Patent Application
20070118063
The present invention relates generally to the field of extracorporeal blood processing methods which are particularly useful in blood component collection, and more particularly, the present invention relates to methods for the leukoreduction of red blood cells collected with an apheresis system.
One well-known type of extracorporeal blood processing involves an apheresis system and/or procedure in which blood is removed from a donor or a patient (hereafter cumulatively referred to as a donor), directed to a blood component separation device (e.g., centrifuge), and separated into various blood component types (e.g., red blood cells, white blood cells, platelets, plasma) for collection or therapeutic purposes. One or more or all of these blood component types may be collected, and/or treated for therapeutic purposes before storage or return to a patient, while the remainder may simply be returned to the donor or patient.
A number of factors may affect the commercial viability of an apheresis system. One factor relates to the time and/or expertise required of an individual to prepare and operate the apheresis system. For instance, reducing the time required by the operator to complete an entire collection procedure, as well as reducing the complexity of these actions, can increase productivity and/or lower the potential for operator error. Moreover, reducing the dependency of the system on the operator may further lead to reductions in the credentials desired/required for the operators of these systems.
Donor-related factors may also impact the commercial viability of an apheresis system and include, for example, donor convenience and donor comfort. For instance, donors/patients may have a limited amount of time which may be committed to a donation or therapeutic procedure. Consequently, once at the collection or treatment facility, the amount of time which is actually spent collecting and/or treating blood components is an important consideration. This also relates to donor comfort as the actual collection procedure may be somewhat discomforting because at least one and sometimes two access needles are disposed in the donor throughout the procedure.
Performance-related factors also affect the commercial viability of an apheresis system. Performance may be judged in terms of the collection efficiency of the apheresis system, which may impact or improve product quality and/or may in turn reduce the amount of processing time and thus decrease operator burden and increase donor convenience. The collection efficiency of a system may be gauged in a variety of ways, such as by the amount of a particular blood component type which is collected in relation to the quantity of this blood component type which passes through the apheresis system. Individual characteristics of the donor also contribute to the performance of apheresis systems, for example, some donors have greater percentages of certain blood cell types than other donors.
Performance may also be evaluated based upon the effect which the apheresis procedure has on the various blood component types. For instance, it is desirable to minimize the adverse effects on the blood component types as a result of the apheresis procedure (e.g., reduce platelet activation).
Another performance-related factor is the end quality of the collected blood component. For example, if red blood cells are the component to be collected, it is generally desirable that such red blood cells be leukoreduced by the removal of white blood cells or leukocytes. Contaminating white blood cells can present problems to the ultimate recipient of the collected blood component, by provoking immunogenic reactions and viral diseases.
Conventionally, filters have been used to remove leukocytes from collected blood products or components. For example, U.S. Pat. No. 5,954,971 discloses the use of a filter with an apheresis system for filtering a diluted blood component prior to collection. Other distinctive methods have also been used, and these have generally dictated special preliminary steps such as pre-chilling and/or overnight storage of collected components prior to filtration. Another distinct conventional filtration step is the venting or air handling/re-circulation or by-passing at the end of the filtration procedure which had been deemed important for substantial recovery of a remainder portion of the blood component to be processed through a red blood cell filter.
Leukocytes are made up of mononuclear cells and polymorphonuclear cells. Mononuclear cells consist of lymphocytes, monocytes and stem cells. Polymorphonuclear cells consist of granulocytes, eosinophils and basophils. As discussed above, a performance related factor, which may affect apheresis efficiency, is the amount of a particular cell component a donor has. For example, it has been observed that if a donor has a high percentage of lymphocytes as compared to other white blood cell subtypes, (or has a high lymphocyte load), leukofiltration is not as effective as in donors who do not have such high lymphocyte loads. There is often a high residual population of lymphocytes which are not removed via filtration and which contaminate the separated red blood cell component.
The present invention is directed towards removing mononuclear cells in an apheresis procedure before leukoreducing the separated blood components.
The present invention relates to the extracorporeal separation and collection of red blood cells using an apheresis blood processing system. More particularly, this invention relates to a method for the continuous separation of red blood cells from whole blood wherein the portion of the red blood cells which are closest to the layer containing lymphocytes are collected within the blood processing vessel and are returned to the donor, along with the lymphocytes in the buffy coat, leaving the mononuclear cell reduced red blood cells within the separation vessel.
According to the present invention, before the ultimate collection of the red blood cells in the collection container, the MNC-reduced red blood cells are filtered through a filtration device. This filtration preferably occurs during the overall separation procedure, although it could be initiated soon after and as part of the commencement of the collection procedure. Nevertheless, the separation procedure may be a continuous or batch process, and in either case, the filtration occurs upon or soon after removal of the separated high hematocrit MNC-reduced red blood cells from the processing vessel, yet preferably concurrently with or soon after the overall separation process.
These and still further aspects of the present invention are more particularly described in the following description of the preferred embodiments presented in conjunction with the attached drawings which are described briefly below.
The present invention will be described in relation to the accompanying drawings which assist in illustrating the pertinent features hereof. Generally, the primary aspects of the present invention relate to both procedural and structural improvements in or a sub-assembly for use with a blood apheresis system. However, certain of these improvements may be applicable to other extracorporeal blood processing applications whether any blood components are returned directly to the donor or otherwise; and such are within the scope of the present invention as well.
It should be noted that like elements are depicted by like numbers.
A preferred blood apheresis system 2 for use in and/or with the present invention is schematically illustrated in
In the blood apheresis system 2, blood is withdrawn from the donor 4 and directed through a preconnected extracorporeal tubing circuit 10 and, in one embodiment, a blood processing vessel 352 which together define a closed, sterile and disposable system. The set 10 is preferably disposable and is adapted to be mounted on and/or in the blood component separation device 6. The separation device 6 preferably includes a pump/valve/sensor assembly 1000 for interfacing with the extracorporeal tubing circuit 10, and a channel assembly 200 for interfacing with the disposable blood processing vessel 352.
The channel assembly 200 may include a channel housing 204 which is rotatably interconnected with a rotatable centrifuge rotor assembly 568 which provides the centrifugal forces required to separate blood into its various blood component types by centrifugation. The blood processing vessel 352 may then be interfitted within the channel housing 204. When connected as described, blood can then be flowed substantially continuously from the donor 4, through the extracorporeal tubing circuit 10, and into the rotating blood processing vessel 352. The blood within the blood processing vessel 352 may then be continuously separated into various blood component types and at least one of these blood component types (platelets, plasma, lymphocytes or red blood cells) is preferably continually removed from the blood processing vessel 352. Blood components which are not being retained for collection or for therapeutic treatment are preferably also removed from the blood processing vessel 352 and returned to the donor 4 via the extracorporeal tubing circuit 10. Note, various alternative apheresis systems (not shown) may also make use of the present invention; including batch processing systems (non-continuous inflow of whole blood and/or non-continuous outflow of separated blood components) or smaller scale batch or continuous RBC/plasma separation systems, whether or even if no blood components may be returned to the donor.
Operation of the blood component separation device 6 is preferably controlled by one or more processors included therein, and may advantageously comprise a plurality of embedded computer processors to accommodate interface with ever-increasing PC user facilities (e.g., CD ROM, modem, audio, networking and other capabilities). Relatedly, in order to assist the operator of the apheresis system 2 with various aspects of its operation, the blood component separation device 6 preferably includes a graphical interface 660 with an interactive touch screen 664.
Further details concerning the operation of a preferred apheresis system, such as the Gambro Trima® System and the Trima Accel® System (available from Gambro BCT, Inc., Lakewood, Colo.) may be found in a plurality of publications, including, for example, WO99/11305 and U.S. Pat. No. 5,653,887; No. 5,676,644; No. 5,702,357; No. 5,720,716; No. 5,722,946; No. 5,738,644; No. 5,750,025; No. 5,795,317; No. 5,837,150; No. 5,919,154; No. 5,921,950; No. 5,941,842; No. 6,129,656; and No. 6,730,055 among numerous others. The disclosures hereof are incorporated herein as if fully set forth. A plurality of other known apheresis systems may also be useful herewith, as for example, the Baxter CS3000® and/or Amicus® and/or Autopheresis-C® and/or Alyx systems, and/or the Haemonetics MCS® or MCS®+ and/or the Fresenius COM.TEC™ or AS-104™ and/or the system described in Pat. No. 6,773,389.
Separation Vessel
Although the ports 56, 58, and 60 and lines 62, 64, and 68 are referred to as being “collection” ports and lines the substances removed through these ports and lines can be either collected or reinfused back into a donor.
The separation vessel 352 has a generally annular flow path 46 and includes an inlet portion 48 and outlet portion 51. A wall 52 prevents substances from passing directly between the inlet and outlet portions 48 and 51 without first flowing around the generally annular flow path 46 (e.g., counterclockwise as illustrated by arrows in
Although
The separated substances flow into the outlet portion 51 where they are removed via first 56, second 58, and third 60 collection ports respectively, of first 62, second 64, and third 68 collection lines. Separated substances may also be removed by an interface control port 61 of the interface control line 44. As shown in
The outlet portion 51 includes a barrier 38 for substantially blocking flow of the intermediate density substances, such as the buffy coat, which as discussed above, consists of white blood cells and platelets. Preferably, the barrier 38 extends completely across the outlet portion 51 in a direction generally parallel to the axis of rotation. The first collection port 56 is positioned immediately upstream of barrier 38, downstream of the inlet portion 48, to collect the intermediate density substances blocked by the barrier 38.
Radially inner and outer edges of the barrier 38 are spaced from radially inner and outer walls of the separation vessel 352 to form a first passage 40 for collection of lower density substances if desired, such as plasma, at a radially inner position in the outlet portion 51 and a second passage 66 for higher density substances, such as red blood cells, at a radially outer position in the outlet portion 51. The second and third collection ports 58 and 60 are positioned downstream of the barrier 38 to collect the respective low and high density substances passing through the first and second passages 40 and 66.
The interface port 61 is also positioned downstream of the barrier 38. During a separation procedure, the interface port 61 removes the least dense of the most dense substances in the outlet portion 51 to thereby control the radial position of the interface between the buffy coat layer 82 and the red blood cell layer 86 and plasma layer 84 in the outlet portion 51.
First port 56 may be used to remove platelets if desired, or may be used to remove the buffy coat layer 82 and a portion of the red blood cell layer next to the buffy coat layer which may contain some contaminating white blood cells. Although the second and third collection ports 58 and 60 and the interface control port 61 are shown downstream of the barrier 38, one or more of these elements may be upstream of the barrier 38. In addition, the order of the collection ports 56, 58, 60, and the interface port 61 along the length of the outlet portion 51 could be changed. Further details concerning the structure and operation of the separation vessel 352 is described in U.S. Pat. No. 6,053,856 to Hlavinka, which has been incorporated herein by reference.
Disposable Set: Extracorporeal Tubing Circuit
As illustrated in
The disclosures of the above-listed patents include numerous further details of an apheresis system for use with the present invention. Such details are not repeated here except generally for certain of those which may relate particularly to red blood cell (hereafter, RBC) collection and/or other RBC processes. Other blood component separation and collection processes are discussed at various points herein where they may be involved in or somewhat related to features of the present disclosure.
For a particular example, emanating from vessel 352 is an RBC outlet tubing line 64 of the blood inlet/blood component tubing assembly 60 which is interconnected with integral RBC passageway 170 of cassette 115 of cassette assembly 110 (see
An alternative tubing set filter and collection bag assembly 950a is shown in
A further alternative embodiment is shown in
The embodiment shown in
The additive fluid assembly 980 further preferably includes one or more (as shown) spike assemblies 984a, 984b with respective spikes 985a, 985b and associated sterile barrier devices 986a, 986b and tubing connection lines 988a, 988b which may be connected to tubing line 982 via a Y-connector 989 as shown. Note, it may be that only one of one or more of the above devices may be necessary; e.g., perhaps only one sterile barrier device may be used even with more than one bag of solution. One or more slide clamp(s) 990 and/or a level sensing or fluid detection apparatus 995 may also be included.
The cassette assembly 110 further includes a pump-engaging, additive fluid inlet tubing loop 142 interconnecting the first respective integral additive fluid passageway 140c and a second integral additive fluid passageway 140d. The second integral or additive fluid passageway 140d includes first and second spurs 144c, 144d, respectively. The second spur 144d of the second additive fluid passageway 140d (
In an intervening portion of the cassette 115, a plasma tubing 68 of blood inlet/blood component tubing assembly 60 (see
Most portions of the tubing assemblies 20, 50, 60, 90, 100, 950, 950a, 950b and/or 980 and cassette assembly 110 are preferably made from plastic components including, for example, polyvinyl chloride (PVC) tubing lines, that may permit visual observation and monitoring of blood/blood components therewithin during use. It should be noted that thin-walled PVC tubing may be employed for approved, sterile docking (i.e., the direct connection of two pieces of tubing line) for the RBC collector tubing lines 952 and 965, as may be desired and/or for an RBC storage solution spike assembly 980. In keeping with one aspect of the invention, all tubing lines are preconnected before sterilization of the total disposable assembly to assure that maximum sterility of the system is maintained. Note, a highly desirable advantage to preconnection of all of the elements of the tubing circuit including the filter and collection bag sub-assembly 950 involves the complete pre-assembly and then sterilization hereof after pre-assembly such that no sterile docking is later necessary (spike addition of storage solution excepted). Thus, the costs and risks of sterile docking are eliminated. Alternatively, thicker-walled PVC tubing may be employed for approved, sterile docking RBC collector tubing lines 952 and/or 965, inter alia.
As mentioned, a cassette assembly 110 in the embodiment of
Operation of Extracorporeal Tubing Circuit and Blood Component Separation Device
Priming and various other operations of the apheresis process are preferably carried out as set forth in the above-listed patents, inter alia. However, certain basic features are also described generally here with particular reference to the schematic diagrams of
For example, during a blood removal submode, whole blood will be passed from a donor 4 into tubing line 22 of blood removal/return tubing assembly 20 and is then transferred to blood component separation device 6 (see generally
Note also that certain components may be collected simultaneously or consecutively one after the other. In one example, platelets and plasma may be collected prior to collection of RBCs. In the primary example shown in
With specific reference to
Aphersis Protocol
One protocol, which may be followed for performing an apheresis procedure relative to a donor 4 utilizing the described system 2, will now be summarized. Initially, an operator loads the disposable plastic assembly 8 in and/or onto the blood component separation device 6. According hereto, the operator hangs the various bags (e.g., collection bag 954 (and 94, if used); see
With the extracorporeal tubing circuit 10 and the blood processing vessel 352 loaded in the described manner, the donor 4 may then be fluidly interconnected with the extracorporeal tubing circuit 10 by inserting an access needle of the needle/tubing assembly 20 into the donor 4 (see, e.g.,
It should be noted that when the centrifuge rotor is spinning (as it preferably will be whenever blood is disposed within the blood processing vessel) it will impart centrifugal forces on the blood which will then separate into three primary component layers around the blood processing vessel: a first innermost layer containing at least plasma, a second intermediate layer of “buffy coat” which contains at least platelets and mononuclear cells (MNCs) and a third outermost layer containing primarily red blood cells. It should be noted however, that due to the close sizes of red blood cells and leukocytes, the RBC layer closest to the buffy coat layer interface (at the outermost layer) will contain at least a portion of WBCs. This red blood cell layer partially overlaps with the buffy coat layer.
The buffy coat layer is generally found on the interface between the red blood cell layer and the plasma layer (see element 82 of
Although separation and collection of various components may be performed, RBCs are the component of the most interest in the current invention, and thus the separation and collection protocol will continue with a description of the collection and filtration hereof. It is understood that RBCs may also be the only component collected with all other components being returned to the donor.
In turn, such separated blood components may be selectively collected in corresponding storage reservoirs (not shown) or immediately or after a minor delay returned to the donor 4 during respective blood return submodes (or substantially constantly in a two-needle setup). In this regard, and in one approach where more than one blood component is to be collected, such as plasma and/or platelets, blood apheresis system 2 may be used to collect other components during a time period(s) separate from the collection of red blood cells. These components may also be collected simultaneously. Note, if other components are collected prior to RBCs, then RBCs separated during any such other component phase may be diverted back to the donor and not filtered. Preferably, only collected MNC-reduced RBCs will be filtered in the current embodiment (though therapeutic filtration for a particular donor/patient may also be performed). By removing the other component layers, especially the buffy coat layer and the red blood cell layer which partially overlaps with the buffy coat layer, the remaining MNC-reduced red blood cells will be less contaminated with lymphocytes, and will be able to be filtered more efficiently to remove any remaining white blood cells. The buffy coat layer and the RBC layer containing the at least a portion of MNCs can either be returned to the donor, or collected into a storage reservoir or collection bag and further processed.
In any event, the RBC collection procedure is preferably controlled via control signals provided by blood collection device 6. Such an RBC collection procedure may include a setup phase and a collection phase. During such a setup phase, the blood apheresis system 2 may be adjusted automatically to establish a predetermined hematocrit in those portions of the blood processing vessel 352 and extracorporeal tubing circuit 10 through which separated RBCs will pass for collection during the RBC collection phase. A desirable resulting hematocrit for RBC collection may be between about 70 and about 90 or even up to 95+, and may be established at about 80. The term high hematocrit refers to those separated, undiluted RBCs leaving the separation vessel 352. Dilution with storage solution to a different (generally lower) collected hematocrit may follow.
Additionally, blood component device 6 may, during the set-up phase, divert the flow of separated RBCs flowing through RBC tubing line 64 through return tubing loop 172 and into blood return reservoir 150 for return to the donor 4 until the desired hematocrit is established in the separation vessel 352.
Also during the set up phase, the blood component separation device may divert the flow of the buffy coat layer 82 and the portion of the red blood cells 83 which are closest to the buffy coat layer either back to the donor or into a collection bag for further processing. By removing this portion of the red blood cells and the buffy coat layer from the blood processing vessel, the majority of the mononuclear cells will be removed. The red blood cells remaining in the separation vessel 52 are known as mononuclear cell reduced red blood cells.
The increased efficiency of removing the buffy coat layer and the layer of RBCs next to the buffy coat layer is shown in the table below.
As can be seen in the table above, the step of removing the buffy coat layer and the RBCs located next to the buffy coat layer produced a final RBC product with much lower WBC contamination as compared to the final RBC product produced without the removal step.
In order to establish the desired packing factor and/or hematocrit for the separated MNC-reduced RBCs, the operating speed of centrifuge rotor assembly 568 (see
To establish a desired anticoagulant (AC) ratio, blood component separation device 6 provides appropriate control signals to the anticoagulant pump so as to introduce anticoagulant into the blood inlet flow at a predetermined rate. Relatedly, it should be noted that the inlet flow rate of anticoagulated blood to blood processing vessel 352 may be limited by a predetermined, maximum acceptable anticoagulant infusion rate (ACIR) to the donor 4. As will be appreciated by those skilled in the art, the predetermined ACIR may be established on a donor-specific basis (e.g. to account for the particular total blood volume of the donor 4). To establish the desired total uncollected plasma flow rate out of blood processing vessel 352, blood collection device 6 provides appropriate control signals to the plasma (and platelet) pump assembly(ies), This may also serve to increase the hematocrit in the separated RBCs.
In one embodiment, the desired high hematocrit for the separated RBCs will be between about or approximately 75 and about 85 and will preferably be about or approximately 80; although, again higher hematocrits may be available as well. Then, where a centrifuge rotor assembly 568 may present a defined rotor diameter of about 10 inches, and where a blood processing vessel 352 is utilized, as described hereinabove, it has been determined that in one preferred embodiment channel housing 204 can be typically driven at a rotational velocity of about 3000 rpms to achieve the desired RBC hematocrit during the setup and red blood cell collection phases. Correspondingly, the blood inlet flow rate provided by pumping through loop 132 to vessel 352 may preferably be established at below about 65 ml/min. The desired hematocrit can be reliably stabilized by passing about two whole blood volumes of vessel 352 through vessel 352 before the RBC collection phase is initiated.
To initiate the MNC-reduced RBC collection phase, blood component separation device 6 provides an appropriate control signal to the RBC divert valve assembly (not shown) so as to direct the continuous outflow of the separated MNC-reduced high hematocrit RBCs removed from blood processing vessel 352 via line 64 into the RBC collection system 950 through tubing lines 951 and 952, and filter 960 into collection container 954 via line 965.
As may be appreciated, the MNC-reduced, separated RBCs are not pumped out of vessel 352 for collection, but instead are flowed out vessel 352 and through extracorporeal tubing circuit 10 by the pressure of the blood inlet flow to vessel 352. The inlet blood is pumped into vessel 352 via loop 132 of cassette 110. The separated MNC-reduced RBCs are pushed or pressed out of the vessel 352.
During the RBC collection phase, the inlet flow into vessel 352 will likely be limited by the above-noted maximum acceptable ACIR to the donor 4. The desired inlet flow rate may also be limited by that necessary to maintain the desired packing factor and/or hematocrit, as also discussed. In this regard, it will be appreciated that relative to the setup phase, the inlet flow rate may be adjusted slightly upwards during the RBC collection phase since not all anticoagulant is being returned to the donor 4. That is, a small portion of the AC may remain with the small amount of plasma that is collected with the high hematocrit RBCs in RBC reservoir 954.
According to the present invention, the relatively high hematocrit (high-crit) MNC-reduced RBCs optionally may be diluted and then filtered as soon as the blood is separated or very soon after having been separated within vessel 352. Alternatively, the MNC-reduced RBCs may be filtered without dilution in a high-crit state. The phrase high-crit refers to the state of the separated MNC-reduced RBCs as they emerge from the separation vessel 352. In the substantially continuous centrifugal separation process as described here, a freshly separated stream of MNC-reduced RBCs is substantially continually flowing out of the vessel 352, first through tubing line 64, to and through cassette assembly 110 and then through lines 951 and 952 (where they optionally may be joined by diluting storage solution) to the filter 960 and then through line 965 to bag 954 (see
Note, the phrase freshly-separated is intended to describe the newly-separated blood components in and as they emerge from the mechanical separation system such as device 6 and separation vessel 352. It also includes the state of these same separated components for a reasonable length of time after removal from the mechanical separation device such as from vessel 352. Thus, for example, a reasonable length of time may include the entire apheresis procedure which may last up to (and perhaps exceed) two (2) or more hours during which filtration may be substantially continuously performed. Two further terms used herein have similar distinctions, namely, “recently removed” and “soon after.” Recently removed is referred to herein primarily relative to that blood taken from the donor which may be immediately taken and processed in a mechanical separation system, or which may have been taken and held subject to a reasonable non-long-term-storage type of delay prior to separation processing in a device such as device 6. Similarly, “soon after” is used in like manners relative to both of these circumstances as well, as, for example, when separated blood components may be removed from the separation vessel, e.g. soon after separation (whether in continuous or batch mode).
In any event, from the standpoint of the donor 4 and machine 6, following the separation, filtration and collection processes of the desired quantity of red blood cells, blood separation device 6 may then provide a control signal to the RBC divert assembly so as to divert any further RBC flow back to the donor 4 via loop 172, reservoir 150 and return line 24. Additionally, if further blood processing, by apheresis centrifugation here, is not desired, rinseback procedures may be completed. Additionally, once the minimum desired RBCs have been diverted into filtration/collection assembly 950 and after filtration completion, the red blood cell collection reservoir 954 (and/or the entire sub-assembly 950) may then be disconnected from the extracorporeal tubing circuit 10. Filter 960 may also be removed herewith or separately or remain attached and disposed of with the cassette 110 and other remaining bags or tubes. However, according to the present invention, a storage solution will be, perhaps during and/or after filtration of the RBCs, added to the RBC flow in tubing line 952 to the filter 960 ultimately to the red blood cell reservoir or bag 954. Preferably, a spike connection to one or more storage solution bag(s) 970 (see
The storage additive solution may be and preferably is contained in a discrete storage solution bag 970 that can be pre-connected, or is separate and may selectively be later interconnected to the tubing circuit 10 via line 982, preferably through a spike connection 985. In an alternative embodiment, such selective interconnection may be provided via sterile-docking to tubing line 982 as an example (process not shown) utilizing a sterile connecting device (not shown). By way of example, one such sterile connecting device to interconnect a tubing line 982 to such a storage solution container 970, is that offered under the trade name “TSCD” or “SCD™ 312” by Terumo Medical Corporation located in Somerset, N.J. In the alternative above, the selective interconnection may be established utilizing a sterile barrier filter/spike assembly 980. The use of such a sterile barrier filter/spike assembly 980 facilitates the maintenance of a closed system, thereby effectively avoiding bacterial contamination. By way of example, the mechanical, sterile barrier filter 986 (
In order to ensure the maintenance of RBC quality, the collection RBC bag 954, and the storage solution and the anticoagulant used during blood processing should be compatible. For example, the collection RBC reservoir 954 may be a standard PVC DEHP reservoir (i.e. polyvinyl chloride-diethylhexylphthallate) such as those offered by the Medsep Corporation. Alternatively, other PVC reservoirs may be employed. Such a reservoir may utilize a plasticizer offered under the trade name “CITRIFLEX-B6” by Moreflex located in Commerce, Calif. Further, the anticoagulant utilized in connection with the above-described red blood cell collection procedures may be an acid citrate dextrose-formula A (ACD-A).
Nevertheless, according to an embodiment of the present invention as introduced above, the storage solution may be flowed after and/or added to the flow of separated MNC-reduced red blood cells flowing in lines 951 and 952, and flow therewith to and through the filter 960. Filter 960 will remove the majority of the remainder of white blood cells which are left in the MNC-reduced red blood cells. More particularly leukoreduction filtering is desired to establish a white blood cell count of <5×106 white blood cells/unit (e.g. about 250 ml.) to reduce any likelihood of febrile non-hemolytic transfusion reactions. Moreover, such filtering will more desirably achieve a white blood cell count of <1×106 white blood cells/unit to reduce any risk of HLA (i.e. human leukocyte A) sensitization and/or other serious side reactions. Studies have also shown positive effects for pre-storage leukocyte reduction in improving the functional quality of erythrocytes during storage and in decreasing the occurrence of alloimmunization in patients receiving multiple transfusions, as well as being favorable in metabolism reactions such as intra-erythrocyte ATP and/or extracellular potassium levels declining more slowly in filtered products. Perhaps more important is the reduction of transfusion transmitted disease, especially cytomegalovirus (CMV) and/or HIV, inter alia.
Accordingly, the red blood cell collection container 954 receives, in one embodiment, RBCs and additive solution from the red cell filter 960 such that high hematocrit (preferably Hct between 70 and 90 and/or approximately equal to 80), freshly separated MNC-reduced red blood cells alone or together with additive solution are preferably pushed through filter 960 and into the ultimate RBC collection bag 954. Such pushed filtration is shown in
Referring now primarily to
Either simultaneously with the substantially continuous separation and collection process (i.e., as soon as high hematocrit (high-crit) MNC-reduced RBCs are separated from other components and pushed out of vessel 352 to cassette 110 and not diverted back to the donor), or soon after a desired minimum quantity of other blood components have been collected, if desired, the RBC collection/filtration system 950 is activated to filter the MNC-reduced RBCs. This collection process is activated by switching the clamp/valve of device 6 to stop diversion flow through loop 172 and allow flow through line 951 to line 952 and filter 960.
In either case; simultaneously with the continuous collection in bag 954 from the separation vessel 352, or soon after completion of any other non-RBC collection process(es), the MNC-reduced RBCs are flowed preferably by intrinsic pressure pushing (non-active pumping) through filter 960. As such, collection bag 954 may be hung at a level above both the separation vessel 352 and the filter 960 (see
Any air from bag 954, or air caught between the incoming filtered RBCs and bag 954 is ultimately removed to air removal bag 962 through tubing line connection 961. The air is evacuated to air removal bag 962 prior to the flow of the incoming RBCs or is evacuated by the flow of the incoming RBCs. It is also understood that air can also be vented prior to even the separation process by initially running the return pump, (not shown) of the apheresis system. It is also understood that removal of air may also be achieved by other known methods, including, for example, hydrophobic vents and/or by-pass lines. It is desirable to perform the filtering of the MNC-reduced RBCs according to the present invention directly on the machine 6 during the apheresis separation process and without pre-cooling or pre-storing the RBCs. In such a case, these procedures are thus performed without the previously conventional steps of intermediate separation/collection and cooling and storing overnight at 4° C.
Then, either after completion of or during and/or even before the filtration in either of these embodiments, namely, the simultaneous collection and filtering, or in the filtering and collection soon after any other component collection processes, storage solution is flowed to and through the filter and/or added to the MNC-reduced RBCs. Again, this may be performed either before and/or during and/or after completion of the filtration of the otherwise high hematocrit MNC-reduced RBCs through filter 960, although it is preferred that an amount of additional additive or storage solution displace the volume of the filter to recover any residual RBCs therefrom. In particular, a storage solution bag 970 has been connected (by pre-connection or by spike or sterile welding) as depicted in
It should be noted that storage solution does not need to be pumped through the filter. Storage solution may also be flushed through the filter manually, using gravity.
One embodiment of the storage solution addition step is shown in
Alternatively, the embodiment shown in
The embodiment shown in
In either event, upon completion of filtration and/or chasing with additive solution, the collection bag 954 may be separated from the rest of the set 8. Optional clamp 966 may be closed prior to such a separation. The separation may be made by RF sealing the tubing line 965 above the filter 960 or line 952 below the filter 960 and then separating in accordance with U.S. Pat. Nos. 5,345,070 and 5,520,218, inter alia, along the RF-sealed portion of the tubing line. Other well known methods can also be used to close the tubing line and then also separate the RBC collection system 950 from the remainder of the disposable assembly 8. An RBC collection system 950 which would be remaining after one such severing, e.g., below the filter 960, is shown schematically in FIGS. 5 and/or 6A or 6B (see below).
With respect to
Several advantages can be realized utilizing the preconnected disposable assembly and the above-described procedure for high-crit MNC-reduced red blood cell collection and filtration. Such advantages include: consistency in final RBC product volume and hematocrit; reduced exposure of a recipient if multiple units of blood products are collected from a single donor and transfused to a single recipient; reduced time requirements for RBC collection and filtration, including collection of double units of red blood cells if desired, and reduced risks of leukocyte contamination of the final RBC product due to the filter becoming clogged with MNCs which get pushed through the filter into the previously filtered RBCs, thus causing recontamination of the previously filtered RBCs. Further advantages include a system which is less complicated and requires less human interaction. Less human interaction is advantageous because it decreases the possibilities of human contamination.
In order to assist an operator in performing the various steps of the protocol being used in an apheresis procedure with the apheresis system 2, the apheresis system 2 preferably includes a computer graphical interface 660 as illustrated generally in
For example, the display screen optionally may sequentially display a number of pictorials to the operator to convey the steps which should be completed to accomplish the filtering procedure described here. More particularly, a pictorial image optionally may be shown on the screen to pictorially convey to the operator when and/or how to hang the respective RBC and solution bags 954 and/or 970 on the machine 6, initially and/or during use with a storage solution dilution and/or flush (see
Note, a further advantage of the presently described system includes the manner of handling air. More specifically, the present invention eliminates the prior need for the vents and/or by-pass methods and/or apparatuses of conventional red blood cell filters. Moreover, the present invention is capable of delivering this advantage with no reduction in and/or perhaps an increase in the recovery of RBCs that historically have been trapped inside the filtration device.
A means used by the present invention to deliver this advantage is through the provision of a storage solution flush through the filter 960 after the MNC-reduced RBCs have finished filtering therethrough. The storage solution may then be able to wash MNC-reduced RBCs caught therein out of the filter and then into the collection bag 954. Prior devices relied upon vents or by-pass mechanisms to assist in pushing out any RBCs disposed in the filter. Note, though not preferred or needed, vents or by-passes could still be used with the current pushed filtration process, and also with and/or in lieu of the storage solution flush after filtration. Thus such vents or by-passes may be optional features to the described system if it is desired to purge the filter 960 with air or with a combination of air and fluid.
In any event, elimination of the need for vents or by-passes also reduces other prior difficulties such as inadvertent allowances of excess air into the system. Extra air in the present system will not stop or slow the flow of blood or storage solution through the filter in the present invention. The extra air will then be caught within the collection bag 954 and may thus be removed at the end of the overall process to the air bag 962 (air moved thereto by bag positioning or squeezing, etc.). Then, also, because neither vents nor by-passes are required in this embodiment, failures with respect to the operation of such vents are not of concern since the subsequent storage solution flush recovers the RBCs from the filter without the previously desired use of a vent or by-pass. Consequently, also, the filter may be disposed at any of a plurality of alternative vertical dispositions above or below the vessel 352 and/or the collection bag 954. Operation of the present invention should not be hindered by such alternative placements. It is understood, however, that air could also be used to chase either the RBCs or additive solution through filter 960 as described above.
Although the instant invention eliminates the need for by-passes it is understood that one could be provided in the extracorporeal tubing circuit to by-pass the filter 960 in the event the leukoreduction is terminated or is not desired. Similarly it is understood that an optional pressure relief valve or vent could be added to prevent pressure build up in parts of the system including the filter.
The volume of storage solution to be used may, however, be modified depending upon the relative lengths of tubing lines used and/or the air that gets into the system. For example, if 100 ml of storage solution is desired to be mixed with the end product RBCs in collection bag 954 then some certain volume more than 100 ml of storage solution would preferably be fed into the system to compensate for the tubing lengths and the volume of the filter. The amount of solution may be chosen such that 100 ml would go into the collection bag 954 with the additional amount remaining in the tubing line and filter between the cassette 110 and the collection bag 954.
Note, a storage solution dilution during RBC filtration and/or flush after filtration completion are the primary alternatives taught here. However it is possible that storage solution flow into bag 954 may be begun at other times as well as, for example, prior to starting the high-crit or diluted MNC-reduced RBC pushed filtration. Pulsed and/or intermittent flows may also be desirable to assist in removing final volumes of RBCs from the filter 960.
Another alternative introduced hereinabove involves the use of other extracorporeal blood processing systems. Although the preference is for a continuous flow apheresis system, as described here, which includes returning some components back to the donor, batch flow and non-return systems are also useable herewith. For example, a batch mode processor takes in a certain quantity of whole blood which was previously collected from a donor at some point before the separation process is begun. The batch mode processor separates the blood into components (in a centrifuge bowl, e.g.) and then passes the separated components to collection containers. The separated components may also be given back to the donor. The filtration process of the present invention could foreseeably nevertheless operate in substantially the same manner such that the separated MNC-reduced RBCs would nonetheless exist in a substantially high hematocrit state as they are flowed from the separation mechanism, at which point these high-crit separated MNC-reduced RBCs could be flowed to a junction with a storage solution tubing line and from there be passed directly or soon thereafter to and through a filter 960 to be collected ultimately in a collection bag 954. Though continuity may be reduced (or substantially removed), the principles of firstly removing the buffy coat layer and the RBCs located next to the buffy coat layer before pushed filtration (high-crit or diluted) during or soon after the overall separation and collection remain the same. Note, even if flow through the filter 960 stops at any point, or a plurality of points, this does not appear problematic here where any air entry therein is handled by ultimate capture in the air bag 962.
Smaller scale separation and collection devices are also envisioned to be useful herewith. For example, various separation devices (whether centrifugal or membrane or other types) are designed to separate only RBCs and plasma (with the remainder usually remaining in the RBC product), and these can take on smaller scale mechanizations. Nevertheless, the present invention is useful herewith as well in that MNC-reduced RBCs separated hereby may also be freshly push-filtered at high and/or diluted hematocrits. The principle of push-filtering such MNC-reduced RBCs during or soon after the overall separation and collection process remains the same here as well. Thus, whether continuous or in batch mode, a flow of high-crit or diluted, freshly-separated MNC-reduced RBCs can be push-flowed from the separation device immediately or soon after previous processing therein, to and through filter 960 to a collection bag 954.
The foregoing description of the present invention has been presented for purposes of illustration and description. Furthermore, the description is not intended to limit the invention to the form disclosed herein. Consequently, variations and modifications commensurate with the above teachings, and skill and knowledge of the relevant art, are within the scope of the present invention. The embodiments described hereinabove are further intended to explain best modes known of practicing the invention and to enable others skilled in the art to utilize the invention in such, or other embodiments and with various modifications required by the particular application(s) or use(s) of the present invention. It is intended that the appended claims be construed to include alternative embodiments to the extent permitted by the prior art.
This invention claims the benefit of U.S. provisional application No. 60/596,591 filed Oct. 5, 2005.
| Number | Date | Country | |
|---|---|---|---|
| 60596591 | Oct 2005 | US |
