11-19 Scott W. Morley Method and system for purging moisture from an oxygenator
EP2334353A4 (en) 2008-10-01 2013-03-27 H R D Corp Applying shear stress for disease treatment
CA2786310A1 (en) * 2010-01-21 2011-07-28 Kkj, Inc. Vortex-enhanced filtration devices
US8453742B2 (en) 2010-09-07 2013-06-04 Saudi Arabian Oil Company Method and apparatus for selective acid diversion in matrix acidizing operations
AU2012229313B2 (en) * 2011-03-11 2016-08-11 Fenwal, Inc. Membrane separation devices, systems and methods employing same, and data management systems and methods
US10130751B2 (en) 2011-03-11 2018-11-20 Fenwal, Inc. Membrane separation and washing devices, systems and methods employing same, and data management systems and methods
US10413652B2 (en) * 2011-04-13 2019-09-17 Fenwal, Inc. Systems and methods for use and control of an automated separator with adsorption columns
US8840790B2 (en) 2011-04-27 2014-09-23 Fenwal, Inc. Systems and methods of controlling fouling during a filtration procedure
US9603986B2 (en) * 2013-08-30 2017-03-28 Fenwal, Inc. Device and method for processing and producing autologous platelet-rich plasma
EP3238759B1 (en) 2016-04-29 2019-07-17 Fenwal, Inc. System and method for processing, incubating and/or selecting biological cells
EP3238760B1 (en) * 2016-04-29 2019-10-02 Fenwal, Inc. System and method for selecting and culturing cells
US10046278B2 (en) * 2016-05-10 2018-08-14 Fenwal, Inc. Method for controlling fouling during a spinning membrane filtration procedure
EP3338823B1 (en) 2016-12-21 2021-06-16 Fenwal, Inc. System and method for separating cells incorporating magnetic separation

Citations (62)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1664769A (en) * 1925-07-29 1928-04-03 Henry M Chance Method and apparatus for centrifugal thickening of mixtures and clarifying of liquids
US2197509A (en) * 1936-07-14 1940-04-16 Frank C Reilly Process of and machine for separating solids from suspension in a liquid
US2294248A (en) * 1940-07-15 1942-08-25 Productive Inventions Inc Spark plug
US2398233A (en) * 1944-05-10 1946-04-09 B F Sturtevant Co Dust collector
US2670849A (en) * 1952-05-01 1954-03-02 Russell P Dunmire Apparatus for filtering materials
US2709500A (en) * 1951-05-31 1955-05-31 William R Carter Centrifugal air separator for removal of particles
US3026871A (en) * 1958-01-30 1962-03-27 Const Mecaniques De Stains Soc Apparatus for oxygenating blood
US3183908A (en) * 1961-09-18 1965-05-18 Samuel C Collins Pump oxygenator system
US3355382A (en) * 1964-07-29 1967-11-28 Waterdrink Inc Centripetal acceleration method and apparatus
US3396103A (en) * 1965-04-01 1968-08-06 Waterdrink Inc Method and apparatus for mounting membrane filters on tubular supports without laterally stressing the active surface
US3400074A (en) * 1965-09-15 1968-09-03 Carl A. Grenci Centrifugal reverse osmosis for desalination
US3491887A (en) * 1967-10-13 1970-01-27 Gino Maestrelli Solvent filter particularly designed for dry-cleaning plants
US3523568A (en) * 1967-03-13 1970-08-11 Lever Brothers Ltd Concentrating liquid solutions as films on gas swept rotating hollow porous members
US3567030A (en) * 1968-11-29 1971-03-02 Robert I Loeffler Reverse osmosis apparatus
US3568835A (en) * 1968-07-01 1971-03-09 Int Marketing Corp The Liquid separator and filter unit
US3634228A (en) * 1969-10-22 1972-01-11 Cryogenic Technology Inc Sterile washing method and apparatus
US3647632A (en) * 1968-04-11 1972-03-07 Little Inc A Apparatus for cell culture
US3674440A (en) * 1970-05-07 1972-07-04 Tecna Corp Oxygenator
US3705100A (en) * 1970-08-25 1972-12-05 Amicon Corp Blood fractionating process and apparatus for carrying out same
US3750885A (en) * 1971-06-28 1973-08-07 Universal Oil Prod Co Strainer apparatus with power assisted cleaning means
US3771658A (en) * 1971-10-20 1973-11-13 R Brumfield Blood transport membrane pump
US3771899A (en) * 1971-12-13 1973-11-13 R Brumfield Pulsator pump and heat exchanger for blood
US3795318A (en) * 1972-05-26 1974-03-05 Dow Chemical Co Control of ultrafiltration rates during hemodialysis with highly permeable membranes
US3821108A (en) * 1972-05-23 1974-06-28 S Manjikian Reverse osmosis or ultrafiltration module
US3847817A (en) * 1972-12-04 1974-11-12 Dover Corp Filter unit having a generally cylindrical filter element supported on bearings
US3883434A (en) * 1972-10-25 1975-05-13 Atomic Energy Authority Uk Reverse osmosis apparatus
US3900398A (en) * 1971-07-30 1975-08-19 Univ Iowa State Res Found Inc System for exchanging blood ultrafiltrate
US3900290A (en) * 1973-03-13 1975-08-19 Int Octrooi Mij Octropa Nl1973 Method and apparatus for determining the degree of platelet aggregation in blood
US3946731A (en) * 1971-01-20 1976-03-30 Lichtenstein Eric Stefan Apparatus for extracorporeal treatment of blood
US3977976A (en) * 1973-08-05 1976-08-31 Spaan Josef A E Apparatus for exchange of substances between two media on opposite sides of a membrane
US4040965A (en) * 1975-07-03 1977-08-09 Firma Supraton Aurer & Zucker Ohg Rotary filter separator
US4062771A (en) * 1975-06-11 1977-12-13 Hoechst Aktiengesellschaft Apparatus and process for membrane filtration
US4066554A (en) * 1975-12-11 1978-01-03 Escher Wyss Limited Filtration apparatus
US4082668A (en) * 1973-09-04 1978-04-04 Rashid Ayoub Zeineh Ultra filtration apparatus and method
US4093552A (en) * 1975-12-11 1978-06-06 Escher Wyss Limited Filtration apparatus
US4113614A (en) * 1976-12-10 1978-09-12 International Business Machines Corporation Automated hemodialysis treatment systems
US4184952A (en) * 1978-05-12 1980-01-22 Shell Oil Company Measurement of BSW in crude oil streams
US4191182A (en) * 1977-09-23 1980-03-04 Hemotherapy Inc. Method and apparatus for continuous plasmaphersis
US4212741A (en) * 1978-04-10 1980-07-15 Brumfield Robert C Blood processing apparatus
US4212742A (en) * 1978-05-25 1980-07-15 United States Of America Filtration apparatus for separating blood cell-containing liquid suspensions
US4214990A (en) * 1975-07-28 1980-07-29 Nippon Zeon Co. Ltd. Hollow-fiber permeability apparatus
US4229291A (en) * 1977-11-21 1980-10-21 Hoechst Aktiengesellschaft Permselective membrane and use
US4303068A (en) * 1978-02-28 1981-12-01 Rensselaer Polythechnic Institute Method and apparatus for single pass hemodialysis with high flux membranes and controlled ultrafiltration
US4381999A (en) * 1981-04-28 1983-05-03 Cobe Laboratories, Inc. Automatic ultrafiltration control system
US4412553A (en) * 1981-06-25 1983-11-01 Baxter Travenol Laboratories, Inc. Device to control the transmembrane pressure in a plasmapheresis system
US4444596A (en) * 1980-03-03 1984-04-24 Norman Gortz Automated cleaning method for dialyzers
US4486303A (en) * 1981-10-06 1984-12-04 Brous Donald W Ultrafiltration in hemodialysis
US4490135A (en) * 1982-09-24 1984-12-25 Extracorporeal Medical Specialties, Inc. Single needle alternating blood flow system
US4493693A (en) * 1982-07-30 1985-01-15 Baxter Travenol Laboratories, Inc. Trans-membrane pressure monitoring system
US4535062A (en) * 1982-02-12 1985-08-13 Chemap Ag Apparatus for growing microorganisms
US4579662A (en) * 1975-07-07 1986-04-01 Jonsson Svante U R Method and apparatus for filtration of a suspension or a colloidal solution
US4753729A (en) * 1985-04-26 1988-06-28 Baxter Travenol Laboratories, Inc. Rotor drive for medical disposables
US4776964A (en) * 1984-08-24 1988-10-11 William F. McLaughlin Closed hemapheresis system and method
US4790942A (en) * 1983-12-20 1988-12-13 Membrex Incorporated Filtration method and apparatus
US4876013A (en) * 1983-12-20 1989-10-24 Membrex Incorporated Small volume rotary filter
US5000848A (en) * 1987-01-28 1991-03-19 Membrex, Inc. Rotary filtration device with hyperphilic membrane
US5034135A (en) * 1982-12-13 1991-07-23 William F. McLaughlin Blood fractionation system and method
US5135667A (en) * 1990-06-14 1992-08-04 Baxter International Inc. Method and apparatus for administration of anticoagulant to red cell suspension output of a blood separator
US5194145A (en) * 1984-03-21 1993-03-16 William F. McLaughlin Method and apparatus for separation of matter from suspension
US5919369A (en) * 1992-02-06 1999-07-06 Hemocleanse, Inc. Hemofiltration and plasmafiltration devices and methods
US6099730A (en) * 1997-11-14 2000-08-08 Massachusetts Institute Of Technology Apparatus for treating whole blood comprising concentric cylinders defining an annulus therebetween
US20030155312A1 (en) * 2002-02-15 2003-08-21 Ivansons Ivars V. Spin-hemodialysis assembly and method

Family Cites Families (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE1442874A1 (en) 1963-11-02 1968-11-28 Mobil Oil Corp Method and device for the selective separation of particles in a gaseous or liquid medium
FR1583221A (en) 1968-05-22 1969-10-24
GB1283273A (en) 1970-11-05 1972-07-26 Amicon Corp Process and apparatus for blood fractionation
GB1480406A (en) 1974-12-04 1977-07-20 Univ Strathclyde Blood oxygenator
PL129007B1 (en) 1980-01-25 1984-03-31 Polska Akademia Nauk Instytut Plasma isolating apparatus utilizing a membrane
EP0050146A4 (en) 1980-04-14 1982-12-09 Baxter Travenol Lab Blood fractionation apparatus.
CA1188998A (en) 1980-11-12 1985-06-18 Stephen R. Ash System and method for controlling and monitoring blood or biologic fluid flow
WO1982003568A1 (en) 1981-04-13 1982-10-28 Eng Inc Biomedical Method and apparatus for high-efficiency ultrafiltration of complex fluids
EP0076320A1 (en) 1981-04-13 1983-04-13 Biomedical Engineering, Inc. Method and apparatus for treating blood and the like
BR8205658A (en) 1981-10-02 1983-08-30 Du Pont FILTER PLASMA PHERESIS PROCESS AND APPLIANCE
CA1258053A (en) 1982-12-13 1989-08-01 Halbert Fischel Blood fractionation system and method
CA1266443A (en) 1983-12-20 1990-03-06 Iosif Shmidt Filtration method and apparatus

Patent Citations (64)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1664769A (en) * 1925-07-29 1928-04-03 Henry M Chance Method and apparatus for centrifugal thickening of mixtures and clarifying of liquids
US2197509A (en) * 1936-07-14 1940-04-16 Frank C Reilly Process of and machine for separating solids from suspension in a liquid
US2294248A (en) * 1940-07-15 1942-08-25 Productive Inventions Inc Spark plug
US2398233A (en) * 1944-05-10 1946-04-09 B F Sturtevant Co Dust collector
US2709500A (en) * 1951-05-31 1955-05-31 William R Carter Centrifugal air separator for removal of particles
US2670849A (en) * 1952-05-01 1954-03-02 Russell P Dunmire Apparatus for filtering materials
US3026871A (en) * 1958-01-30 1962-03-27 Const Mecaniques De Stains Soc Apparatus for oxygenating blood
US3183908A (en) * 1961-09-18 1965-05-18 Samuel C Collins Pump oxygenator system
US3355382A (en) * 1964-07-29 1967-11-28 Waterdrink Inc Centripetal acceleration method and apparatus
US3396103A (en) * 1965-04-01 1968-08-06 Waterdrink Inc Method and apparatus for mounting membrane filters on tubular supports without laterally stressing the active surface
US3400074A (en) * 1965-09-15 1968-09-03 Carl A. Grenci Centrifugal reverse osmosis for desalination
US3523568A (en) * 1967-03-13 1970-08-11 Lever Brothers Ltd Concentrating liquid solutions as films on gas swept rotating hollow porous members
US3491887A (en) * 1967-10-13 1970-01-27 Gino Maestrelli Solvent filter particularly designed for dry-cleaning plants
US3647632A (en) * 1968-04-11 1972-03-07 Little Inc A Apparatus for cell culture
US3568835A (en) * 1968-07-01 1971-03-09 Int Marketing Corp The Liquid separator and filter unit
US3567030A (en) * 1968-11-29 1971-03-02 Robert I Loeffler Reverse osmosis apparatus
US3634228A (en) * 1969-10-22 1972-01-11 Cryogenic Technology Inc Sterile washing method and apparatus
US3634228B1 (en) * 1969-10-22 1984-02-07
US3674440A (en) * 1970-05-07 1972-07-04 Tecna Corp Oxygenator
US3705100A (en) * 1970-08-25 1972-12-05 Amicon Corp Blood fractionating process and apparatus for carrying out same
US3946731A (en) * 1971-01-20 1976-03-30 Lichtenstein Eric Stefan Apparatus for extracorporeal treatment of blood
US3750885A (en) * 1971-06-28 1973-08-07 Universal Oil Prod Co Strainer apparatus with power assisted cleaning means
US3900398A (en) * 1971-07-30 1975-08-19 Univ Iowa State Res Found Inc System for exchanging blood ultrafiltrate
US3771658A (en) * 1971-10-20 1973-11-13 R Brumfield Blood transport membrane pump
US3771899A (en) * 1971-12-13 1973-11-13 R Brumfield Pulsator pump and heat exchanger for blood
US3821108A (en) * 1972-05-23 1974-06-28 S Manjikian Reverse osmosis or ultrafiltration module
US3830372A (en) * 1972-05-23 1974-08-20 S Manjikian Reverse osmosis system adaptable for manual operation
US3795318A (en) * 1972-05-26 1974-03-05 Dow Chemical Co Control of ultrafiltration rates during hemodialysis with highly permeable membranes
US3883434A (en) * 1972-10-25 1975-05-13 Atomic Energy Authority Uk Reverse osmosis apparatus
US3847817A (en) * 1972-12-04 1974-11-12 Dover Corp Filter unit having a generally cylindrical filter element supported on bearings
US3900290A (en) * 1973-03-13 1975-08-19 Int Octrooi Mij Octropa Nl1973 Method and apparatus for determining the degree of platelet aggregation in blood
US3977976A (en) * 1973-08-05 1976-08-31 Spaan Josef A E Apparatus for exchange of substances between two media on opposite sides of a membrane
US4082668A (en) * 1973-09-04 1978-04-04 Rashid Ayoub Zeineh Ultra filtration apparatus and method
US4062771A (en) * 1975-06-11 1977-12-13 Hoechst Aktiengesellschaft Apparatus and process for membrane filtration
US4040965A (en) * 1975-07-03 1977-08-09 Firma Supraton Aurer & Zucker Ohg Rotary filter separator
US4579662A (en) * 1975-07-07 1986-04-01 Jonsson Svante U R Method and apparatus for filtration of a suspension or a colloidal solution
US4214990A (en) * 1975-07-28 1980-07-29 Nippon Zeon Co. Ltd. Hollow-fiber permeability apparatus
US4093552A (en) * 1975-12-11 1978-06-06 Escher Wyss Limited Filtration apparatus
US4066554A (en) * 1975-12-11 1978-01-03 Escher Wyss Limited Filtration apparatus
US4113614A (en) * 1976-12-10 1978-09-12 International Business Machines Corporation Automated hemodialysis treatment systems
US4191182A (en) * 1977-09-23 1980-03-04 Hemotherapy Inc. Method and apparatus for continuous plasmaphersis
US4229291A (en) * 1977-11-21 1980-10-21 Hoechst Aktiengesellschaft Permselective membrane and use
US4303068A (en) * 1978-02-28 1981-12-01 Rensselaer Polythechnic Institute Method and apparatus for single pass hemodialysis with high flux membranes and controlled ultrafiltration
US4212741A (en) * 1978-04-10 1980-07-15 Brumfield Robert C Blood processing apparatus
US4184952A (en) * 1978-05-12 1980-01-22 Shell Oil Company Measurement of BSW in crude oil streams
US4212742A (en) * 1978-05-25 1980-07-15 United States Of America Filtration apparatus for separating blood cell-containing liquid suspensions
US4444596A (en) * 1980-03-03 1984-04-24 Norman Gortz Automated cleaning method for dialyzers
US4381999A (en) * 1981-04-28 1983-05-03 Cobe Laboratories, Inc. Automatic ultrafiltration control system
US4412553A (en) * 1981-06-25 1983-11-01 Baxter Travenol Laboratories, Inc. Device to control the transmembrane pressure in a plasmapheresis system
US4486303A (en) * 1981-10-06 1984-12-04 Brous Donald W Ultrafiltration in hemodialysis
US4535062A (en) * 1982-02-12 1985-08-13 Chemap Ag Apparatus for growing microorganisms
US4493693A (en) * 1982-07-30 1985-01-15 Baxter Travenol Laboratories, Inc. Trans-membrane pressure monitoring system
US4490135A (en) * 1982-09-24 1984-12-25 Extracorporeal Medical Specialties, Inc. Single needle alternating blood flow system
US5034135A (en) * 1982-12-13 1991-07-23 William F. McLaughlin Blood fractionation system and method
US4790942A (en) * 1983-12-20 1988-12-13 Membrex Incorporated Filtration method and apparatus
US4876013A (en) * 1983-12-20 1989-10-24 Membrex Incorporated Small volume rotary filter
US5194145A (en) * 1984-03-21 1993-03-16 William F. McLaughlin Method and apparatus for separation of matter from suspension
US4776964A (en) * 1984-08-24 1988-10-11 William F. McLaughlin Closed hemapheresis system and method
US4753729A (en) * 1985-04-26 1988-06-28 Baxter Travenol Laboratories, Inc. Rotor drive for medical disposables
US5000848A (en) * 1987-01-28 1991-03-19 Membrex, Inc. Rotary filtration device with hyperphilic membrane
US5135667A (en) * 1990-06-14 1992-08-04 Baxter International Inc. Method and apparatus for administration of anticoagulant to red cell suspension output of a blood separator
US5919369A (en) * 1992-02-06 1999-07-06 Hemocleanse, Inc. Hemofiltration and plasmafiltration devices and methods
US6099730A (en) * 1997-11-14 2000-08-08 Massachusetts Institute Of Technology Apparatus for treating whole blood comprising concentric cylinders defining an annulus therebetween
US20030155312A1 (en) * 2002-02-15 2003-08-21 Ivansons Ivars V. Spin-hemodialysis assembly and method

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100108606A1 (en) * 2008-10-31 2010-05-06 Baxter International Inc. Systems and methods for performing hemodialysis
WO2010051207A2 (en) 2008-10-31 2010-05-06 Baxter International Inc. Systems and methods for performing hemodialysis
US8961789B2 (en) 2008-10-31 2015-02-24 Baxter International Inc. Systems and methods for performing hemodialysis
US9757504B2 (en) 2008-10-31 2017-09-12 Baxter International Inc. Systems and methods for performing hemodialysis
CN103463979A (en) * 2013-09-18 2013-12-25 浙江索纳克生物科技有限公司 Environment-friendly and high-efficient blood plasma concentration device
WO2022254018A1 (en) * 2021-06-04 2022-12-08 University College Dublin An annular tubular phase separator

Also Published As

Publication number Publication date
US7494591B2 (en) 2009-02-24
US20050133448A1 (en) 2005-06-23
US7182867B2 (en) 2007-02-27
US20070181500A1 (en) 2007-08-09
AR038242A1 (en) 2005-01-05
AU2003209399A1 (en) 2003-09-02
US6863821B2 (en) 2005-03-08
US20030146154A1 (en) 2003-08-07
WO2003066200A1 (en) 2003-08-14

Similar Documents

Publication Publication Date Title
US7182867B2 (en) Shear-enhanced systems and methods for removing waste materials and liquid from the blood
JP5106102B2 (en) Metabolic detoxification system and method
US7169303B2 (en) Sorbent reactor for extracorporeal blood treatment systems, peritoneal dialysis systems, and other body fluid treatment systems
JP4334771B2 (en) Efficient hemodiafiltration
US7976709B2 (en) System and method for regeneration of a fluid
EP1175917B2 (en) Hemodialysis apparatus
AU2013362119B2 (en) Haemodiafiltration method
US9173986B2 (en) Blood treatment unit for an extra-corporeal blood treatment apparatus
JP4436569B2 (en) Permeation type filtration system by osmotic pressure difference
US9757504B2 (en) Systems and methods for performing hemodialysis
JP4964133B2 (en) Two-stage blood filtration to produce exchange fluid
UA46256A (en) METHOD OF INCREASING THE ELIMINATION OF TOXIC SUBSTANCES THROUGH THE DIALYZER MEMBRANE

Legal Events

Date Code Title Description
STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION