The accompanying drawings are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification. The drawings illustrate an embodiment of the invention and, together with the description, serve to explain the principles of the invention. In the drawings,
Reference will now be made in detail to the embodiments of the invention, examples of which are illustrated in the accompanying drawings. Wherever possible, the same reference numbers are used in the drawings and the description to refer to the same or like parts.
The embodiment of the present invention includes an Elutra® blood component centrifuge manufactured by Gambro BCT, Inc. of Lakewood, Colo. The Elutra® centrifuge incorporates a one-omega/two-omega sealless tubing connection as disclosed in U.S. Pat. No. 4,425,112 to Ito, the entire disclosure of which is incorporated herein by reference. Although the embodiments of the invention are described in combination with the Elutra® centrifuge, this reference is made for exemplary purposes only and is not intended to limit the invention in any sense. It is understood that other centrifuges could be used with the embodiments of the instant invention, including, but not limited to, the COBE® Spectra apheresis system, the Trima® system and the Trima Accel® system, also manufactured by Gambro BCT Inc., as well as other elutriation devices used to separate blood components.
Similarly, the present invention may be advantageously used in a variety of centrifuge devices including, but not limited to, those commonly used to separate blood into its components. In particular, the present invention may be used with any centrifugal apparatus regardless of whether or not the apparatus employs a one-omega/two-omega seal-less tubing connection.
It will also be apparent that the teachings of the present invention can also be used for separating particles and blood cells as well as other cells. The description refers to both particles and cells and it is understood that both are used interchangeably without departing from the spirit of the invention. The teachings of the present invention further can be used with any elutriation system for separating particles and blood cells as well as other cells.
As embodied herein and illustrated in
As shown in
The fluid chamber 18 may be constructed similar to or identical to one of the fluid chambers disclosed in U.S. Pat. No. 5,674,173 referred to above, although in the illustrated embodiment the fluid chamber may have smooth sides as shown in the Figures and described below. As shown in
The fluid chamber 18 includes two frustoconical shaped sections 25, 27 joined together at a maximum cross-sectional area 23 of the fluid chamber 18. The interior of the fluid chamber 18 tapers (decreases in cross-section) from the maximum cross-sectional area 23 in opposite directions toward the inlet 22 and the outlet 20. Although the fluid chamber 18 is depicted with two sections (25, 27) having frustoconical interior shapes, the interior of each section may be paraboloidal, or of any other shape having a major cross-sectional area greater than the inlet or outlet area.
The fluid chamber 18 may be constructed from a unitary piece of plastic or from separate pieces joined together using known fixative or sealing methods to form separate sections of the fluid chamber 18. The fluid chamber 18 may be formed of a transparent or translucent co-polyester plastic, such as PETG, to allow viewing of the contents within the chamber interior with the aid of an optional strobe (not shown) during a separation or debulking procedure.
As shown in
As shown in
The fluid and particles from the first source 38 and the diluting, sedimentation or elutriation fluid from the second source 42 flow through the respective first conduit 28 to the three-way connector 34. These substances then flow through the inlet line 32 into the inlet 22 of the fluid chamber 18. In the fluid chamber 18, which turns with rotor 12 when mounted thereon, the particles in the centrifugal field separate according to differences in sedimentation velocity leaving faster sedimenting particles in the fluid chamber 18 and allowing some slower sedimenting particles to flow from the fluid chamber 18 as will be described below.
As the fluid chamber 18 is loaded with particles as is more fully described below, the fluid and particles having a relatively slower sedimentation velocity, which generally includes plasma, platelets, and possibly some white blood cells, flow through the fluid chamber outlet 20 into conduit tubing or line 48. As shown in
Adjacent to an outer portion of the centrifuge rotor 12, the separation vessel 52 or concentrator has a collection well 54 for collecting particles flowing into the separation vessel 52 or concentrator. Rotation of centrifuge rotor 12 sediments particles into the collection well 54 while slower sedimenting fluid and possibly some slower sedimenting particles remain above a top boundary of the collection well 54. The collected particles in the collection well 54 can include any cells or particles that have exited the fluid chamber 18, including a separated subset of white blood cells, as noted above.
The collection well 54 has a particle concentrate outlet 56 connected to a particle concentrate line or conduit 58. The particle concentrate line 58 removes particles retained in the collection well 54 along with a small portion of fluid as is more fully described below. The separation vessel 52 also includes a fluid outlet 60 connected to a fluid outlet line or conduit 62. The fluid outlet line 62 removes fluid flowing above a top boundary of the collection well 54. This fluid may include plasma or elutriation buffer or low density fluid. In addition, the fluid outlet line 62 may remove some slower sedimenting particles flowing above the top boundary layer past the collection well 54.
Preferably, fluid outlet 60 is located at or adjacent to one end of the separation vessel 52 or concentrator, and the inlet 50 is located at or adjacent to an opposite end of the separation vessel 52 or concentrator. This spacing ensures ample time for separation of particles from fluid, collection of a substantial number of particles in the collection well 54, and corresponding removal of a substantial number of particles including any separated subsets of white blood cells through the particle concentrate line 58.
In the embodiment shown in
As shown in
Also as shown in
After sedimentation in chamber 18, as shown in
To control the flow rates of the various substances and cells and the rotational speed of the rotor 12 during operation of the system 10, a controller is provided. The controller (not shown) controls pumps (not shown) for pumping substances through the tubing loops 43, 44, 46 and 72 and controls a motor (not shown) for rotating the centrifuge rotor 12.
In
In
In both the embodiments of
In the further embodiment
A method of separating components of blood and, in particular, separating white blood cells from red blood cells is discussed below with reference to
Initially, blood is collected from a patient and this blood is separated in a centrifugal separation process to isolate what is known as a blood product containing white blood cells. During this initial centrifugation process, platelet rich plasma and a portion of the red blood cells and more dense white blood cells may be separated from the blood, leaving the resulting white blood cell product. In addition, this resulting blood product most likely includes some platelets and red blood cells. Not all starting blood products will require an initial centrifugal separation. For example, collected blood from umbilical cords is generally not subject to an initial centrifugal separation. The starting blood product will then be provided from first source 38 in the apparatus described above.
The initial separation of the collected blood described above is preferably performed on a centrifuge (not shown) separate from the system 10, such as a dual stage or single stage centrifugal separator. In an alternative embodiment, the centrifuge rotor 12 may include structure for providing initial blood component separation on the centrifuge rotor 12, as disclosed in above-referenced U.S. Pat. No. 5,674,173. It is understood that the separated blood product could also be collected and initially separated if desired by other methods.
The resulting separated or collected blood product is placed in the first source 38 although the blood product could also come directly from a separation system through a conduit (not shown). The first source 38 is coupled to the first conduit 28 through conduit 17. In addition, the second source 42 (
The inlet pump associated with the tubing loop 44 is stopped to stop the flow of low density diluting, sedimentation or elutriation fluid into the chamber 18. As the centrifuge continues to rotate the particle constituents loaded in the chamber sediment under the resulting centrifugal force.
After sedimentation of the particle constituents of the blood product, the pump associated with tubing loop 46 is activated to remove or debulk at a low flow rate the sedimented red blood cells R through the inlet 22 of the chamber 18 and then through inlet conduit 32 and debulking conduit 30 to container 31 if reduction of red blood cells is required.
After the reduction of fractionated red blood cells, the white blood cells remaining in chamber 18 can be further separated by elutriation, as described below, or the inlet pump associated with tubing loop 43 can be restarted to reintroduce a second batch of blood product from source 38 into chamber 18.
The elutriating step including introduction of diluting, sedimentation or elutriation fluid for separating white blood cells into the desired subsets can be done after each debulking procedure or after the source 38 is empty of blood product. The only requirement is that there be a sufficient number of white blood cells in chamber 18 to achieve effective separation or fractionation. Therefore, the white blood cell content of the starting blood product should be considered in determining the sequence order of the elutriation step.
For collection of fractionated or separated white blood cells or separated desired particles, an operator, after debulking or after the first source 38 is empty, slowly increases the inlet pump speed associated with tubing loop 44, decreases the centrifuge speed, or increases the density or viscosity of the diluting, sedimentation or elutriation fluid to separate the cells in chamber 18 into subsets by elutriation, as is well known in the art. With respect to the embodiments of
With respect to
The loading, adding of low density fluid, sedimenting, debulking and elutriating steps, described above are thus repeated until the entire blood product has been separated or fractionated into desired components or desired subsets and debulked of red blood cells.
At the end of the separation process slide clamp 68 or other well known operable connectors or clamps are opened and the remaining low density fluid passes into waste bag 66.
As noted above the cells loaded in chamber 18 can be elutriated or even washed by addition of a low density diluting, sedimentation, or elutriation fluid from source 42 having a sedimentation agent. It may be desirable that such low density fluid contain a protein such as Human Serum Albumin (HSA) or a fluid sedimentation agent such as Hydroxyethyl Starch (HAES).
It is understood that the protein and sedimentation agent specified above is only exemplary and that other well known proteins or sedimentation agents could be or could form the diluting, sedimentation fluid. It is also understood that the low density fluid could be media or plasma.
As the blood product is being loaded into the separation chamber 18, and during the elutriating step, the diluting, sedimentation or elutriation fluid, plasma, platelets, and the white blood cells and any other materials flowing from the fluid chamber outlet 20 pass through the intermediate tubing 48 to the inlet 50 of the separation vessel 52 or concentrator as noted above. In the separation vessel 52 or concentrator, centrifugal force caused by rotation of the rotor 12 retain the particles in the collection well 54, while the diluting fluid and plasma flow through the fluid outlet 60 and fluid outlet line 62 to container 66 or to recirculation lines 67, 167 or 267 (
The particles and a portion of the fluids flow through the particle concentrate line 58 to one or more particle collection containers 70. As described above, any desired number of containers 70 can be used to collect the desired separated subsets of cells, including any separated subsets of white blood cells.
It is understood that other configurations could be used to re-circulate cell-free media or buffer, sedimentation fluid or diluting fluid. Such configurations include a separate media pump 144 as shown in
In the present invention, only one bag of liquid buffer or diluting fluid may be needed if the buffer is re-circulated through the chamber along with any additional needed fluid from bag or source 42. This provides an advantage to the user as the amount of liquid buffer purchased would be decreased. The user would no longer need to buy larger or multiple bags of liquid. In addition, as the amount of liquid buffer introduced into the elutriation system decreases so does the amount of bag waste produced. This saves the user the additional cost incurred for destruction or disposal of the waste products. This makes the present invention with recirculation a less expensive alternative to existing systems. Re-circulating the liquid buffer could be cost effective, more convenient and could provide the user an easier way of operating the system. With re-circulation the user would no longer need to handle cumbersome heavier bags, replace multiple smaller bags or monitor the level of liquid in the bags. Only one bag would need to be used and the user would not need to replace or monitor the bag until optimum cell separation was achieved. This method provides an easier and more convenient way for the user to operate the elutriation system.
The total volume available for reuse can be calculated as follows:
VT is the total amount of re-circulated fluid available for separation.
Vo is the initial volume of media or fluid in bag or source 42 after priming or other start up activities.
R is the percentage of the fluid re-circulated each flow cycle.
Example: Assume a starting media bag volume of 4 Assume 500 m is used to prime the system and to flush the system before recirculation is started.
Thus: Vo=3.51
If: 90% of the media is re-circulated then R=90
Giving: VT=35
Thus an initial 4 of media provided 500 m for priming and an effective 35 for elutriating, with a total waste of less than 4.
Although the diluting, sedimentation or elutriation fluid is added only at certain parts of the process, it is understood that other configurations are possible. For example, the fluid chamber 18 could be modified to include separate inlets for blood components and diluting or sedimentation fluid. The diluting or sedimentation fluid could also be added to the blood components in the first source 38 before, or at the beginning of, a batch separation process. This alternative arrangement can also be used with the recirculation line or conduit. That is, the line can be connected to the inlet of the fluid chamber or to the source bag 38.
It is anticipated that the fluid chamber 18 can be sized to contain any desired amount of product.
The disposable particle separation system may also optimally include sensors at various output locations such as in the particle concentrate line for monitoring the types of cells and concentration being collected. Any known type of a sensor could be used.
It will be apparent to those skilled in the art that various modifications and variations can be made to the structure and methodology of the present invention without departing from the scope or spirit of the invention. For example, the present invention could be used to separate tumor cells from red blood cells, and the cell suspension in the first source 38 may include T cells and/or stem cells. In view of the foregoing, it is intended that the present invention cover modifications and variations of this invention provided they fall within the scope of the following claims and their equivalents.
This application claims the benefit of U.S. Provisional Application No. 60/821,983 filed Aug. 10, 2006.
Number | Date | Country | |
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60821983 | Aug 2006 | US |