Patent Application
20060226088
1. Field of the Invention
The present invention generally relates to blood processing systems for the automated collection of blood and separation of blood into its component parts. More particularly, the present invention relates to a centrifuge which can separate blood into two or more components and may be used in such blood processing systems.
2. Description of Related Art
The adult human body contains approximately 10 units (or approximately 5,000 mL) of whole blood consisting of both cellular and liquid portions. The cellular portion (about 45% by volume) comprises red blood cells, white blood cells and platelets. The liquid portion (about 55% by volume) is made up of plasma and soluble blood proteins. Each of these components can be directly transfused into patients and used in a wide variety of therapeutic applications. Blood component therapy is used in the treatment of blood disorders and conditions involving blood loss. Platelet therapy is also used to treat side effects of chemotherapy.
The world's current whole blood supply is estimated at 75 million units annually, with approximately 45 million whole blood units per year collected from donors at either mobile or fixed collection sites in North America, Europe, Japan and Australia. In the United States, collections have declined slightly during the 1990s to 13.1 million units in 2000, or 29% of the industrialized world's collections. Western Europe accounts for 44% of collections, Japan for 16%, and 11% are collected throughout the rest of the industrialized world. Seventy five percent of donated blood is collected in the United States in mobile settings (e.g., schools, offices, and community centers), with the remaining 25% collected at fixed blood center sites.
Collection of blood is currently done through two processes: the collection of whole blood using a 50 year-old manual process and the collection of blood components through apheresis. The manual process takes about 75 to 90 minutes per unit. The process begins with the manual whole blood collection from the donor, which takes about 6 to 15 minutes. Then the unit of whole blood and the test samples are transported to a fixed blood components laboratory where the whole blood is tested, centrifuged, expressed, labeled, leukoreduced, and placed into inventory. Further centrifugation and handling are required to produce platelets. In general, manual methods of collection and separation of blood are less efficient than automated methods such as apheresis. For example, with the manual method of platelet collection, four to six collections are required to produce a therapeutic dose.
In the United States, collection of certain components is frequently performed using apheresis. This automated process collects the donor blood, removes a desired component and returns the remainder to the donor. For example, plasmapheresis (plasma) and plateletpheresis (platelets) are automated apheresis procedures developed for the collection of specific components. Plasmapheresis is the automated removal of plasma from the body through the withdrawal of blood, its separation into plasma and red blood cells, and the reinfusion of the blood cells back into the body. Plateletpheresis is the automated removal of platelets from the body through the withdrawal of blood, its separation into red blood cells, plasma, and platelets, and the re-infusion of the red blood cells and plasma back into the body.
Blood supply is low. The blood shortage is so severe that in 2000, 7% of all elective surgies in the United States were delayed due to blood shortages and the American Red Cross (ARC) has reported blood inventories of less than one day of supply. Recently, the ARC and other blood organizations around the world imposed new restrictions on donor eligibility due to “Mad Cow” disease. This and other stringent donor screening programs is predicted to reduce the pool of available donors by 8%. Nonetheless, the adoption of these programs, along with the increasing prevalence of aggressive medical procedures requiring blood components, has resulted in widespread shortages of blood products.
Additionally, there is a shrinking donor base. Less than 3% of healthy North Americans regularly donate blood. The amount of eligible donors in the United States is expected to decline by approximately 8% from its level in 2002. The decline is anticipated for a variety of reasons, including more stringent donor screening to prevent contamination of the blood supply by various diseases such as Human Immunodeficiency Virus (HIV). The regulatory climate and issues affecting the donor population would also appear to favor an alternative approach to the current blood collection procedures including the standard manual collection and separation process.
Some entities have proposed the collection of two red cell units, an apheresis procedure, during one donor session as a partial solution to supply problems. One study has suggested that the adoption of double red cell collection could reduce the required donor pool by 6% and continue to meet existing blood supply requirements from a smaller donor pool. However, many blood banks currently do not have the capacity or apheresis equipment required to perform double red cell collection.
Furthermore, most of the blood banks in the United States currently operate at or close to breakeven position. Medicare and private insurers have limited reimbursements to hospitals for the purchase of blood units. Blood centers in the United States continue to experience the usual effects that have accompanied the growth of managed health care systems. At many blood centers, the fully loaded cost to collect and process one unit of red blood cells exceeds its selling price since hospitals have enforced price pressures on blood centers. Therefore, blood centers have focused their efforts on reducing expenses to achieve breakeven.
Blood products are biological products, and blood centers must therefore operate under the United States Food and Drug Administration's (FDA) regulations and established practices. Operating in compliance with regulations and practices when utilizing manual collection and processing procedures imposes an enormous quality assurance burden, under which more than one-half of blood centers in the United States still fail to operate. Additionally, blood bank organizations have experienced significant price erosion for their blood products and have had to absorb costly, unfunded new safety and quality control procedures and tests mandated by the FDA.
Moreover, new regulations are being implemented worldwide. For example, leukocytes have been identified to cause negative physiological reactions in a small percentage of blood transfusion recipients. As a result, the FDA's Blood Products Advisory Committee has formally recommended that the FDA mandate leukocyte reduction, and nations around the world, including Canada and the United Kingdom, have adopted leukocyte filtering. Leukocytes are currently removed from red cells and platelets by manual filtration processes which are time consuming and labor intensive.
Although manual processes for blood collection and separation have some serious disadvantages, they are generally far less expensive than the automated alternatives, such as apheresis, as they do not require specialized staff, expensive equipment and disposables. Additionally, the cumbersome (large and heavy) apheresis equipment does not lend itself to transportation to or use at mobile collection sites, where the majority of blood donations are collected. In part for the foregoing reasons, although apheresis is used extensively for certain procedures, such as platelet collection where up to sixty-five percent of platelets collected in the United States are collected using plateletpheresis, apheresis has not achieved high penetration or displaced the current manual processes for blood collection and separation where one or more red cell products are obtained. Similarly, double unit collection has not been implemented, in part, because current procedures for double unit collection are expensive and relatively complex. Finally, for some procedures, such as leukocyte filtering, there are few, if any, alternatives to a time consuming and expensive manual process.
The present invention relates to a blood collection and processing system that reduces direct collection and processing costs, automates and standardizes collection and processing procedures, automates data collection to minimize errors, performs multiple processes (including the collection of both single and double units of red blood cells), functions well in uses at remote sites on mobile blood drives as well as at fixed, blood center sites, and simultaneously collects, processes, and leukofilters blood. The present invention further relates to a centrifuge that can be incorporated into the aforementioned blood collection and processing system.
In one embodiment, the present invention relates to an automated blood collection and separation system that includes a console and a disposable set. The disposable set may include a manifold, a continuous-flow centrifuge (CFC) (including a CFC drive cup and a CFC disk that resides therein during system operation), and various components attached by tubing (e.g., solution bags, blood product bags, bacterial filters, leukofilters, donor blood collection tube with access needle). A manifold and CFC disk may be included in a cassette that mounts onto the front panel of the console. Alternatively, the manifold and CFC disk may be mounted into the console separately (i.e., without use of a cassette). The system may contain roller pump mechanisms and a CFC drive system to drive fluids through the system; a series of valves to control the flow of fluids through the system; and pressure sensors, ultrasonic sensors and optical sensors to monitor the flow of these fluids. System electronics, software, user interface components, a bar code reader and data acquisition components may also be included to control the system's operation and instruct the performance of various tasks.
The CFC disk may include an annular separation channel positioned at or near its periphery and/or a plasma shelf that lies within the annular separation channel. The CFC disk may further include a red cell outlet port located at or near the largest radius of the separation channel. Holes and/or locking ports for angular orientation of the CFC disk may also be included, as may various fluid lines from the CFC disk to the manifold. A variety of passages and tubes may additionally be included in the CFC disk to transport fluids and various blood products. Fluids and blood products may be transported into and out of the CFC disk by way of a seal assembly that includes a series of circumferential channels; one for each fluid or blood product (e.g., whole blood, red blood cells, plasma, storage solution).
In another aspect, the present invention is directed toward a variety of processes that implement blood processing and collection procedures, employing the CFC and the inventive blood collection and processing system. By way of example, in one embodiment, one unit of leukoreduced RBCs in storage solution and one unit of plasma are produced. In another embodiment, sufficient whole blood is collected from a donor to produce two units of leukoreduced RBCs in storage solution. In a further embodiment, sufficient whole blood is collected to produce one unit of leukoreduced RBCs in storage solution and two units of plasma. In another embodiment, sufficent whole blood from a donor is processed to collect a desired volume of plasma only. In another embodiment, whole blood is collected to produce one unit of leukoreduced RBCs in storage solution, plasma and buffy coat.
Other features and advantages of the invention will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate, by way of example, various features of embodiments of the invention.
FIGS. 32A-E depict the two-way rotary tubing pinch valve mechanism in accordance with an embodiment of the present invention.
FIGS. 33A-F depict the four-way rotary tubing pinch valve mechanism in accordance with an embodiment of the present invention.
The present invention relates to a blood collection and processing system, which includes, in one embodiment, a continuous-flow centrifuge (CFC). The CFC may, in turn, include a CFC drive cup and a CFC disk. The blood collection and processing system uses a console with electromechanical instrumentation that can perform an array of different processes to collect and/or process blood products. In connection with each of these different processes, the blood collection and processing system may use correspondingly different disposable sets that function interactively with the system's console. The disposable sets may be used to generate one or more blood products particular to a respective process. For example, blood products that result from each process may include: one or more units of leukoreduced packed red cells in storage (additive) solution; one or more units of plasma meeting the requirements of plasma fractionators and of fresh frozen plasma; and one or more units of buffy coat.
The console may include roller pump mechanisms to pump fluids through the disposable set and a CFC drive system to drive fluids to control CFC rotational speed; a series of valves to control the flow of fluids through the system; and pressure sensors, ultrasonic sensors and optical sensors to monitor the location and/or flow of these fluids. System electronics, software, user interface components, a bar code reader and/or data acquisition components may also be included to control the system's operation and instruct the performance of various tasks.
The CFC and other components of the disposable set can be used in connection with a variety of system functions, including simultaneous blood collection, anticoagulant addition, blood component separation and removal to blood product bags, red cell storage solution addition, and red cell leukofiltration. These processes may occur with continuous flow rates from the donor through the CFC disk and leukofilter to the blood component bags, as shown in
As shown in
As will be readily appreciated by one of skill in the art, one unit of whole blood usually has a volume of 450 mL or 500 mL in the United States. This whole blood volume does not include the anticoagulant volume added to whole blood during its collection.
Disposable Set
As illustratively depicted in
A donor access sub-assembly is illustrated in greater detail in
As illustrated in
As illustrated in
The manifold 210 (or the cassette) may be secured in place on the front panel 705 of the console by pins or similar mechanical elements that engage alignment holes or similar elements in the manifold 210 (or the cassette). The console door 702 is configured to close over the manifold 210 and to thereby secure the manifold 210 against the console front panel 705. In various embodiments of the present invention, particular elements of sensing components (e.g., pressure sensors, ultrasonic sensors) are included in the manifold 210, while other elements of these components are included in the console front panel 705.
Furthermore, the system may include a series of valves that control the flow of fluids through the tubing and other components in the disposable set. In one embodiment of the invention, the valves may be configured on the front panel 705 of the console, and the tubing may be brought into mechanical communication with the valves when the manifold 210 is mounted on the front panel 705 and the console door 702 is subsequently closed. Rotary pinch valves may be appropriate for use in connection with this embodiment of the invention, although other types of valves may be used as well. Alternatively, the valves (or particular elements thereof) may be configured on the manifold 210. Remaining elements of the valves may be included upon the front panel 705 of the console and configured so as to interact with the elements on the manifold 210 when the manifold 210 is mounted to the front panel 705. Alternatively, entire valve assemblies may be configured upon the manifold 210.
The selection of particular components, bags, and tubing and the configuration thereof in a disposable set depend upon the particular process to be implemented with the system of the invention. One configuration used in accordance with an embodiment of the invention is illustrated in
Manifold
As illustrated in
The manifold 210 supports tubing attached between it and other system components. In particular, the manifold 210 may support a series of tubing segments that are configured for interaction with other system components upon mounting of the manifold 210 to the console front panel 705 and the subsequent closing of the console door 702. In one embodiment of the present invention, as illustrated in
By way of example, selected tubing segments may be positioned in this manner opposite rotary valves on the console front panel 705. The rotary valves may impart sufficient pressure on the tubing segment so as to cut off the flow of fluid through the tubing segment, or, in an alternate position, the rotary valves may impart little or no pressure to the tubing segment; thereby allowing the free flow of fluid through the tubing segment. Alternatively, as seen in
Additionally, segments of selected tubes may be located opposite ultrasonic sensors upon the console front panel. As illustrated in
Additionally, at least one roller pump tubing section 231 (with at least one corresponding roller pump in the console front panel) may be included in the manifold 210 for fluid flow control. In the embodiment of the instant invention depicted in
As seen in
In an alternate embodiment of the invention, rigid plastic diaphragms may be used rather than elastomeric diaphragms (not shown). A rigid pressure-sensing plastic diaphragm may be integrally molded with the manifold and located opposite the console front panel. Such diaphragms may be in the range of from about 0.3 to about 1.0 inches in diameter and from about 0.020 to about 0.080 inches thick. The small deformation of the plastic diaphragm may be measured with a position sensor (e.g., a linear variable differential transformer).
The manifold fluid pumping components are depicted in
The pump tubing inside diameter may be selected for the flow rates of fluid desired, the degree of “pulsatility” of the fluid that can be allowed, and the speed range capability of the pump rotors. This inside diameter is controlled precisely in order to achieve accurate flow control. The pump rotor speeds are accurately controlled using feedback from encoders on the electrical motors that drive the pump rotors.
It will be appreciated by those skilled in the art that a variety of manifold designs may be used with the present invention. For instance, the manifold design may be simplified by the elimination of valves, the elimination of ultrasonic sensors, and/or by the reduction of the number of tubing connections.
In an alternate embodiment, the valve may include a four-way rotary tubing pinch valve mechanism, as illustrated in
In an alternate embodiment (FIGS. 32A-E), the valve design may include a two-way rotary tubing pinch valve mechanism. This design includes a single rotor 1210 with one roller 1290. This design permits rotating the rotor 1210 to three positions: both tubes 1280 open (
As seen in
Continuous-Flow Centrifuge
The CFC disk of the present invention may be used, among other things, to separate whole blood into its component parts. In this embodiment of the present invention, whole blood is pumped into the CFC disk. The blood may be anticoagulated prior to being pumped into the CFC disk, and the CFC disk may be rotating when the whole blood is introduced thereto at a sufficient speed to separate it.
A plasma outlet port 584 is positioned within a plasma shelf 581 in the CFC disk. The plasma outlet port 584 and red cell outlet port 544 may each be positioned about 180° opposite a whole blood inlet port 594; however, the whole blood inlet port 594 position may independently vary with respect to the red cell outlet port 544 and plasma outlet port 584. The plasma outlet port 584 is positioned at a radius of the separation channel 508 smaller than the radius of the red cell outlet port 544. Moreover, the configuration of the plasma shelf 581 with respect to the plasma outlet port 584 may vary in alternate embodiments. In one embodiment, as depicted in
The plasma shelf is configured somewhat like a funnel to collect plasma from a large area in the separation channel and direct it towards the plasma collection port with a flow-cross-section-area that decreases as flow moves toward the plasma collection port. The purpose of this “funnel” shape is to keep localized velocities for plasma low in and near the separation channel to allow any cells (red cells, white cells, or platelets) in the plasma to be separated by centrifugal forces. The plasma velocity component in the radially inward direction is intended to be less than the radially outward velocity of each cell under centrifugal forces. This causes cells to move to the RBC-plasma interface and not to be carried with plasma into the plasma product bag.
Plasma optical sensing pathway 531 and RBC interface optical sensing pathway 532 may be located within the separation channel 508.
During operation of the system to separate whole blood into its constituent parts, whole blood enters the separation channel 508 through the whole blood inlet port 594, and then separates; about half flows through the separation channel 508 in a clockwise direction and the remaining part flows in a counterclockwise direction. RBCs 541, plasma 580, and buffy coat layer 571 lie within the separation channel 508. The plasma shelf 581 aids in bringing plasma to the plasma outlet port 584. The plasma shelf 581 provides a large cross-sectional area for plasma 580 flow to the plasma outlet port 584, permitting cells to sediment out of this plasma 580 toward the red cell interface 542 (
Storage solution or saline solution may be added to packed RBCs 541 after they pass through the RBC outlet port 544 and before the red cells enter the face seal of the CFC disk. The solution is metered into the flowing packed RBCs 541 at an approximately constant ratio. This ratio may be controlled by a microprocessor and software via the solution pump and the red cell pump. The addition of storage solution decreases the packed red cell hematocrit from about 90% to about 60% and significantly reduces viscosity. This permits RBCs to be removed from the CFC disk with lower pressure drops and lower red cell damage. As depicted in
A seal assembly 600 and corresponding tubing provide fluid communication between the CFC disk and the manifold. The seal assembly 600 is positioned at the axial center of the CFC disk. The tubing includes the plasma from CFC disk to manifold line 257, the RBC from CFC disk to manifold line 260, the whole blood from manifold to CFC disk line 253, and the solution from manifold to CFC disk line 259. A red blood cell storage or additive solution, saline or another solution may be added to packed RBCs separated in the CFC disk, with the solution passing through a circumferential channel in the seal assembly 600. The radial location of the mixing location of solution and RBCs may be selected to maintain a low pressure in the solution channel in the range of about −200 mmHg to about +200 mmHg, preferably about +50 mmHg, in order to prevent forces that might separate the face seal elements or otherwise create a fluid leak into or out of the solution channel in the face seal. The mixing of solution and RBCs will reduce hematocrit and viscosity of the RBCs when they flow through the face seal, thereby reducing pressure drop and red cell damage caused by the face seal.
As depicted in
A series of channels are formed by the stationary seal 606 and rotating seal 604: a center channel 656 to transport red blood cells (after solution addition) from the CFC disk to the manifold, a first circumferential channel 654 to transport whole blood from the manifold to the CFC disk, a second circumferential channel 658 to transport plasma from the CFC disk to the manifold, and a third circumferential channel 652 to transport storage solution or saline solution from the manifold to the CFC disk. Center, first, second and third couplings in communication with the corresponding channels in the seal assembly 600 connect the respective channels with appropriate tubing to provide fluid communication between the channels and the manifold. These couplings are located in the distributor 619.
The radial location of the connector 586 where solution is added to RBCs is critical because it determines the pressure of the solution in its circumferential groove 652 in the face seal. This is the outermost groove in the face seal, separated from ambient air by the outer narrow face seal land. This land provides a fluid-tight seal before, during, and after disposable set use. It prevents non-sterile ambient air from entering the seal and contaminating the solution with bacteria, and it prevents the solution from leaking out of the seal. It is desired to maintain a slightly positive pressure of solution in its circumferential groove 652 in the seal. This positive pressure discourages ambient air from leaking into the seal as may be possible with a negative pressure. A low positive pressure of about +10 to +60 mmHg gauge also prevents pressure forces that could separate the seal faces and cause leaks or contamination, as may be possible with a higher pressure. The radial location of the connector where the solution is added to RBCs is directly related to the pressure because of the centrifugal field effects on pressure; the larger the radius, the higher the pressure. This optimal radial location providing the desired pressure is in the range of 0.3 inch to 1.0 inch from (radially less than) the radial location of the opening of the RBC duct in the separation channel.
The solution also provides the function of cooling the face seal elements and may also provide some lubrication or wetting to reduce rotating friction between these contacting seal elements.
As depicted in
When assembled into the drive cup on the front panel of the console, the CFC disk will first engage and slip easily into its drive mechanism. Locking ports 512 may be used for angular orientation of the CFC disk in the drive cup. The console door closure is used to engage the CFC disk such that certain components thereof can rotate freely and are positioned and supported correctly and safely within the centrifuge drive mechanism. The CFC disk seal assembly depicted in
The tongue 683 protruding from stationary seal housing 602 enters and engages with slot 684 in console door engagement piece 680. This engagement occurs when the door is closed and prevents the stationary seal housing 602 from rotating.
The stationary seal housing 602 is free to move in a direction along the spin axis (centered along the central RBC port in the seal). Its axial travel is limited in one direction by lip 681 on seal housing 602 contacting seal or mounting ring seat 682 on outer rotating housing 601. Travel is limited in the opposite direction by lip 681 on contacting surface 689. When the lip 681 is between seat 682 and contacting surface 689 it does not contact any rotating parts and the disk 517 with its separation channel is free to rotate with seal housing 602 and lip 681 held stationary.
As seen in
Seal element 606 is bonded or attached to distributor 619. Distributor 619 is held stationary by engagement with stationary seal housing 602. One or more ribs 685 run axially inside seal housing 602 and engage slots 686 in distributor 619. The rib-in-slot engagement permits seal housing 602 to move axially while springs 621 prevent axial movement of distributor 619 and keep stationary seal element 606 forcibly pressed against rotating seal element 604.
When the centrifuge disk is not inside the console with the door closed, the springs 621 force lip 681 of seal housing 602 against seat 682 of outer rotating housing 601. One or more radial ribs or projections 687 on lip 681 engage open slots 688 on outer rotating housing 601. This engagement not only prevents relative rotation between these parts but also orients tongue 683 on outer rotating housing 601 so that it will automatically and properly engage slot 684 in engagement piece 680 when the door is closed, with no manual adjustment required. The console clocks the drive cup to a fixed angular orientation to achieve this alignment and permit tongue in slot engagement. When the door is closed, the axial movement of lip 681 is more than sufficient to disengage rib 687 from slot 688.
Console
The console may include: a console body with an enclosure, including a vertical front panel; a door hinged horizontally along its bottom edge and facing the console body front panel; roller tracks for the pumps are located in the door; four roller pumps with electric drive motors and drive mechanisms mounted in the console; valve actuators, pressure transducers, and ultrasonic sensors mounted on the front panel (these interact with sensing and actuation components in the disposable cassette and/or manifold inserted between the front panel and door); a centrifuge drive system that drives the disposable centrifuge disk with a drive cup that supports the outer wall of the disk; microprocessor-based control electronics and electronics that interface with all electromechanical components and the user interface components; software that implements, controls, monitors, and documents the processes carried out by the system of the invention; a user interface that provides user control of the process to a limited and well-defined extent, provides monitoring and warning functions for the user, and provides a bar-code wand reader for rapid and efficient data collection; a data port that permits process and system data to be transmitted to a printer, a portable memory, or the blood bank computer; and A.C. power as well as battery power operating capabilities.
The electronics located in the console may utilize a microprocessor based controller with a separate microprocessor for safety to meet medical device electronic system requirements. The electronic PC boards provide electronic interfaces to various motors, actuators, and sensors.
In one embodiment of the instant invention (not shown), the bag hangers may be configured with individual scales that provide a measurement of the weight of each bag hanging therefrom. In this manner, the system can compute the fluid volume of any individual bag, based on its weight. This feature may be used, for example, to provide an indication of the bag fluid volume during operation of the system, to aid in function of an “off” feature when the bag reaches a desirable volume, or the like.
The console front panel 705 includes a centrifuge drive cup 1500 that rotates the disposable CFC disk, and orientation pins 1502 that hang the disposable cassette onto the console front panel 705. The CFC drive cup may also include pins 1505 for orientation and locking of the CFC disk. The CFC drive cup 1500 is surrounded by a centrifuge bucket 1510 which is attached to the console front panel 705.
The pump rotors 810 mounted in the console body 715 are visible on the console front panel 705. A leak collection gutter 731, located near the bottom region of the console front panel 705, directs leaks to the leak reservoir 732. A hinge 704 may attach the console door to the console body along the horizontal bottom of the console front panel 705.
A bar code reader may be provided in order to take bar code data (e.g., identifiers, lot numbers, expiration dates) from bags, the user, the donor, and other sources. For example, the cassette may have a bar code read by the console bar code scanner window 720. This provides identification to the console of the process to be implemented. It may also provide cassette calibration (e.g., pump tubing, valves), cassette lot number, and expiration date. The console may provide date, time, and process and blood product information. Process and system data, process parameters, warnings, failures and a process validation may be provided to a central blood bank computer.
Components of the roller pump mechanism are depicted in
As illustrated in
As depicted in
Each of the pump rotors 810 has eight pump rollers 818 equally spaced on its periphery. The small spacing between pump rollers 818 and the relatively large rotor diameter achieve a short roller pump track 851 length and short pump tubing 840 segment. This pump tubing 840 segment is deformed into a short, shallow arc by the pump rotors 810 and roller pump track 851. Short pump tubing 840 segments are advantageous in order to minimize overall manifold 210 size and cost and allow straight pump tubing 840 to be engaged easily and deformed into a short, shallow arc. This permits easy loading of the manifold 210 onto the console front panel 705, with pump tubing 840 located between the pump rotors 810 and pump track 851.
When the console door 702 is closed, the pump rotors 810 compress and occlude a segment of pump tubing 231 against the roller pump track 851. The pump rotors 810, supported by concentric drive shafts 830, are driven by belt drives and pulley components 820 which are powered by a total of four D.C. motors 806. The solenoid valve actuator and pressure sensor components 900 which are mounted in the console front panel 705 are located between the pump rotors 810 and the concentric drive shafts 830.
The donation (whole blood from the donor) may be selected at 500 ml, the preferred value, or pre-selected by the blood center or user at some other value from about 400 to 500 ml. The purpose of completely filling the separation channel with packed RBCs at a hematocrit of about 90%, plus buffy coat, is to remove all plasma from this channel to the plasma product bag, and maximize the volume of this plasma product.
As seen in
The plasma path length for optical detection is made quite thin (about 4 mm) in both the separation channel 508 and the plasma shelf 581 optical sensing regions. This is intended to minimize the effect of plasma transmissibility, which is highly variable from donor to donor, on the accuracy of RBC interface location detection. It is desired to have a quite accurate and consistent, repeatable analog output signal from these detectors that can measure with precision the location of this RBC-plasma interface. Additionally, the plasma light source looks through a thin (about 2 mm) wall of plastic at the plasma shelf 581, illuminating a plasma layer about 4 mm thick axially.
The following examples illustrate certain processes that may be implemented with the system of the present invention.
Before blood donation begins, a disposable set is removed from its sterile package and hung on the console. Solution bags (anticoagulant, red blood cell additive solution, and saline) are attached to the console. Solution bags could be pre-attached but are assumed in these processes to be attached at disposable set-up. The solution bags may have Luer-lock or spike attachments. Bacterial (0.2 micron) filters are used in the flow paths from these bags to maintain sterility. The bags are hung in designated locations on the console. The console calibrations and system software status are performed automatically before blood donation begins. Data collection is performed manually by the user with a bar code wand reader and automatically via the console.
The processes of the present invention are automatic. The automatic process begins after the phlebotomist (user) places the access needle in the donor's vein and after the non-anticoagulated blood samples are taken into a pouch or diverter bag providing a sample site near the needle. Then the system start button is pressed or the system is activated by another way to begin the automatic process.
Each process begins with a filling or priming of the CFC disposable disk by whole blood with anticoagulant added. This CFC disk has an annular separation channel that has a volume of about 90 mL. This volume is initially filled with sterile air. This air is displaced by the whole blood entering the separation channel. The air is removed to a bag for use later in purging or removing blood components from the CFC disk and disposable set.
As blood flows from the donor in tubing that connects the donor to the disposable set, anticoagulant is metered into the whole blood. The ratio of anticoagulant flow to donor blood flow is fixed at about 1 to 7, the ratio currently used in manual blood collections. However, this ratio may be optimized at somewhere between 1 to 7 and 1 to 14 for processes that return blood components to the donor.
When the CFC disk separation channel becomes filled with donor blood, steady state operation begins. Blood flows from the donor into the CFC at a more or less fixed flow rate; separation of whole blood into packed red cells, plasma, and a buffy coat occurs continuously, and red cells and plasma are removed at more or less fixed flow rates from the CFC.
An interface between the red cell layer and the plasma forms near the center of the CFC separation channel. An optical detector measures the radial location of this interface. This interface position is controlled to be maintained at or near the center of the separation channel throughout most of steady-state continuous-flow operation, and then the interface is moved radially inward to displace (remove) all plasma to the plasma product bag. This is achieved primarily by changing the RBC pump flow rate to remove greater or fewer RBCs from the separation channel, using standard feedback control methods.
When the donor hematocrit is above 40%, the RBC flow rate will increase appreciably at a fixed donor blood flow rate. In order to maintain a maximum effective and safe flow rate through the leukofilter, the RBC flow rate has a maximum value. When it reaches this maximum flow rate, then the donor flow is increased or decreased to maintain the red cell-plasma interface in its desired location. This will increase the donation time for that small percentage of donors who have hematocrits substantially above 40% and who are donating a fixed pre-set volume of whole blood. This will not increase donation time for donors who are donating a fixed volume of RBCs.
The buffy coat consists of white cells (including leukocytes) and platelets. It is less dense than red cells and more dense than plasma. Consequently the buffy coat forms a radially narrow white region at or near the radial center of the separation channel, at the red cell-plasma interface. The packed red cells are at the outermost part of the annular channel and against the outer wall of the channel. The plasma is at the innermost part of the channel and against the inner wall. The buffy coat collects throughout the steady state continuous-flow separation process at this red cell-plasma interface.
During the purge or component removal part of the process the buffy coat is either removed to another bag, left in the CFC disk, or left in tubing and other components in the disposable set. It is not pumped into or through the leukofilter with the packed red cells. In certain embodiments of the invention, the buffy coat in the air bag or another bag at the end of the separation and donation step is removed. This removal of buffy coat from the whole blood decreases the amount of leukocytes that must be removed by the leukofilter. The desired leukocyte count in the packed red cells after leukofiltration is about ×106. Platelet reduction by buffy coat removal is also beneficial. Platelets can form a layer on the leukocyte filter or otherwise plug it, increasing leukofilter pressure drop with resultant hemolysis, and forcing lower flow rates to avoid hemolysis. Buffy coat removal therefore significantly aids leukoreduction and permits higher flow rates with a smaller, lower-cost filter having less filter volume and consequently less red cell loss in the filter.
The packed red cells are pumped out of the CFC disk, through a leukofilter, and into a RBC product bag. A storage or additive solution is metered into the packed RBC flow stream at a rate that achieves the desired concentration or hematocrit of RBCs. This occurs before the RBC pump, within the CFC disk.
The RBC pump flow rate is controlled so that the flow through the leukofilter is maintained at or near an optimum. This optimum is a flow high enough that it does not increase donation time or process time appreciably, and low enough to prevent high leukofilter inlet pressures and resultant hemolysis.
At the end of the donation, when the selected volume of whole blood or RBCs, and/or plasma has been taken from the donor, the needle is removed from the donor. As the end of the donation approaches, the CFC disk separation channel may be almost completely full of packed red cells. When the donation ends, the blood in the donor line may be pumped out by anticoagulant flow. Then the buffy coat may be pumped into the air bag by reverse flow of the RBC pump. The packed red cells filling the separation channel are then pumped through the leukofilter into the RBC product bag, with the addition of storage solution to the RBCs as before.
Storage solution is pumped into the leukofilter to purge or remove RBCs trapped in the leukofilter and pump them into the RBC product bag, to minimize red cells lost in the disposable set and maximize overall red cell recovery. The volume of storage solution used for this purpose is limited by the maximum amount of storage solution that can be added to a unit of red cells, and by the possible liberation of leukocytes from the leukofilter which are then carried into the RBC product bag.
The red cell product has been separated from one or more units of whole blood, has been packed to a hematocrit of about 90%, has had storage solution added, and has been leukofiltered. It has been placed in one or two product bags at the end of the process. Plasma is expelled to the plasma bag by the differential flow rates of the whole blood pump and the packed RBC pump, as in steady state operation. The end of the process occurs when the leukofilter purge is completed. The product bags are now sealed off and removed from the set. The disposable set is then removed from the console and the set is prepared for disposal as a biohazard material.
In one embodiment of the invention, one unit of whole blood is collected from a donor to produce one unit of leukoreduced RBCs in storage solution and plasma. This embodiment of the invention is depicted in
As seen in the schematic depicted in
The anticoagulant bag 138 and storage solution bag 72 are attached by connectors 71 and 72 such as Luer-lock or spike attachments to the blood processing system. Bacterial filters 141 and 142 are used in the anticoagulant bag 138 flow path and storage solution bag 72 flow path to ensure the maintenance of sterility. During this process, the anticoagulant is pumped by way of an anticoagulant pump 162 to the donor line to purge air and ensure correct anticoagulation of the first amount of blood pumped from the donor. The donor venous needle access is made by the phlebotomist in standard fashion. Removal of the manual clamp 32 near the donor needle 110 purges anticoagulant from the line near the sample pouch 22. Then the manual clamp 31 on the sample pouch 22 is opened and blood fills the sample pouch 22. The sample pouch 22 is then clamped by manual clamp 31. Blood samples can subsequently be taken from sample pouch 22.
Blood is pumped from the donor at rates determined by donor venous pressure. Anticoagulant is pumped into the blood downstream of the donor needle 110 and upstream of a blood sample site 21. The ratio of anticoagulant flow to blood flow is fixed.
As blood is pumped initially from the donor it begins to fill (prime) the disk separation channel of the CFC 500. The CFC 500 disk is rotated at a moderate speed to ensure all air removal and that blood completely fills the disk channel and passages. Air is displaced into an air bag 128 for later use. When the disk separation channel of the CFC 500 is filled with whole blood, its speed is increased and steady-state continuous-flow separation into concentrated red cells and plasma begins. Red cells are pumped out at a rate determined by the whole blood flow rate and by the optically-measured red cell interface location. The red cell flow rate is adjusted to keep the red cell interface in the desired, optimal location in the separation channel of the CFC 500. Plasma flows out into the plasma bag 132.
When red cells flow out of the CFC 500 disk they are mixed with a storage or additive solution prior to entering the face seal to reduce viscosity and red cell damage. This storage solution is pumped by a solution pump 163 at a flow rate that achieves the fixed, desired ratio of additive solution flow to red cell flow. The combined flow goes through a red cell leukofilter 150 into the RBC bag 131.
This continuous-flow process continues until the end of the donation. The user has selected a whole blood or RBC volume to be collected from the donor and the calibrated whole blood pump 161 stops when this volume has been collected. The donor blood line is purged with anticoagulant to maximize red cell and plasma recovery. Red cells fill the entire separation channel at this point. All plasma has been removed to the plasma bag 132. Then red cells are pumped back into the disk by the RBC pump 164 to displace the buffy coat and anticoagulant into the air bag 128. The donor line at the needle is then clamped off and the needle is removed from the donor.
The CFC 500 disk speed is decreased and air flows into the rotor from air bag 128, as RBCs are pumped out of the rotor, through the leukofilter 150 (after storage solution addition) and into the RBC bag 131. Storage solution is pumped through the red cell lines and leukofilter 150 to purge red cells and maximize red cell recovery. Air is then removed from the RBC bag 131 and plasma bag 132. An air pouch 25 or small flexible bag at the end of the line segment 41 attached to the RBC bag 131 may be used to collect air from the RBC bag 131 and fill line segment 41 with RBCs from the RBC bag 131. The RBC bag 131 and plasma bag 132 are then heat-sealed off and the disposable set is removed and disposed of.
A more detailed description of the user implementation of the process depicted in
The system then performs a disposable and system self check. During this step, the system determines the type of disposable set installed based on its bar code, checks to see whether the disposable set is installed correctly, checks the lines clamped, checks the disposable set's integrity (e.g., leak check), checks internal system points, moves air if required, and zeros transducers. A protocol confirmation is achieved when the user interface display indicates “Protocol disposable may process is . . . ” The user confirms that the disposable set recognized agrees with protocol to be performed and presses the continue button for “yes.”
Then the disposable set is prepared for blood donation. The user interface display reads “Attach solutions to set per IFU.” The user hangs the anticoagulant bag 138 and storage solution bag 122 by spike or luer attachments and presses the continue button. The anticoagulant line to sample pouch 22 is primed. Confirmation with the anticoagulant pump 162 time/rotations and ultrasonic air sensor US2 and flow is established. Back pump reverses the system to reduce the amount of anticoagulant in the tubing. The user then prepares the donor.
The storage solution line to CFC 500 is primed concurrently with the anticoagulant priming. Confirmation with solution pump 163 and ultrasonic air sensor US3 and flow is established. Confirmation that the system is ready for the donor is then established and the user interface displays “ready for a donor.” The user then further prepares the donor and phlebotimizes, unclamps the donor needle 110 line and sample pouch 22 line and draws volume of blood into sample bag 22 along with air in line. Afterward, the user clamps/seals off the sample pouch 22, removes it from the disposable set, and takes VACUTAINER samples from the sample pouch 22. The user then presses the continue button to start the drawing of blood.
The blood donation begins, and the blood primes the system. Blood is drawn at a maximum of 65 ml/minute from the donor filling line to CFC 500 with anticoagulant being metered. The system then pauses to check zero at donor line pressure transducer No. 1. The CFC 500 is primed during which whole blood fills the CFC 500 while spinning and developing separation interface. At this point, all air is purged to air bag 128 and RBC and white blood ports are covered with blood. Priming of the CFC 500 continues as whole blood fills the CFC 500, rotations per minute (“RPM”) increases (from about 1000 RPMs to 4000 RPMs) until the plasma optical sensor sees liquid, a little RBCs are pulled to clear seal, and all air is purged to air bag 128. At the completion of the priming of the CFC 500, the CFC is rotating at its operable speed which is about 4000 to 4500 RPMs, the plasma port is clear, and the valve to plasma bag 132 is switched.
The leukofilter 150 is primed at a maximum of about 25 ml/min for 35 ml volume. During this stage, the leukofilter 150 is primed with blood, storage solution is metered to RBC flow, plasma is drawn, and a RBC bed is built in CFC 500 during the leukofilter 150 priming. During separation, blood is drawn at rates acceptable to donor pressure and leukofilter 150 flow of about 45 ml/min maximum; this is the steady state part of the run. A RBC bed is built in anticipation of the end of draw volume, purging out plasma. The CFC 500 rate increases to about 5000 RPM to pack the RBC bed and minimize plasma contamination. The RBC bed is built until the buffy coat is in the plasma port. Switch valves V1 and V2 continue to build the RBC bed, pushing the buffy coat and some RBC into the plasma line and air bag 128.
The donation ends when the donor draw volume is reached. Blood pump 161 and anticoagulant pump 162 ratio is adjusted to purge donor line of RBCs to CFC 500 and the line to air bag 128 is open at this step of the process.
The CFC 500 rotation comes to a stop and homes to RBC port at the six o'clock position. The user attends to the donor, and the donor is removed from the system when the user interface display indicates “clamp needle line and remove donor.” Subsequently, the user clamps the donor needle 110 line, removes the donor needle 110, applies a needle protector, and applies a sterile gauze onto the donor.
RBCs are purged from the CFC 500. The drawing of the RBC from the CFC 500 allows air to return from the air bag 128 (ratio storage solution) by a timed drain or optical detector in disk. At this stage, the user attends to the donor. The leukofilter 150 is purged by pumping 30 ml of storage solution into the leukofilter 150 to purge out remaining RBCs. Airing out the plasma occurs when the user interface displays “Invert Plasma Product Bag and Purge Air.” At this point, the user inverts the plasma bag 132, presses and holds the remove air button, squeezes plasma bag 132 until air is removed, seals tube to bag and presses continue.
Airing out RBCs occurs when the user interface displays “Invert RBC Product Bag, mix and purge air.” The user then inverts the RBC bag 131 and mixes it, presses and holds the remove air button until air reaches the mark in the tube line segment 41, seals tube at mark, and presses continue.
The process is complete when the user interface displays “process complete, Please remove set.” The user then opens the console door, removes the disposable set, removes the anticoagulant bag 138, storage solution bag 122, RBC bag 131, plasma bag 132, and air bag 128, and disposes the disposable set as appropriate. At this point, the system detects no barcode and is ready to accept a new disposable set as indicated by the user interface display which reads “Ready to Accept Disposable.”
In another embodiment of the invention, sufficient whole blood is collected from a donor to produce two units of leukoreduced RBCs in storage solution. This embodiment is depicted in
The 2RBC Process produces two products (bags) of leukoreduced AS-5 RBCs of 180, 200, and 210 ml maximum target absolute RBC volume for each unit. All plasma is returned to the donor.
The AC, SS, and saline lines are primed. A total of three to four draws and return cycles are used for each donor to accumulate the target RBC volumes and return all plasma.
In the first donor draw the disk fills with anticoagulated donor blood, displacing air in the disk and donor line to the plasma holding bag. The disk, rotating at low speeds initially and then about 4250 RPM, separates the blood into packed red cells and plasma. As whole blood enters the disk, the RBC-plasma interface is developed and moves radially inward. The RBC pump is initially off until the interface reaches about 50 ml of packed RBCs in the disk. Then the RBC pump speed is controlled to maintain this interface at somewhere between 50 ml to 95 ml of packed RBCs. The maximum disk volume is about 95 ml. The RBC pump pumps RBCs, after storage solution addition, through the leukofilter into the RBC product bag. When the donor blood volume specified for this first draw cycle is reached, then the donor draw and RBC pump flow stop. Plasma flows to the plasma holding bag throughout this first draw.
The first return of plasma to the donor then begins, with all plasma in the plasma bag pumped out of this bag by the whole blood pump to the donor. One of the rotary valves (RV1) opens a tubing connection between the plasma bag and a Tee located between the disk and the whole blood pump. This valve also closes the tubing connection between the Tee and the disk to prevent pumping RBCs out of the disk. During this return flow, some RBCs may be slowly pumped out of the disk through the leukofilter to the RBC product bag. Saline is added to plasma in the return to achieve a near-zero intravascular volume change at the end of this and each draw and return cycle.
The second donor draw step controls the RBC interface to between 50 ml to 95 ml of packed RBC volume at the end of this second draw. RBCs are pumped through the leukofilter to the RBC product bag during this step. Plasma flows to the plasma holding bag. This step ends when a specified volume of donor blood has been collected during this draw. The second return step is similar to the first. A third draw and return cycle, if not the final cycle, is similar to the second cycle.
The final (third or fourth) draw step ends when RBCs pumped to the RBC product bags reach their target volume as measured by RBC product bag scales. Then the final return to the donor pumps all of the contents of the disk and plasma bag to the donor via the whole blood inlet port. The plasma bag contents may be returned first to the donor. This return may include the accumulated buffy coat or, the buffy coat may remain in the disk, or the buffy coat may be pumped to the leukofilter. Air from the plasma bag backfills the disk. Saline is added to the returning plasma and any returning RBCs. The disk and donor line are emptied of plasma and RBCs.
The donor is now disconnected from the M2000 system. The process ends by purging the leukofilter with storage solution to remove as many RBCs as possible. Alternatively, the disk may be almost fully emptied after the donor is disconnected. The remaining RBCs and buffy coat stay in the disk or are pumped to the leukofilter. Then the leukofilter is purged.
The RBCP Process produces one unit of leukoreduced RBCs in additive solution of 180 to 210 ml maximum target absolute RBC volume. This process also produces about 450 ml to 550 ml maximum target plasma volume. No plasma is returned to the donor; only RBCs are returned to the donor.
The schematic for this process is depicted in
The AC, SS, and saline lines are primed. A total of perhaps three to eight cycles of donor draw and return steps are needed to obtain these blood products. The number of cycles depends upon donor hematocrit, weight, and extracorporeal and intravascular volume considerations.
In the first donor draw the disk fills with anticoagulated donor blood, displacing air in the disk and donor line to the air bag. The disk develops a packed RBC-plasma interface that gradually moves to fill the disk almost completely with packed RBCs (perhaps 70 to 90 ml of RBCs). Plasma flows to the plasma product bag. Some RBCs are pumped to the RBC product bag after adding SS and passing through a leukofilter.
In the first return step all RBCs in the disk are returned to the donor via the whole blood pump and the disk whole blood inlet port. Saline is metered into these red cells by the solutions pump. Plasma flows back into the disk as packed RBCs are removed. The disk continues to spin during all return steps to maintain plasma-red cell separation and achieve a largely cell-free plasma.
These draw and return steps are repeated until both absolute RBC target volume and plasma target volume are achieved, as determined by scales separately weighting the two product bags.
The disk is emptied after the last donor draw step and after the plasma target volume has been reached by pumping all packed RBCs in the disk into the RBC product bag. Air from the air bag backfills the disk. Then the leukofilter is purged with storage solution to improve RBC recovery.
The donor is removed from this system immediately after the final donor draw step.
The Plasma Only Process produces about 450 ml to 800 ml maximum target plasma volume. No plasma is returned to the donor; only RBCs are returned to the donor.
The schematic for this process is depicted in
The AC, SS, and saline lines are primed. A total of perhaps three to eight cycles of donor draw and return steps are needed to obtain these blood products. The number of cycles depends upon donor hematocrit, weight, and extracorporeal and intravascular volume considerations.
In the first donor draw the disk fills with anticoagulated donor blood, displacing air in the disk and donor line to the air bag. The disk develops a packed RBC-plasma interface that gradually moves to fill the disk almost completely with packed RBCs (perhaps 70 to 90 ml of RBCs). Plasma flows to the plasma product bag. Some RBCs are pumped to the RBC product bag after adding SS and passing through a leukofilter.
In the first return step all RBCs in the disk are returned to the donor via the whole blood pump and the disk whole blood inlet port. Saline is metered into these red cells by the solutions pump. Plasma flows back into the disk as packed RBCs are removed. The disk continues to spin during all return steps to maintain plasma-red cell separation and achieve a largely cell-free plasma.
These draw and return steps are repeated until both absolute RBC target volume and plasma target volume are achieved, as determined by scales separately weighting the two product bags.
The disk is emptied after the last donor draw step and after the plasma target volume has been reached by pumping all packed RBCs in the disk into the RBC product bag. Air from the air bag backfills the disk. Then the leukofilter is purged with storage solution to improve RBC recovery.
The donor is removed from this system immediately after the final donor draw step.
Another embodiment of the invention employs an identical blood collection and processing process as depicted in
The buffy coat, a mixture of leukocytes and platelets, develops at the red cell-plasma interface in the CFC 500 (
While the description above refers to particular embodiments of the present invention, it will be understood that many modifications may be made without departing from the spirit thereof. The accompanying claims are intended to cover such modifications as would fall within the true scope and spirit of the present invention. The presently disclosed embodiments are therefore to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims, rather than the foregoing description, and all changes that come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.
This application is a continuation of U.S. patent application Ser. No. 11/102,215, filed on Apr. 8, 2005, which is incorporated herein by reference.
| Number | Date | Country | |
|---|---|---|---|
| Parent | 11102215 | Apr 2005 | US |
| Child | 11386441 | Mar 2006 | US |
