INCREASED YIELD BLOOD COMPONENT COLLECTION SYSTEMS AND METHODS

Abstract: A system (10) which embodies the features of the invention includes first means (12) for establishing a flow of whole blood from a donor and second means (14) for separating the whole blood into essentially plasma and plasma-poor components without using a centrifugation device. The system (10) also includes third means (16) for collecting a volume of the separated plasma and forth means (18) for returning the plasma-poor components associated with this collected volume of separated plasma to the donor. The system further includes fifth means (20) for collecting a volume of whole blood. In the preferred embodiment, the second means (14) includes microporous membrane means (22) which is operative for filtering the plasma from the other components of whole blood. Also in the preferred embodiment, the fifth means (20) includes means (60) for collecting the components of the whole blood in response to subsequent centrifugal separation.

Description: INCREASED YIELD BLOOD COMPONENT COLLECTION SYSTEMS AND METHODS FIELD OF THE INVENTION: This invention generally relates to systems and methods which enable the collection and separation of whole blood into its therapeutic components. This invention also generally relates to whole blood collection and separation systems and methods which enable the storage of whole blood and its various therapeutic components for the maximum allowable periods. This invention also generally relates to εemiperrrieable membrane systems and methods. OMPI BACKGROUND AND OBJECTS OF THE INVENTION: At the present time, over 12 million units of whole blood are collected from volunteer donors in the United States each year. Because of the advent *-> of blood component therapy * approximately 60% to 80% of the whole blood collected today is not itself stored and used for transfusion. Instead, the whole blood is first separated into-its clinically proven components, which are themselves individually stored 0 and used to treat a multiplicity of specific conditions and diseased states. The clinically proven components of whole blood include red blood cells, which can be used to treat chronic anemia; cryoprecipitate, which is rich 5 in Clotting Factor VIII (also known as AHF) and can be used to treat hemophilia; plasma, which can be used to restore all of the clotting factors to patients; platelets, which can be used to treat thrombocy openia; as well as numerous other 0 plasma-based fractions, such as albumin, protein fraction, gamma globulin, and various other specific coagulation protein concentrates. The present medical consensus is that care of a patient is improved by providing only the 5 therapeutic components of whole blood which are required to treat the specific disease. The demand for therapeutic components of whole blood is thus ever-increasing. Likewise, the demand for safe and effective systems and methods for collecting, 0 separating, and storing the therapeutic components of whole blood grows accordingly. OMP One desirable feature for a blood collection and separation system and method is the capability to maximize, to the greatest extent possible, the yield of clinically proven blood components during a single collection procedure. The importance of this feature stems in large part from the traditionally limited number of individuals who volunteer to donate whole blood- on a regular basis. The importance of this feature also stems from the periodic nature of blood collection procedures themselves. In the United States, for example, a collection of one unit of whole blood (approximately 450 milliliters) from an individual volunteer donor for separation into its various components can be undertaken only once every 8 weeks if the red cells are retained for storage. Maximizing the component yield for each procedure can help to offset these supply-side factors which together limit the supply of available whole blood. Another desirable feature for a blood collection and separation system and method is the capability of yielding components which are suited for storage for prolonged periods. This feature, which also helps to offset the limited supply of available whole blood, is closely related to the degree of sterility a given blood collection system . can assure. For example, in the United States, whole blood and components which are collected and processed in a nonsterile, or "open", system must be transfused within twenty-four (24) hours of collection. On the other hand, in the United States, whole blood and red cells which are collected in a sterile, or "closed", system may be stored for upwards to thirty-five days, depending upon the type of anticoagulant and storage medium used. Likewise, platelets which are collected in a "closed" system may be stored for upwards to five days, and possibly longer, depending upon the ability of the storage container to maintain proper storage conditions. Plasma which is collected in a "closed" system may be frozen for even more prolonge -storage periods. In the United States, Federal Regulations CTitle 21 C.F.R. §640.16(b)J define a "closed" bloo collection system as one in which the initially sterile'blood collection and transfer containers are integrally attached to each other and not open to communication with the atmosphere. Furthermore, to remain a "closed" blood collection system in the United States, the blood collection container of the system cannot be "entered" in a non-sterile fashion after blood collection. By present United States standards, an entry into a blood collection system which presents the probability of non-sterility which exceeds one in a million (i.e., greater than 10- ) constitutes a "non-sterile" entry. A non-sterile entry "opens" a heretofore "closed" system and dictates the significantly shortened storage periods for the blood and components collected and processed within the system. Representative examples of known whole blood collection assemblies include the following United States Patents: Earl . 3,064,647 andell et al 3,078,847 , Bellamy Jr. 3,110,308 Tenczar Jr. 3,187,750 Viguier 3,870,042 Garber et al 3,.986,506 Djerassi 4,111,199 Smith 4,222,379 '' Representative examples of known commercially available whole blood collection assemblies are sold by Fenwal Laboratories, Inc. (a division of Travenol Laboratories, Inc., Deerfield, Illinois); Delmed Corp., Irvine, California; and Cutter Laboratories, Inc., Berkeley, California. It should be noted that most, if not all, of the above-identified blood collection assemblies are "closed" as judged by United States standards. The assemblies thereby enable the storage of blood and its various components for the maximum allowable periods. However, none of the above-cited systems enables the processing of more than one unit of whole blood during a given procedure. Thus, none of these assemblies has the capability of effectively increasing the component yield per procedure. Furthermore, all of the above-identified blood collection assemblies rely upon non-automated batch centrifugation to separate the collected unit of whole blood into various components. During batch centrifugation, the collected unit of whole blood is first centrifugally separated within the original collection container into platelet-rich plasma and red blood cells. The 5 platelet-rich plasma is then transferred into another container which is integrally attached to the original collection container for further centrifugal separation into platelet-poor plasma and platelets. Batch centrifugation is normally done at 10. central blood processing facilities. Therefore, whole blood which is collected by mobile collection units must be returned to the processing facility for batch centrifugation, usually within four hours of collection. As a result, mobile collection 15 procedures, which play an important part in maintaining adequate reserves of blood components, tend to be costly and time consuming. Furthermore, during the course of non-automated batch centrifugation, approximately 100 20 milliliters of plasma otherwise suited for storage is "lost", because some of it remains with the red blood cells, and some of it is transferred along with the platelets. Therefore, using conventional batch centrifugation, plasma yields cannot be optimized. 25 A novel blood collection systems which is capable of optimizing component yields using non-automated batch centrifugation techniques is disclosed in copending Ronald A. Williams et al, U.S. Patent Application No. 373,555, filed April 30, 1982, and entitled INCREASED YIELD BLOOD COLLECTION SYSTEMS AND METHODS, which is a continuation-in-part of U.S. Patent Application No. 316,918, filed October 30, 1981. It is possible to boost component yields by employing blood collection and separation systems which are capable of being used in combination with automated "continuous flow" centrifugal blood processing procedures. In such a procedure, whole blood from a donor is continuously circulated through the separation system. A portion of the components are collected (or "harvested"), and the remainder are returned to the donor. As a result, significantly larger total volumes of whole blood can be processed using a continuous flow procedure than using a single unit batch collection procedure. One of the results is larger yields of plasma-based fractions. For example, in a single unit batch collection procedure, approximately 5 x 10 platelets can be harvested; whereas, in a continuous flow procedure, upwards to 60 x 10 platelets can be collected. Representative examples of "continuous flow" extracorporeal blood processing procedures and devices include the following United States Patents Cullis et al 4,146,172 Cullis et al 4,185,629 Representative examples of "continuous flow" systems also include the copending Patent Applications of DeVries, Patent Application No. 100,975 (filed December 6, 1979), entitled MONITOR O PI AND FLUID CIRCUIT ASSEMBLY, which is a continuation of DeVries, U.S. Patent Application No. 843,223 (filed October 18, 1977), now abandoned; and Ronald A. Williams et al, Patent Application No. 403,832 (filed July 30, 1982) and entitled INCREASED YIELD CONTINUOUS FLOW BLOOD COMPONENT COLLECTION SYSTEM. An example of a commercially available device which operates in a "continuous flow" mode is the CS-3000® Blood Cell Separator, which is manufactured and sold by Fenwal Laboratories. "Continuous flow" processing systems typically require the use of relatively expensive, large, and sophisticated centrifugation machines. These machines are not suited for easy transport from one collection site to another, and are usually installed only at central blood processing facilities- They are simply not available to boost the yields of mobile blood collection units. Yet another overall consideration in the field of blood component collection is donor time. In both non-automated batch processing and automated "continuous flow" processing, the donor is required to be present virtually throughout the entire collection and separation procedure. The period of time a person must spend in order to donate blood cannot help but bear upon that person's willingness to regularly donate blood in the first place. With the foregoing considerations in mind, one of the principal objects of this invention is to provide blood collection systems and methods which maximize, to the greatest extent possible, the yield of blood components obtained during a single collection procedure in a manner which also assures the maximum available storage period for each of the components collected, as measured by applicable United States standards. Another principal object of this invention is to provide blood collection systems and methods which are compact and easily handled and which can be efficiently manufactured, stored, and utilized by the operator, particularly at remote collection sites away from the central processing facility. Yet another one of the principal objects of this invention is to provide blood collection systems and methods which, in addition to the just described attributes, do not depend entirely upon costly, relatively large, and sophisticated processing devices which cannot be easily transported to a remote collection site. Still another of the principal ojects of this invention is to provide blood collection systems and methods which seek to minimize, to the greatest possible extent, donor time during a given procedure. SUMMARY OF THE INVENTION: To achieve these and other objects, the invention provides increased yield blood collection systems and methods which maximize, to the greatest extent possible, the yield of blood components obtained during a single collection procedure in a manner which also assures the maximum permissible storage period for each of the components collected. OMPI A system which embodies the features of the invention includes first means for establishing a flow of whole blood from a donor and second means for separating the whole blood into essentially plasma and plasma—poor components without using a centrifugation device. The system also includes third means for collecting a volume of the separated plasma and fourth means for returning the plasma-poor components associated with this collected volume of separated plasma to the donor. The system further includes means for collecting a volume of whole blood. In the preferred embodiment, the second means includes microporous membrane means which is operative for filtering the plasma from the other components of whole blood. Also in the preferred embodiment, the fifth means includes means for collecting the components of the whole blood in response to subsequent centrifugal separation. * Use of the just-described system enables the collection, via filtration, of upwards to 425 milliliters of plasma, followed by the collection of one unit (450 milliliters) of whole blood. The collected whole blood can be further separated, via conventional batch centrifugation procedures, into still additional components, such as plasma,, platelets, and red cells. The total volume of components which can be collected using the system during a given procedure will depend upon the physiology of the donor and the maximum allowable total volumes permitted by governing regulations. However, using the system, a blood collection facility is able to significantly OMPI increase its plasma yields during each collection procedure over the plasma yields obtained using conventional non-automated batch centrifugation techniques. Furthermore, and significantly, the system achieves its increased component yields without reliance upon relatively complicated and sophisticated "continuous flow" centrifugal devices. For example, only a conventional peristaltic pump is necessary to initially separate the plasma from the red cells and return the plasma-poor comonents to the donor, and only non-automated batch centrifugation equipment is required to later separate the collected volume of whole blood into additional components. In the preferred embodiment, the elements of the system are integrally connected together and offer interconnecting fluid paths which are closed from communication with the atmosphere. The system , thus constitutes a "closed" system, as judged by applicable standards in the United States. Thus, all of the components which are collected are suited for maximum allowable storage periods. To further enhance the storage of the collected components, in one embodiment, each of the collection means is imparted with a predetermined physical characteristic which is beneficial to the long-term storage of the particular blood component collected. A method which embodies the features of the invention includes the steps of establishing a flow of whole blood from the donor and noncentrifugally separating the whole blood into essentially plasma OMPI and plasma-poor components. The method further includes the steps of collecting a volume of the separated plasma, while continuously returning the associated plasma-poor components to the donor. The ^ method further includes the step of collecting a volume of whole blood. In a preferred embodiment, the unit of whole blood is subsequently separated into its components using batch centrifugation methods. Preferably, the step of collecting the unit of whole blood occurs after the step of collecting the filtered plasma. As a result, the donor is required to be present only during the collection of the volume of plasma and the unit of whole blood. The subsequent separation of the whole blood into its various components can occur without the presence of the donor. Donor time during this extended yield procedure is thus minimized to the greatest extent possible. Another system and associated method which embody the features of the invention employ, like the system and method heretofore described, first means for establishing a flow of whole blood from a donor and second means for noncentrifugally separating the whole blood into essentially plasma and plasma-poor components. Also like the first-described system and method, this embodiment of the system' and method employ third means for collecting a volume of the separated plasma. However, unlike the system and method heretofore described, this system and method employ means for collecting a volume of the OMPI plasma-poor components associated with the collected volume of plasma. The system and method further employ fourth means for returning the remaining volume of the plasma-poor components to the donor. Use of the just-described system and method enables the collection, during a single procedure, of upwards to 320 milliliters of the plasma-poor components (notably, packed red blood cells having approximately a 60 hematocrit), and upwards to 555 milliliters of plasma. Again, the total volume of components collected will depend upon the physiology of the donor as well as applicable maximum allowable volumes dictated by governing regulations. Nevertheless, the system and method provides increased overall plasma yields, compared to conventional non-automated batch centrifugation techniques. Significantly, the foregoing embodiment of , the system and method requires only a peristaltic pump to perform the entire collection procedure. The system and method are thus extremely mobile and suited for use at remote collection facilities. Like the first described system, the foregoing system preferably constitutes a closed system, and all of the components which are collected are suited for maximum allowable storage periods. Also as before, each of the collection means is preferably imparted with a predetermined physical characteristic which is beneficial to the long-term storage of the particular blood component collected. To further simplify the storage and transport of any of the systems heretofore described, in one embodiment, all or some of the collection means comprise physically separate entities which can be separately manufactured, stored, and transported, and which can be selectively joined to form the required system at the collection site, all without compromising the sterile integrity of any of the collection means or the formed system as a whole. Other features and advantages of the invention will be pointed out in, or will be apparent from, the specification and claims, as will obvious modification of the embodiments shown in the drawings. DESCRIPTION OF THE DRAWINGS: Fig. 1 is a functional diagrammatic view of an increased yield blood component collection system which embodies the features of the invention; Fig. 2 is a functional block diagrammatic view of a method which utilizes the increased yield blood component collection system shown in Fig. 1 and which embodies the features of the invention; Fig. 3 is a functional diagrammatic view of another increased yield blood component collection system which embodies the features of the invention; Fig. 4 is an enlarged side view, with portions broken away and in section, of the microporous membrane device which is associated with the system shown in Figs. 1 and 3; Fig. 5 is an end section view, with a portion broken away and in section, of the microporous membrane device taken generally along line 5-5 in Fig. 4; Fig. 6 is a functional block diagrammatic view of a method which utilizes the increased yield blood component collection system shown in Fig. 3 and which embodies the features of the invention; PI Fig. 7 is a plan view of yet another increased yield blood component collection system which embodies the features of the invention; Fig. 8 is an enlarged view of a portion of the increased yield collection system shown in Fig. 7; Fig. 9 is a further enlarged' view, with portions broken away and in section, of a portion of the system shown in Fig. 7, showing the connector means associated with the system in an uncoupled relationship; Fig. 10 is an enlarged view, with portions broken away and in section, of the connector means shown in Fig. 9 in a coupled relationship and being exposed to a radiant energy-induced melting apparatus to open a fluid path therethrough; and Fig. 11 is an enlarged view, with portions broken away and in section, of the connector means shown in Fig. 10 after the fluid path has been opened therethroug . Before explaining the embodiments of the invention in detail, it is to be understood that the invention is not limited in this application to the details of construction and the arrangement of components as set forth in the following description or as illustrated in the accompanying drawings. The invention is capable of other embodiments and of being practiced or carried out in various ways. Furthermore, it is to be understood that the phraseology and terminology employed herein is for the purpose of description and should not be regarded as limiting. - * ξ l s . l l m Kt OMPI DESCRIPTION OF THE PREFERRED EMBODIMENT: An increased yield blood component collection system 10 is shown in Fig. 1. The system 10 includes first means 12 for establishing a flow of whole blood from a donor and second means 14 for separating the whole blood into essentially plasma and plasma-poor components (which can include red blood cells, leucocytes, and platelets). The system 10 further includes third means 16 for collecting a volume of the separated plasma and fourth means 18 for returning the plasma-poor components which are associated with the collected volume of separated plasma to the donor. The system 10 further includes fifth means 20 for collecting a volume of whole blood. The second means 14 is operative for separating the whole blood without using centrifugal separation techniques. Noncentrifugal separation techniques include membrane filtration, glass filtration, and depth filtration, as well as the use of absorption columns, chemical separation, and electrical separation. In the illustrated and preferred embodiment, the second means 14 includes microporous membrane means 22 which is operative for separating the plasma from the other components of whole blood (i.e., the plasma-poor components heretofore identifie ). The microporous membrane means 22 may be variously constructed. In the illustrated embodiment, and as best shown in Figs. 4 and 5, the -gUREX§- OMPI - f7~- membrane means 22 includes a tubular housing 24 in which a bundle of microporous hollow fiber membranes 26 is mounted. The membranes 26 are preferably mounted within the housing 24 utilizing conventional potting techniques, such as the one disclosed in Mahon, U.S. Patent 3,228,876. During the potting operation disclosed in the above patent, a liquid potting compound 28, typically polyurethane, is introduced into opposite ends of the housing 24 to impregnate the exterior areas of the membranes 26 about and between the ends 27 of the individual fibers (see Fig. 5). Ingress of the potting compound 28 into the bores of the fiber ends 27 can be prevented by various means, such as those discussed in the above-cited Mahon patent. After the potting compound 28 has cured and the fiber ends 27 opened, end caps 30 and 32 may be sealed to the potted ends of the housing 24. An inlet port 31 is formed on the end cap 30, and an outlet port 33 is formed on the other end cap 32. Circumferentially surrounding the bundle of hollow fiber membranes 26 is an open volume 34 (see Fig. 4) which is sealed at each end by the cured potting compound 28. An outlet port 36 communicates with the volume 34. Materials from which the microporous hollow fiber membranes can be made to accomplish the separation of plasma from whole blood include certain thermoplastic polymers, such as polypropylene. These materials can be formed into hollow fibers by known processes such as solution spinning or melt spinning. For example, a polypropylene hollow fiber can be manufactured which has a wall thickness of approximately 150 microns, an interior diameter of approximately 320 microns, a maximum pore size of approximately .55 microns, and an average pore size of approximately .30 microns. Such a hollow fiber is commercially available from Enka AG, the Federal Republic of Germany, and is well-suited for the purposes herein described. In an alternate embodiment (not shown), the membrane means 22 can take the form of a device having spaced-apart, generally planar membranes made of the.-same or comparable microporous material. An example of such a device is disclosed in Ξdelman et al, U.S. Patent 4,313,813. As can be seen in Fig. 1, the system 10 includes conduit means 38 which establishes a plurality of interconnected fluid paths, each of which is preferably integrally connected with its associated element of the system 10 and is thereby closed from communication with the atmosphere. The "closed" embodiment of the system 10 is preferred, because it permits the storage of the collected components for the maximum allowable time. However, it should be appreciated that the system 10 could be "open" and operate in the same fashion, except that the plasma collected could be used only for fractionation purposes (which includes a subsequent sterilization step), and the collected unit of whole blood and its components would have to be reinfused within twenty-four (24) hours. In the illustrated "closed" embodiment shown in Fig. 1, the portion of the conduit means 38 associated with the first means 12 includes first branch means 40. In the illustrated embodiment, the first branch means 40 takes the form of a length of flexible tubing made of hemocompatible material, such as plasticized polyvinyl chloride, which communicates, at one end, with the inlet port 31 of the membrane means 22 and, at the other end, with a phlebotomy needle 42. The first branch means 40 includes a portion 41 which is capable of being operatively connected with external pump means 44 to introduce whole blood from the donor into the membrane means 22. The pump means 44 may be variously constructed. However, in order to meet all of the collection objectives of the system 10 (which includes extended storage times), operative contact . between the tubing portion 41 and the pump means 44 must not compromise the sterile integrity of, or otherwise "open", the system 10, as judged by applicable standards in the United States. In the illustrated embodiment, the pump means 44 takes the form of a conventional peristaltic pump, such as one manufactured and sold by Renal Systems under the trade name MINIPUMP. The pump 44 serves to repeatedly compress and expand the tubing portion 41 and causes whole blood to flow from the donor through the first branch means 40 and into the hollow fibers 26. OMPI By controlling the pump speed, the pressure at the inlet port 31 of the membrane means 22 can be maintained to provide the proper flow characteristics within the hollow fiber membranes 26 to cause effective separation of the plasma from the rest of the components of the whole blood without hemolysis. The desired flow conditions are disclosed, for example, in Blatt et al, U.S. Patent 3,705,100. As the plasma separates, it collects in the open volume 34. Meanwhile, the plasma-poor components (essentially consisting of red blood cells, leucocytes, and platelets) exit the outlet port 3.3. The conduit means 38 further includes second branch means 46 which takes the form of a length of flexible hemocompatible tubing communicating with the plasma filtrate volume 34 and the plasma collection means 16. * In the illustrated embodiment, the plasma collection means 16 includes one or more flexible containers or bags 48, hereafter referred to as the first collection container. In Fig. 1, the second branch means 46 is integrally connected with the first collection container or containers 48. The second branch means 46 is thus operative for- transferring the plasma filtrate from the volume 24 into the first container 48. The conduit means 38 which is associated with the return means 18 includes third branch means 50 for returning the plasma-poor components exiting the membrane means 22 to the donor. The third conduit means 50 takes the form of a length of flexible hemocompatible tubing which communicates, at one end, with the outlet port 33 of the membrane means 22 and, at the other end, with another phlebotomy needle 52. Each phlebotomy needle 42 and 52 may be integrally connected to the respective branch conduit means 40 and 50 and be normally closed from communication with the atmosphere by a conventional needle cover 54 or sheath (not shown in Fig. 1, but shown in the embodiment shown in Fig. 4). Alternately, each branch conduit means 40 and 50 can include a conventional needle adaptor (not shown) to receiye the needles 42 and 52 at the time - venipuncture is desired. An example of such a needle adaptor is one utilized in FENWAL® Blood Recipient Sets sold by Fenwal Laboratories. While two individual phlebotomy needles 42 and 52 are shown in Fig. 1, it should be appreciated* that the first and third branch means 40 and 50 could communicate in common with a single, multiple lumen needle of conventional construction (not shown) . The conduit means 38 associated with the whole blood collection means 20 includes fourth branch means 56 which takes the form of a length of flexible hemocompatible tubing communicating"with the first branch means 40 upstream of the membrane means 22. The fourth branch means 56 is thus operative for diverting whole blood away from the membrane means 22 and into the whole blood collection means 20 of the system 10. The remainder of the whole blood collection means 20 may be variously constructed. In the illustrated and preferred embodiment, the collection means 20 includes a primary container 58 (hereafter referred to as the second collection container) integrally attached to the fourth branch means 56. The collection means 20 also preferably includes at least one transfer container 60 which is integrally attached in fluid communication with the second collection container 58. The transfer container 60 or containers enable the whole blood collected in the second collection container 58 to be sequentially processed using conventional batch centrifugation methods into its various components, such as red blood cells, platelets, and platelet-poor plasma. The number of transfer containers 60 associated with the second collection container 58 can vary according to the collection objectives of the system 10. In the illustrated embodiment, two transfer containers 60 are shown, one (designated 60a) to store platelets, and the other (designated 60b) to store platelet-poor plasma. The remaining red cells are retained in the second collection container 58 for storage. In the illustrated embodiment, the system 10 also includes an integrally attached source 62 of a sterile anticoagulant solution and an integrally attached source 64 of a sterile saline solution. In this arrangement, the conduit means 38 includes fifth branch means 66 which takes the form of a length of flexible hemocompatible flexible O PI tubing integrally connected with the anticoagulant source 62 and the first branch means 40 upstream of the pump means 44. The fifth branch means 66 is thus operative for introducing the anticoagulant solution * into the system 10 to prevent the donor • s blood from clotting during the course of the procedure. A peristaltic pump (not shown) may be used to meter the introduction of the anticoagulant solution. Also in this arrangement, the conduit means 38 includes sixth branch means 68 which takes the form of a length of flexible hemocompatible tubing integrally connected with the saline source 64 and the first branch means 40 upstream of the pump means 44. The sixth branch means 68 is operative for introducing saline into the system 10 to purge air from the system 10 prior to the procedure and to wash components from the system 10 after the procedure. The source 62 of anticoagulant solution includes a bag 70 made of a plasticized polyvinyl chloride material or the like which contains the sterile anticoagulant. A suitable overwrap 72 is provided to prevent evaporation of the saline from the bag 70 during storage. The fifth branch means 66 is integrally connected with the bag 70 and extends (via a drip chamber 74) to integrally join the first branch means 40 upstream of the pump means 44. The source 64 of sterile saline likewise includes a bag 76 having a suitable overwrap 78. The sixth branch means 68 is also integrally connected with the bag 56 and proceeds (via another drip chamber 80) to join the first branch means 34 upstream of the pump means 44. " po The integral connection between the overwrapped anticoagulant and saline bags 70 and 76 and their associated branch conduits, respectively 66 and 68, may be variously made. In the illustrated embodiment, a port block assembly 82 is used, such as the one described in Boggs et al, U.S. Patent Application Serial No. 282,894, filed July 13, 1981. In an alternate embodiment (not shown), the membrane means 22 can itself be suitably preprimed with saline, thereby eliminating the need for a separate source 64 of saline. To further facilitate priming the system 10, the sixth branch means 68 can include a vent passage 69 communicating with the third branch means 50. The vent passage 69 is also integrally connected with the saline bag 76. This passage 69 recirculates the saline used to prime the system 10 back into the saline bag 76. In another arrangement, instead of using the vent passage 69, the system 10 can optionally include a third collection container 84 (shown in phantom lines in Fig. 1) communicating with the third conduit means 42 via an integrally connected vent passage 85 (also shown in phantom lines). In this arrangement, the third collection container 84 collects the volume of saline used to prime the system 10. Still alternately, the saline solution introduced to prime the system 10 can be directed outwardly of the system 10 into an external container through the phlebotomy needle 52. To control and direct the flow of whole blood and its components through the system, valve means 86a, b, c, d, e, f, and g is provided inline with, respectively, the first; second; third; fourth; fifth; and sixth branch means (respectively 40; 46; 50; 56; 66; and 68), and each of the Optional vent passages 69 or 85. Each of the valve means 86 is preferably a manually operable clamping mechanism, such as a roller clamp or a hemostat. Attention is now directed to Fig. 2, in which a method hich embodies the features of the invention and which can utilize the system 10 as heretofore described is shown. As shown in Fig. 2, the method includes the step of drawing whole blood from the donor for separation by filtration or other noncentrifugal technique into essentially plasma and plasma-poor components (notably, red blood cells). In addition , to the red blood cells, the platelet-poor components C n also include platelets and leucocytes. As shown in Fig. 2, a volume of plasma is collected, and the red blood cells (and any associated platelets and leucocytes) which were associated with the collected volume of separated plasma, are returned to the donor. The method also includes the step of collecting a volume of whole blood from the donor. Preferably, in the interest of minimizing the donor's time, this unit of whole blood is collected after the volume of plasma. After this whole blood collection step, the donor's presence is no longer required. The collection procedure, per se, can thus be terminated as is shown in Fig. 2. O PI * Preferably, the method further includes the step, after the collection procedures have been terminated, of separating the collected volume of whole blood into other blood components such as red *. blood cells, platelet-poor plasma, and platelets. These additionally harvested components are collected and, together with the heretofore collected unit of plasma, constitute the total volume of components collected during the procedure which embodies the features of the invention. In the preferred embodiment, as is shown in Fig. 2, the whole blood components are separated utilizing conventional batch centrifugal separation. Preferably all of the steps are performed in a manner which does not expose the whole blood, the returned red cells, and the collected volumes of components of whole blood to communication with the atmosphere. Maximum permissible storage times for . the collected components can thus be achieved. The blood collection system 10 (shown in Fig. 1) can perform the just described method (shown in Fig. 2) as follows. By opening up the valve means 86f associated with the sixth branch means 68 and any associated vent passages 69 or 85 (i.e., valve means 86g), the system 10 can be suitable primed with saline. The venipunctures can then be made. By closing the valve means 86f and 86g, and by opening up the valve means 86e associated with the fifth branch means 66, as well as opening the valve means 86a and c associated with the first and third branch means 40 and 50, whole blood can proceed from the donor into the membrane means 22 under the "gJRE ^ OMPI influence of the pump means 44. The valve means 86d (associated with the whole blood collection means 20) is preferably closed at this point in the procedure. In the membrane means 22, the plasma is separated from the whole blood. The plasma collects in the volume 34. When the valve means 86b associated with the second branch means 46 is opened, the plasma can be collected'into the first collection container 48 or container. The plasma-poor components exit the membrane means 22 and proceed, via the third branch means 50, back to the donor. The portion of the system 10 and method just-described constitute a "continuous flow" blood processing system and method. This is because whole blood from the donor is continuously being circulated into and through the membrane means 22. The plasma is continously being collected in the first container 48 up to a desired volume, and the remaining plasma-poor components are continuously being returned to the donor. Furthermore, after the desired amount of plasma has been collected, the valve means 86b and 86c associated, respectively, with the second and third branch means 46 and 50 can be closed and the valve means 86d associated with the fourth branch means 56 can be opened to divert a volume of whole blood into the second collection container 58. Once the desired volume of whole blood is collected in the second container 58, the collection procedure can be terminated. The second collection container 58 and integrally attached transfer containers- 60 can then be next separated from the system 10, using a spaced apart pair of hand seal clips (not shown), or by the ^ formation of a hermetic, snap-apart seal using a HEMATRON® dielectric sealer (also not shown) sold by Fenwal Laboratories. The separated unit can then undergo batch centrifugation as heretofore described. The total volume of components which can be collected utilizing the system shown in Fig. 1 or the method illustrated in Fig. 2 will depend upon the physiology of the donor as well as the maximum allowable volume limits prescribed by applicable governing regulations. For example, in the United States, the maximum allowable volume limit is approximately 770 milliliters of plasma (which includes approximately 50 milliliters of a sodium citrate anticoagulant) for donors weighing less than 175 pounds, and approximately 925 milliliters of plasma (again including approximately 50 milliliters of sodium citrate anticoagulant) for donors weighing 175 pounds or more. In the context of these presently prescribed maximum limits, the system and method are capable of collecting from a healthy donor weighing less than 175 pounds approximately 270 milliliters of plasma (including anticoagulant volume) and approximately 500 milliliters of whole blood (including anticoagulant volume) . For a donor weighing 175 pounds or more, the system and method are capable of collecting approximately 425 milliliters of plasma (including anticoagulant volume) and approximately 500 milliliters of whole blood (including anticoagulant volume) during a given procedure. The whole blood collected can be further sequentially processed into an additional volume of platelet-poor plasma, a volume of platelets, and a unit of packed red blood cells. Significantly increased component yields, and notably in plasma yields, are thus possible by using the system and method. It is significant to note that the system 10 as described requires only a single peristaltic pump 44 and 'conventional batch centrifugation techniques to achieve its increased yield objectives. The system 10 thus is not dependent upon large and technologically sophisticated continuous flow centrifugal blood processing devices. Furthermore, because each of the various branch means and vent passages is closed to communication with the atmosphere, the system 10 as a whole constitutes, after sterilization, a closed system, as judged by applicable standards in the United States. This allows the maximum, permissible storage times for each of the components collected. o further enhance the storage of the components collected by system 10, at least a portion of the first and second collection containers 48 and 58, as well as the transfer containers 60, is purposely imparted with a predetermined physical characteristic which is beneficial to the intended storage function of the containers 48, 58, 60. More particularly, to maximize the storage times of components collected by the system 10, the plasma collection container 48 and the plasma transfer container 60b are each is preferably made of a material having a relatively high low-temperature strength to withstand freezing of the • plasma for prolonged storage. Candidate materials, for this purpose includes various polyolefin materials, such as low density polyethylene and copo ' lymers of polyethylene and polypropylene, including those containing a major amount of polypropylene. - To enhance the storage of the plasma-poor components (in particular, the red cells), the second collection container 58 is preferably made of a material which is known to suppress hemolysis in red cells during storage. Candidate materials for this purpose include polyvinyl chloride plasticized with . di-2-ethylhexylphthalate (DEHP) . Alternatively, or in addition, an additional transfer container 60c (shown in phantom lines in Fig. 1) can communicate with the second collection container 58. This transfer container 6oc includes an isotonic red cell storage solution (designated "S" n Fig. 1) which is suited for suppressing hemolysis during storage. The solution S could include ingredients such as saline, adenine, mannitol, and glucose, such as the solution disclosed in Grode et al, U.S. Patent 4,267,269, or in copending Grode et al, U.S. Patent Application No. 377,110, filed May 11, 1982, and entitled RED CELL STORAGE SOLUTION AND METHOD. To maximize the allowable storage time of platelets collected in the system 10, the transfer container 60a in which platelet concentrate will ultimately be stored preferably has a gas transfer characteristic beneficial to prolonged platelet storage. More particularly, the transfer container 60a would preferably have a gas transfer characteristic which exceeds that of polvinyl chloride plasticized with di-2-ethylhexylphthalate (DEHP). For example, the transfer container 60a can include a polyolefin-type container which is disclosed in Gajewski et al, U.S. Patent 4,140,162, or a polyvinyl chloride container which has been plasticized with tri-2-ethylhexyl trimellitate (TEHTM), as disclosed in Warner et al, U.S. Patent 4,280,497. Alternately, or in addition, the platelet • transfer container 60a can include a platelet storage media (not shown) which is suited for maintaining platelet viability during storage. Because red cells are collected, the extended yield procedure can be repeated once every eight weeks. Attention is now directed to the blood collection system 11 shown in Fig. 3. The system 11 shares many common features of the system 10 shown in Fig. 1 and heretofore described. Common components are assigned the same reference numerals as in the system 10 shown in Fig. 1. In the arrangement shown in Fig. 3, the system 11 includes microporous membrane.means 22 as heretofore described. The system 11 also includes the associated branch conduit means 40; 46; 50; 66; and 68. The first branch conduit means 40 includes the portion 41 which can be operatively connected with the appropriate pump means 44. As in the first-described embodiment, it is preferred that the system 11 be "closed" to obtain the maximum permissible storage periods. The first and second collection containers 48 and 58 and the anticoagulant and saline bags 70 and 76.'are also provided. As shown in Fig. 3, the priming volume of saline can be vented from the system 11 in any manner heretofore discussed in context of the first system 10. However, in the system 11, unlike the first described system 10, the counterpart of the second collection container (which is identified with the numeral 59 in Fig. 3) is situated downstream of the microporous membrane means 22 in fluid communication with the third branch means 50 via branch conduit means 57. In this arrangement, the branch conduit means 57 diverts the plasma-poor components tnotably, the red blood cells) away from the donor and into the second collection container 59. Attention is now directed to Fig. 6, in which a method which embodies the features of the invention and which can utilize the system 11 shown in Fig. 3 is illustrated. The method includes the steps of establishing a flow of whole blood from the donor for noncentrifugal separation (using the membrane means 22) into essentially plasma and plasma-poor components (which include red blood cells, platelets, and leucocytes), as heretofore described. Also as heretofore described, a volume of separated plasma is collected (in the first collection container 48) . However, unlike the method shown in Fig. 2, in the method shown in Fig. 6, a volume of the plasma-poor components (notably, the red blood cells) associated with the collected volume of separated plasma is also collected (in the second collection container 59), with the remaining volume of the. ; plasma—poor components being returned to the donor. if desired, a transfer container 61a (shown in phantom lines in Fig. 3) can be integrally attached to the second collection, container 59 to additionally collect by various means (such as by washing) the platelets associated with the red blood cells collected in the container 58. The system 11 shown in Fig. 3 can be utilized to perform this method following generally the same sequence as described with the collection procedure associated with the system 10 shown in Fig. 1. As with the method and system 10 heretofore described, utilizing the system 11 to perform the method shown in Fig. 6 can result in increased yields the total volume of which ultimately depends upon the physiology of the donor as well as the maximum allowable limits prescribed by governing regulations. OMPI In the context of the maximum volume limits heretofore discussed, the system 11 is capable of collecting, from donors weighing less than 175 pounds, approximately 450 milliliters of plasma in the first collection container 48 and approximately 320 milliliters of packed red cells, having a hematocrit of about 60, in the second collection container 59; and, from donors weighing 175 pounds or more, approximately 600 milliliters of plasma and aproximately 320 milliliters of packed red cells (also having a hematocrit of about 60). As before described, the first and second collection containers 48 and 59, and the optional transfer container 61a, may each be purposely imparted with a physical characteristic which is beneficial to its intended storage function. Attention is now directed to the blood collection system 88 shown in Fig. 7. The system 88- shares many common features of the systems 10 and 11 heretofore described, and is capable of being selectively configured either as system 10 or system 11. Common components are assigned the same reference numerals. In the arrangement shown in Fig. 7, the system 88 includes microporous membrane means 22 as heretofore described. The system 88 also includes the same associated branch conduit means 40; 46; 50; 56? 57; 66; and 68. The first branch means 40 includes the portion 41 which can operatively connected with the appropriate pump 44 (not shown in Fig. 7). ' O PI - The first and second collection containers 48 and 58 (in the Fig. 1 system 10) or 59 (in the Fig. 3 system 11), as well as the anticoagulant and saline bags 70 and 76 are also provided. The containers 48, 58, and 59 as well as any associated transfer containers 60 or 61 may each'be purposely imparted with a physical characteristic which is beneficial to its intended storage function in the manners heretofore described. The priming volume of saline can be vented from the system 88 in any manner heretofore described. However, in the system 88 shown in Fig. 7, venting conduit 69 is utilized. In Fig. 7, the needles 4.2 and 52 are each integrally connected to the associated branch means 40 and 50. Each is normally sealed from communication with the atmosphere by a needle cover 54, which is removed at time of venipuncture. Alternately, a needle adaptor as heretofore described ca n be used. Unlike the heretofore described systems 10 and 11, one or, as desired, some of the collection containers 48, 58, and 59, the transfer containers 60a and b or 61a, as well as one or both of the saline and anticoagulant bags 70 and 76 constitute entities which are normally separate from the rest of the system 88. In this embodiment, each of the separated containers 48, 58, 59, 60, 61, 70, and 76 is preferably carried in a tear-away protective overwrap 90. The overwrap 90 associated with the saline and anticoagulant bags 70 and 76 also preferably serves as a vapor barrier to prevent evaporation of anticoagulant or saline from the bags. The system 88 further includes means 92 for establishing a fluid path between each of the containers 48, 58, 59, 60, 61, 70, and 76 and the associated part of the system 88 in a manner which does not compromise the sterile closed integrity of any of the containers or of the formed system as a whole. As before explained, the formed system may be configured as system 10 (in Fig. 1) or as system 11 (in Fig. 3). More particularly, as is best shown in Figs. 8 through 11, the means 92 includes normally closed first and second connector means, respectively 94 and 96. The first connector means 94 communicates with each of the normally separate containers. The second connector means 96 communicates with each of the corresponding branch conduits through which fluid communication with the system 88 is made. In Figs. 8 through 11, only the connector means 94 and 96 used to interconnect the first collection container 48 and the branch conduit 46 are shown in detail. However, the connector means 94 and 96 associated with the remaining portions of the system 88 are identical to those shown in Figs. 8 through 11. As shown in Figs. 8 through 11, each connector means 94 and 96 includes means 98 for selectively mechanically coupling the associated pairs of first and second connector means 94 and 96 together with a portion 100 of each in facing contact (see Figs. 10 and 11). The facing portions 100 include means 102 operative for melting to form a fluid path through the joined pairs of the connector ^ means 94 and 96, thereby opening fluid communication between the associated container and the branch conduit, but only in response to exposure to an energy source efficient in itself to effectively sterilize the means 102 as they melt. This constitutes an active sterilization step which occurs simultaneously with the formation of the fluid path. Furthermore, during the act of melting, the means .102 are preferably operative for fusing together to form a hermetic seal about the periphery of the fluid path. The resulting connection is thus internally sterile and closed from communication with the atmosphere. The connector means 94 and 96 may be variously constructed and employ different means of operation. However, to meet the desired increased-yield objectives of the system 88, the connector means 94 and 96 each must meet certain operative requirements. More particularly, each connector means 94 and 96 must (1) normally close the associated portion of the system 88 from communication with the atmosphere; (2) be opened only in conjunction with an active sterilization step which serves to sterilize the regions adjacent to the fluid path as the fluid path is formed; and (3) be capable of hermetically sealing the fluid path at the time it is formed. It has been determined that the sterile connector generally described in Granzow et al U.S. Patents 4,157,723 and 4,265,280 meets all of the above criteria and, for this reason, such a connector is shown in the illustrated embodiment. More particularly, each connector means 94 and 96 includes a housing 104 which defines ' a hollow interior 106 (see Figs. 9 through 11) which communicates with its associated part of the system 88 as heretofore described. The heretofore described meltable means 102 associated with the facing portions 100 of the connector means 94 and 96 takes the form of meltable wall means, each of which normally seals or closes the associated interior 106 from communication with the atmosphere (see, in particular. Fig. 9). The housing 104 further ^ includes a tubular conduit portion 108 which communicates with the interior 106 and which serves to interconnect the first connector means 94 with a length of a tubing 110 integrall connected with the associated container (which is the container 48 in Figs. 8 through 11), as well as the second connector means 96 with the associated branch conduit (which is the conduit 46 in Figs. 8 through 11). While the connector means 94 and 96 may be variously attached to the end of the tubing 110 or with the branch conduits, in the illustrated embodiment, a hermetic, friction fit between the tubular conduit portion 108 is envisioned. An elastic band 112, such as made from a latex material, preferably encircles the outer periphery of the junction to assure a fluid tight, hermetic fit between the tubular portion 108 and the respective tubing 110 or branch conduits. As before stated, the tubing 110 associated with each of the first connector means 94 is integrally connected with each of the associated containers (see Fig. 8). To normally prevent fluid flow communication with the interior 106 of the connector means 94 in this arrangement, an inline valve member 114 (shown in phantom lines in Fig. 8) is preferably provided. Use of the valve member 114 is particularly preferred in conjunction with the initially fluid-filled bags 70 and 76. While the valve member 114 may be variously constructed, in the illustrated embodiment, it takes the form of an inline frangible valve member such aa one disclosed in Bayham et al, U.S. Patents No. 4,181,140 and 4,294,247. Alternately, the frangible valve member 114 can form an integral part of the connector housing, as is shown in Granzow et al, U.S. Patent 4,265,280. In the illustrated embodiment, the wall means 102 is fabricated from a radiant energy absorbing material. It is thus operative for melting in response to exposure to a source of radiant energy. Furthermore, the material from which the wall means 102 is constructed is purposefully preselected so that it melts only at temperatures which result in the rapid destruction of any bacterial contaminant on the surface of the material OMPI (i.e., over 200 β C). To permit the transmission of radiant energy through the housing 104 to the meltable wall means 102, the housing 104 is made of a material which does not absorb the particular type of radiant energy selected. In the preferred embodiment, the wall means 102 is made of a material fabricated from poly(4-methyl-l-pentene), which is sold under the trademark TPX by Mitsui Chemical Company. This material has a crystalline melting point of approximately 235 β C and is further discussed in Boggs et al U.S. Patent 4,325,417. The material of the wall means 102 includes a carbon filler so as to absorb infrared radiation. On the other hand, the housing 104 is made of a clear TPX material which is generally transparent to the passage of radiation. As can be best seen in Fig. 8, the connecting means 98 takes the form of mating bayonet-type coupling mechanisms, which serve to interlock the connector means 94 and 96 together with their radiant energy absorbing wall means 102 in facing contact (see, in particular. Fig. 10). When exposed to an incandescent quartz lamp 116 focused on the opaque, light-absorbing wall means 102, the radiant energy absorbing wall means 102 melt-and fuse together, as can be seen in Fig. 11. In the process of melting, the wall means 102 form a hermetically sealed opening 118 which establishes through the joined connector means 94 and 96 a fluid path which is at once sterile and hermetically closed to communication with the atmosphere. OMPI As the following Example demonstrates, the utilization of the illustrated connector means 94 and 96 assures a probability of non-sterility which exceeds 10- . EXAMPLE A methanol suspension of 1.5 x 10 Bacillus subtilis var niger (globiguii) spores per milliliter was prepared. This organism was chosen because of its high resistance to dry heat (see Angelotti, et al, "Influence of Spore Masture Content on the Dry Heat Resistance of Bacillus subtilis var niger'!, ' Appl. Microbiol., v 16 (5): 735-745, 1968). Eighty (80) uncoupled sterilized connector members (i.e., forty (40) pairs) identical to the connector means shown in Figs. 8 through 11 were inoculated with 0.01 milliliter of the B subtilis var niger (globiguii) suspension. This constituted exposure of the associated wall means 82 of each connector member to approximately one million (i.e., ιo ) spores of the organisms. Forty (40) of the inoculated uncoupled connectors were each attached to empty, sterile containers. The other forty (40) were each attached to containers containing a sterile microbiological growth medium (soybean casien digest (SCD) broth). These inoculated pairs of connector members will hereafter be referred to as the Test Connectors. Sixteen (16) additional uncoupled and sterilized connector members (i.e., eight (8) pairs) were inoculated only with methanol. Eight (8) of the connectors were each attached to empty, sterile containers, and eight (8) were each attached to sterile containers containing the SCD broth. These will hereafter be referred to as Negative Control Connectors. The Test Connectors were coupled together, forming forty (40) connections between the empty containers and the SCD broth containers. The noninoculated Negative Control Connectors were also coupled together, forming eight (8) connections between the empty containers and the SCD broth containers. Each connection was placed within the light-induced melting apparatus as heretofore described to fuse the membranes together and open a fluid path. The medium was then passed through the connections. Eight (8) additional and already fused connector members were inoculated as Positive Controls. Two of these connections were inoculated . with a theoretical challenge of 10 B_ subtilis var niger (globigii) spores per connection; two were 4 inoculated with a theoretical challenge of 10 spores per connection; two were inoculated with a 2 theoretical challenge of 10 spores per connection; and two were inoculated with a theoretical challenge of 10 spores per connection. Medium was the flushed through the fluid path of these Positive Control Connectors. All units were incubated at approximately 32° to 37"C for up to seven days. After incubation, all turbid broths were subcultured to SCD agar and incubated for 18 to 24 hours at approximately 32" to -£υR- * OMPI 37"C. The subcultures were examined for the presence of orange colonies, which is characteristic of the indicator organism. Upon examination of the forty (40) Test Connections, no turbid broths were observed. All eight (8) Negative Controls also remained negative during incubation. All eight (8) Positive Controls demonstrated growth of the indicator organism at all inoculum levels. The system 88 shown in Fig. 7 comprises a series of initially separate subassemblies which can be easily manufactured, packaged, sterilized, shipped, and stored. The system 88 gives the operator the flexibility to conveniently tailor the configuration of the system 88 to meet the collection objectives of the particular procedure. For example, beginning with the system 88 shown in Fig. 7, the operator can selectively configure a system 10 as shown in Fig. 1 (to carry out the method shown in Fig. 2) or a system 11 as shown in Fig. 3 (to carry out the method shown in Fig. 6). These significant benefits are achieved without a substantial probability of non-sterility to any of the formed systems 10 and 11. The systems 10, 11, and 88, each of which embodies the features of the invention, permit the maximum yields and the maximum storage times permissible for the collected components. None of the systems 10, 11, and 88 is dependent upon -SURE 4 OMPI relatively costly, large, and sophisticated centrifugal processing devices. Each system 10, 11, and 88 is suited for mobile collection procedures conducted away from a main processing facility. Various of the features of the invention are set forth in the following claims.

Claims: CLAIMS : 1. A blood component collection system comprising first means for establishing a flow of whole blood from a donor, second means for noncentrifugally separating the whole blood into essentially plasma and plasma-poor components, third means for collecting a volume of said separated plasma, fourth means for returning said plasma-poor components associated with said collected volume of separated plasma to the donor, and fifth means for collecting a volume of whole bloo . 2. A blood component collection system according to claim 1 wherein said fifth means includes means for collecting components of said whole blood separated i response to centrifugal separation. 3. A blood component collection system according to claim 1 or 2 wherein said second means includes microporous membrane means operative for filtering the plasma from the other components of whole blood. 4. A blood component collection system according to claim 3 wherein said microporous membrane means includes an inlet port for receiving whole blood, a first outlet port for removal of the plasma filtrate, and a second outlet port for removal of the plasma-poor components, wherein said first means includes inlet conduit means operative for communication with said inlet port, wherein said third means includes first container means communicating with said first outlet port for collecting the plasma filtrate, and wherein said fourth means includes outlet conduit means communicating with said second outlet port for returning the plasma-poor components to the donor. 5. A blood component collection system according to claim 4 wherein said fifth means includes second container means communicating with said inlet conduit means for diverting whole blood away from said microporous membrane means. 6. A blood component collection system according to claim 5 wherein said second container means is integrally attached to said inlet conduit means. 7. A blood component collection system according to claim 4 wherein said inlet conduit means, said outlet conduit means, and said first container means are all integrally attached to said associated port of said microporous membrane means. 8. A blood component collection system according to claim 7 wherein said fifth means includes second container means communicating with said inlet conduit means for diverting whole blood away from said microporous membrane means. 9. A blood component collection system according to claim 8 wherein said second container means is integrally attached to said inlet conduit means. 10. A blood component collection system comprising first means for establishing a flow of whole blood from a donor, second means for noncentrifugally separating the whole blood into essentially plasma and plasma-poor components, third means for collecting a volume of said separated plasma, means for collecting a volume of the plasma-poor components associated with said collected volume of separated plasma, and fourth means for returning the remainder of said plasma-poor components to the donor. 11. A blood component collection system according to claim 10 wherein said second means includes microporous membrane means operative for filtering the plasma from the other components of whole blood. 12. A whole component collection system according to claim 11 wherein said microporous membrane means includes an inlet port for receiving said flow of whole blood from the donor, a first outlet port for removal of the plasma, and a second outlet port for removal of said plasma-poor components, wherein said first means includes inlet conduit means operative for communication with said inlet port, wherein said third means includes first container means operative for communication with said first /outlet port, and wherein said fourth means includes outlet conduit means operative for communication with said second outlet port. 13. A blood component collection system according to claim 12 wherein said plasma-poor components collection means includes second container means operative for communication with said outlet conduit means• 14. A blood component collection system acccording to claim 13 wherein said second container means ' is integrally attached to said outlet conduit means. 15. A blood component collection system according to claim 12 wherein said inlet conduit means, said outlet conduit means, and said first container means are all integrally attached to said associated port of said microporous membrane means. -BCT X; O PI < 16. A blood component collection system according to claim 15 wherein said plasma-poor component collection means includes second container means operative for communication with said outlet conduit means. 17. A blood component collection system according to claim 16 wherein said second container means is integrally attached to said outlet conduit means. 18. A blood component collection system according to claim 1 or 10 and further including means for introducing saline into said system to prime said system. 19. A blood component collection system according to claim 18 and further including means for introducing anticoagulant solution into said system. 20. An increased yield blood collection system attachable to pump means and comprising microporous membrane means operative for filtering the plasma from the other components of whole blood, first and second collection containers, and conduit means for establishing a plurality of fluid paths which are closed from communication with the atmosphere and which includes first branch means attachable to the pump means and being operative in response to the pump means for introducing whole blood from the donor into said microporous membrane means, OMPI - 5ύ~ second branch means for transferring the plasma filtrate into said first container, third branch means for returning the plasma-poor components from said microporous membrane means to the donor, and fourth branch means communicating with said first branch means for diverting the whole blood away from said microporous membrane means and into said second collection container. 21. A system according to claim 20 and further including a source of sterile anticoagulant solution and a source of sterile saline solution, and wherein said conduit means includes fifth branch means for introducing the anticoagulant solution into said system, and sixth branch means for introducing the saline into said system. 22. A system according to claim 21 and further including a third collection container, and wherein said conduit means includes passage means for collecting, in said third collection container, saline introduced into said system. 23. A system according to claim 20-or 21 wherein at least a portion of each of said first and second collection containers includes a material which imparts a predetermined physical characteristic which is beneficial to long-term storage of the component therein transferred. 24. A system according to claim 20 or 21 wherein said first collection container is made of a material having relatively high low-temperature strength to facilitate freezing of the plasma therein transferred. 25. A system according to claim 24 wherein said first collection container includes a polyolefin material. 26. A system according to claim 20 or 21 wherein said second collection container is made of a material having the physical characteristic of suppressing hemolysis in red blood cells during storage-. 27. A system according to claim 26 wherein said material is polyvinyl chloride plasticized with di-2-ethylhexylphthlate. 28. A system according to claim 20 or 21 and further including at least one transfer container attached in fluid communication with said second collection container for receiving components of the whole blood separated therefrom by centrifugal forces. 29. A system according to claim 28 wherein one of said transfer containers is made of a material having the physical characteristic of improved gas transmission characteristics for improved platelet survival. 30. A system according to claim 29 wherein said material is a polyolefin material . CΓREΛ C ^ OMPI ° 31. A system according to claim 30 wherein said material is polyvinyl chloride plasticized with tri-2-ethylhexyl trimellitate. 32. A system according to claim 28 and further including a transfer container in fluid communication with said second collection container and including a red blood cell nutrient solution for transfer into said second collection container. 33. A system according to claim 20 or 21 wherein each of said branch means includes a length of flexible tubing integrally connected with its respective part of said system in the manner defined in the referenced claim. 34. A system according to claim 20 or 21 wherein at least one of said branch means includes first and second connector means normally dividing said one branch means into two separate portions, each of which is normally closed from communication with the atmosphere, each of said connector means including means for selectively mechanically coupling said first and second connector means together with a portion of each in facing contact, said facing portions including means operative for melting to form said fluid path through said facing portions only in response to exposure to an energy source sufficient to effectively sterilize said meltable means of said facing portions. 35. A system according to claim 34 wherein said meltable means of said facing portions are further operative for fusing -together about the periphery of said fluid path during melting to hermetically seal said fluid path. 36. A system according to claim 34 wherein each of said meltable means of said facing portions is made of a radiant energy absorbing material and melts in response to exposure to a source of radiant energy sufficient to effectively sterilize said meltable means. 37. A system according to claim 34 wherein said fluid path formed through said connector means presents a probability of non-sterility to said system of at least 10- . 38. A system according to claim 20 or 21 wherein said microporous membrane means includes a plurality of hollow fibers. 39. An increased yield blood collection system attachable to peristaltic pump means and comprising microporous membrane means operative for filtering the plasma from the other components of whole blood, first and second collection containers, and conduit means for establishing a plurality of fluid paths which are closed from communication with the atmosphere and which includes first branch means attachable to the pump means and being operative in response to the pump means for introducing whole blood from the donor into said microporous membrane means, second branch means for transferring the plasma filtrate into said first container, -b4- third branch means for returning the plasma-poor components from said microporous membrane means to the donor, and fourth branch means communicating with _ said third branch means for diverting the plasma-poor component away from the donor and into said second collection container. 40. A system according to claim 39 and further including a source of sterile anticoagulant solution and a source of sterile saline solution, and wherein said conduit means includes fifth branch means for introducing the anticoagulant solution into said system, and sixth branch means for introducing the saline into said system. 41. A system according„to claim 40 and further including a third collection container, and wherein said conduit means includes passage means for collecting saline in said third collection container. 42. A system according to claim 30 or 40 wherein at least a portion of each of said first and second collection containers includes a material which imparts a predetermined physical characteristic which is beneficial to long-term storage of the component therein transferred. 43. A system according to claim 39 or 40 wherein said first collection container is made of a material having relatively high low-temperature strength to facilitate freezing of the plasma therein transferred. f QMPI _. 44. A system according to claim 43 wherein said first collection container includes a polyolefin material. 45. A system according to claim 39 or 40 wherein the plasma-poor component includes red cells, and wherein said second collection container is made of a material having the physical characteristic of suppressing hemolysis in red blood cells during storage. 46. A system according to claim 45 wherein said material is polyvinyl chloride plasticized with di-2-ethylhexylρhthlate. 47. A system according to claim 39 or 40 wherein the plasma-poor component includes red cells, and wherein said second collection container includes a red blood cell nutrient solution. 48. A system according to claim 47 wherein said solution includes saline, adenine, and glucose. 49. A system according to claim 48 wherein said solution further includes mannitol. 50. A system according to claim 39'or 40 wherein each of said branch means includes a length of flexible tubing integrally connected with its respective part of said system in the manner defined in the referenced claim. 51. A system according to claim 39 or 40 wherein at least one of said branch means includes first and second connector means dividing said one branch means into two separate portions each of which is normally closed from communication with the atmosphere, each of said connector means including means for selectively mechanically coupling said first and second connector means together with a portion of each in facing contact, said facing portions including means operative for melting to form said fluid path through said facing portions only in response to exposure to an energy source sufficient to effectively sterilize said meltable means of said facing portions. 52. A system according to claim 51 wherein said meltable means of said facing portions are further operative for fusing together about the periphery of said fluid' path during melting to hermetically seal said fluid path. 53. A system according to claim 52 wherein each of said meltable means of said facing portions is made of a radiant energy absorbing material and melts in response to exposure to a source of radiant energy sufficient to effectively sterilize said meltable means. 54. A system according to claim 51 wherein said fluid path formed through said connector means presents a probability of non-sterility to said system of at least 10 . 55. A system according to claim 39 or 40 wherein said microporous membrane means includes a plurality of hollow fibers. 56. A blood component collection method comprising the steps of establishing a flow of whole blood from a donor, noncentrifugally separating the whole blood into essentially plasma and plasma-poor components, collecting a volume of the separated plasma, returning the plasma-poor components associated with the collected volume of separated plasma to the donor, and collecting a volume of whole blood. 57. A method according to claim 56 and further' including the steps of terminating the flow of whole blood from the donor, and further separating the collected volume of whole blood into other blood components. 58. A method according to claim 57 * wherein said step of separating the collected volume of whole blood includes separating the whole blood into red blood cells, platelets, and platelet—poor plasma. 59. A method according to claim 57 wherein said step of separating the collected volume of whole blood includes centrifugal separation. 60. A method according to claim 56 or 57 or 59 wherein said step of noncentrifugally separating the whole blood includes directing the flow of whole blood through a microporous membrane capable of separating the plasma from whole blood. 61. A method according to claim 56 or 57 or 59 wherein all of said steps are performed in a manner which does not expose the whole blood, the returned red blood cells, and the collected volumes of components to communication with the atmosphere. 62. A blood component collection method comprising the steps of establishing a flow of whole blood from a donor, noncentrifugally separating the whole blood into essentially plasma and plasma-poor components, .-' collecting a volume of the separated plasma, collecting a volume of the plasma-poor components associated with the collected volume of separated plasma to the donor, and returning the remainder of the plasma-poor components to the donor. 63. A method according to claim 62 wherein all of said steps are performed in a manner which does not expose the whole blood, the plasma, and the red cells to communication with the atmosphere.

Inventors: BLOOM PETER A, WILLIAMS RONALD A, BLOOM, PETER, A., WILLIAMS, RONALD, A.
Applicants: BAXTER TRAVENOL LAB, BAXTER TRAVENOL LABORATORIES, INC.
Application year: 1983
Main classification: A61M5
IPC codes: A61M1