Patent Application
20240024560
The present disclosure is directed to a separation system and a method for controlling the flow of fluid into and out of the system. The system monitors fluid flow in and out of a separator using optical measurements and making adjustments to the flow accordingly. The method adjusts the flow rate so that the outlet concentration is equivalent to a target outlet concentration.
The use of devices for the separation of whole blood or its constituent components is widespread. Such devices commonly utilize centrifuges (that separate the cellular components based on their density) or filter membranes (that separate the cellular components based upon their size).
According to one approach, blood or blood components may be separated into its constituents through centrifugation. This requires that the blood or blood components be passed through a centrifuge. The centrifuge rotates the separation chamber of the disposable flow circuit during processing, causing the heavier (greater specific gravity) components of the whole blood or components in the separation chamber, such as red blood cells, to move radially outwardly away from the center of rotation toward the outer or “high-G” wall of the separation chamber. The lighter (lower specific gravity) components, such as plasma, migrate toward the inner or “low-G” wall of the separation chamber. The boundary that forms between the heavier and lighter components in the separation chamber is commonly referred to as the interface. Various ones of these components can be selectively removed from the whole blood by providing appropriately located channeling structures and outlet ports in the flow circuit.
While many blood separation systems and procedures have employed centrifugal separation principles, another common separation device is a spinning membrane separator. This type of device employs relatively rotating surfaces, at least one or which carries a porous membrane. Typically, the device employs an outer stationary housing and an internal spinning rotor covered by a porous membrane. A detailed description of an exemplary spinning membrane separator may be found in U.S. Pat. No. 5,194,145, which is incorporated by reference herein.
In particular separation processes, such as a platelet separation process, the outlet cell concentration (platelet concentration) may impact the storage characteristics of the cells. In these particular processes it is desirable to ensure the outlet concentration is as close to a target outlet cell concentration as possible. Methods incorporating weight scales on the product bag(s) and ultrasonic flow sensors have proven less effective due to issues with accuracy and cost. Therefore, a need for a cost-effective solution to ensure that the fluid exiting the separator is at a target cell concentration is still needed.
There are several aspects of the present subject matter which may be embodied separately or together in the devices and systems described and claimed below. These aspects may be employed alone or in combination with other aspects of the subject matter described herein, and the description of these aspects together is not intended to preclude the use of these aspects separately or the claiming of such aspects separately or in different combinations as set forth in the claims appended hereto.
According to a first aspect, the present disclosure is directed to a method for separating a suspension of biological cells at a target outlet cell concentration. The method is performed using a system comprising a separator with an inlet for introducing the suspension of biological cells into the separator and a first outlet for flowing cell concentrate from the separator. The system further comprises a first optical sensor on the inlet, a second optical sensor on the first outlet, and a controller. The method includes setting a target outlet concentration and target ratio of inlet concentration to outlet concentration, determining an inlet rate and an inlet concentration, and calculating an initial outlet rate based on the target ratio, measured inlet rate and measured inlet concentration. The method also includes setting the initial outlet rate for the separator and operating the separator at this outlet rate, performing an optical measurement at the first and second optical sensors, and comparing the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor to the target ratio. Next, the method includes adjusting the separator to an adjusted outlet rate if the ratios are not equal, and performing previous steps until the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor is equal to the target ratio, producing the target outlet cell
According to a second aspect, the present disclosure is directed to a method for separating a suspension of biological cells at a target outlet cell concentration. The method is performed using a system comprising a separator with an inlet for introducing the suspension of biological cells into the separator and a first outlet for flowing cell concentrate from the separator. The system further comprises a first optical sensor on the inlet, a second optical sensor on the first outlet, and a controller. The method includes setting a target outlet concentration and target ratio of outlet concentration to inlet concentration, determining an outlet rate and an inlet concentration and calculating an initial inlet rate based on the target ratio, measured outlet rate and measured inlet concentration. The method further includes setting the initial inlet rate for the separator and operating the separator at this inlet rate, performing an optical measurement at the first and second optical sensors and comparing the ratio of the optical measurement at the second optical sensor to the optical measurement at the first optical sensor to the target ratio. Next, the method includes adjusting the separator to an adjusted inlet rate if the ratios are not equal and performing previous steps until the ratio of the optical measurement at the second optical sensor to the optical measurement at the first optical sensor is equal to the target ratio, producing the target outlet cell concentration.
In a third aspect, the present disclosure is directed to a system for separating a suspension of biological cells. The system includes a fluid circuit comprising a separator with an inlet for introducing the suspension of biological cells into the separator and a first outlet for flowing cell concentrate from the separator. The system also includes a hardware component comprising a first pump for flowing the suspension of biological cells to the inlet of the separator, a second pump for flowing the cell concentrate from a first outlet of the separator, a first optical sensor associated with the first outlet, and a second optical sensor associated with the second outlet. The system further includes a programmable controller which is configured to set a target outlet concentration and set a target ratio of inlet concentration to outlet concentration, determine an inlet rate and an inlet concentration, and calculate an initial outlet rate based on the target ratio, measured inlet rate and measured inlet concentration. The controller is further configured to set the initial outlet rate for the separator and operate the separator at this outlet rate, perform an optical measurement at the first and second optical sensors and compare the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor to the target ratio. The controller is also configured to adjust the separator to an adjusted outlet rate by adjusting the second pump if the ratios are not equal and perform previous steps until the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor is equal to the target ratio, producing the target outlet cell concentration.
These and other aspects of the present subject matter are set forth in the following detailed description of the accompanying drawings.
The embodiments disclosed herein are for the purpose of providing an exemplary description of the present subject matter. They are, however, only exemplary and not exclusive, and the present subject matter may be embodied in various forms. Therefore, specific details disclosed herein are not to be interpreted as limiting the subject matter as defined in the accompanying claims.
“Biological fluid” includes without limitation blood and blood components, and “cell” or “biological cell” includes without limitation blood cells, such as red cells, white cells and platelets. By “automated,” it is meant that the apparatus can be programmed to carry out the processing steps of a biological fluid processing method without substantial operator involvement. Of course, even in the automated system of the present disclosure, it will be understood that operator activity may be involved, including the loading of the disposable fluid circuits and entering processing parameters. Additional manual steps may be required as well. However, the reusable apparatus can process biological fluid through the disposable circuit(s) described below without substantial operator intervention.
The illustrated processing apparatus is typically capable of effecting the separation of a biological fluid that includes biological cells into two or more components or fractions. Thus, the reusable apparatus may generate conditions that allow for the separation of a biological fluid into selected components or fractions.
Generally speaking, the separation system includes a disposable fluid flow circuit with a spinning membrane separator or a centrifugal separator chamber, additional components that control fluid flow through the disposable flow circuit, and a controller, which governs the operation of the other components of the blood separation system to control the flow in and out of the separator.
The fluid flow circuit or flow set is intended to be a sterile, single use, disposable item. Before beginning a given blood processing and/or collection procedure, the operator mounts the various components of the fluid flow circuit into the blood separation system. The controller implements the procedure based upon preset protocols, taking into account other input from the operator. Upon completing the procedure, the operator removes the fluid flow circuit from association with the blood separation system. The portions of the fluid flow circuit holding the collected blood component or components (e.g., collection containers or bags) are removed and retained for storage, transfusion, or further processing. The remainder of the fluid flow circuit is removed and discarded.
The containers and the plastic tubing of the fluid circuit are made of conventional medical grade plastic that can be sterilized by sterilization techniques commonly used in the medical field such as, but not limited to, radiation or autoclaving. Plastic materials useful in the manufacture of containers and of the tubing in the circuits disclosed herein include plasticized poly(vinyl chloride). Other useful materials include acrylics. In addition, certain polyolefins may also be used.
A variety of different disposable fluid flow circuits may be used in combination with the blood separation system, with the appropriate fluid flow circuit depending on the separation procedure to be carried out using the system. Generally speaking, though, the fluid flow circuit may include a cassette, to which the other components of the fluid flow circuit are connected by flexible tubing. The other components may include a plurality of fluid containers (for holding blood, a separated blood component, an intravenous fluid, or an additive solution, etc.,), one or more blood source access devices (e.g., a phlebotomy needle or a connector for accessing blood within a fluid container), and a separator. The separator may be a spinning membrane separator 16 (
A fluid flow circuit may be provided with a centrifugal separation chamber 36 if platelets and/or white blood cells are to be separated. An exemplary centrifugal separation chamber 36 is shown in
The underside of the centrifugal separation chamber 36 includes a shaped receptacle 86 that is suitable for receiving an end of an umbilicus of a fluid flow circuit. A suitable receptacle 86 and the manner in which the umbilicus may cooperate with the receptacle 86 to deliver fluid to and remove fluid from the centrifugal separation chamber 36 are described in greater detail in U.S. Pat. No. 8,075,468.
The illustrated centrifugal separation chamber 36 has radially spaced apart inner (low-g) and outer (high-g) side wall portions 88 and 90, a bottom or first end wall portion 92, and a cover or second end wall portion 93. The cover 93 comprises a simple flat part that can be easily welded or otherwise secured to the body of the centrifugal separation chamber 36. The wall portions 88 and 90, the bottom 92, and the cover 93 together define an enclosed, generally annular channel 94.
The (whole blood) inlet 96 communicating with the channel 94 is defined between opposing interior radial walls 98 and 100. One of the interior walls 98 joins the outer (high-g) wall portion 90 and separates the upstream and downstream ends of the channel 94. The interior walls 98 and 100 define the inlet passageway 96 of the centrifugal separation chamber 36 which, in one flow configuration, allows fluid to flow from the umbilicus 46 to the upstream end of the channel 94.
The illustrated centrifugal separation chamber 36 further includes first and second outlets 102 and 104, respectively, which may be defined by opposing surfaces of interior radial walls. Both the first and second outlets 102 and 104 extend radially inward from the channel 94. The first (platelet-rich plasma) outlet 102 extends radially inward from an opening which, in the illustrated embodiment, is located at the inner side wall portion 88, while the second (red blood cell) outlet 104 extends radially inward from an opening that is associated with the outer side wall portion 90. The illustrated first outlet 102 is positioned adjacent to the inlet 96 (near the upstream end of the channel 94), while the second outlet 104 may be positioned at the opposite, downstream end of the channel 94.
Blood flowed into the channel 94 separates into an optically dense layer RBC and a less optically dense layer PRP as the centrifugal separation chamber 36 is rotated about the rotational axis 38. The optically dense layer RBC forms as larger and/or heavier blood particles move under the influence of centrifugal force toward the outer (high-g) wall portion 90. The optically dense layer RBC will typically include red blood cells (and, hence, may be referred to herein as the “RBC layer”) but, depending on the speed at which the centrifugal separation chamber 36 is rotated, other cellular components (e.g., larger white blood cells) may also be present in the RBC layer RBC.
The less optically dense layer PRP typically includes platelet-rich plasma (and, hence, will be referred to herein as the “PRP layer”). Depending on the speed at which the centrifugal separation chamber 36 is rotated and the length of time that the blood is resident therein, other components (e.g., smaller white blood cells and anticoagulant) may also be present in the PRP layer PRP.
The transition between the RBC layer RBC and the PRP layer PRP may be referred to as the interface INT. The location of the interface INT within the channel 94 of the centrifugal separation chamber 36 can dynamically shift during blood processing. The ideal or target interface INT may be experimentally determined, which may vary depending on any of a number of factors (e.g., the configuration of the centrifugal separation chamber 36, the rate at which the centrifugal separation chamber 36 is rotated about the rotational axis 38, etc.).
The blood separation system may include an interface monitoring system and a controller with an interface control module to monitor and, as necessary, correct the position of the interface INT.
Preferably, in accordance with the present disclosure, the fluid circuit includes a spinning membrane separator of the type described in U.S. Pat. Nos. 5,194,145 and 5,053,121, which are incorporated by reference.
As shown in
The housing 18 includes an inlet 26 for introducing the suspension of biological cells into the gap 22 to which a source of the biological suspension to be separated is connected by a first tubing segment 30. The suspension to be separated may be contained in a reservoir, it could also be sourced directly from a donor by means of a donor access device (such as a phlebotomy needle) on the free end of the first tubing segment 30.
The housing 18 further includes a first outlet 32 in communication with the gap 22 for flowing retentate from the separator 16 through a second tubing segment 34 to a first collection container, and a second outlet 38 in communication with the flow path 24 on the second side of the filter membrane for flowing filtrate from the separator through a third tubing 40 segment to a second collection container. In one example, the suspension of biological cells may be whole blood, the retentate may be red blood cells and the filtrate may be plasma. In a second example, the suspension of biological cells may be platelet rich plasma, the retentate may be a platelet concentrate and the filtrate may be platelet free plasma.
The spacing between the housing and the spinner is sometimes referred to as the shear gap. The shear gap may be approximately 0.02-0.06 inches (0.05-0.15 cm) and may be of a uniform dimension along axis 11, for example, where the axis of the spinner and housing are coincident. The shear gap may also vary circumferentially for example, where the axis of the housing and spinner are offset.
The shear gap also may vary along the axial direction, for example preferably an increasing gap width in the direction. Such a gap width may range from about 0.02 to about 0.075 inches (0.05-0.19 cm). The gap width could be varied by varying the outer diameter of the rotor and/or the inner diameter of the facing housing surface. The gap width could change linearly or stepwise or in some other manner as may be desired. In any event, the width dimension of the gap is preferably selected so that at the desired relative rotational speed, Taylor-Couette flow, such as Taylor vortices, are created in the gap.
In the illustrated embodiment, the surface of the internal member 20 is at least partially, and is preferably substantially or entirely, covered by a cylindrical porous membrane. The membrane may have a nominal pore size between 0.8 and 10 microns (μm), for example. Membranes may be fibrous mesh membranes, cast membranes, track-etched membranes or other types of membranes that will be known to those of skill in the art. For example, in one embodiment, the membrane may have a polyester mesh (substrate) with nylon particles solidified thereon, thereby creating a tortuous path through which only certain sized components will pass. In an embodiment, the nylon membrane may have a pore size of approximately 0.8 μm and a thickness of approximately 150 μm or greater. Membranes of this type will typically retain all cellular components (e.g., red blood cells, white blood cells) and certain formed blood components, e.g., platelets. In another embodiment, the membrane may be made of a thin (approximately 10 μm thick) sheet of unsupported polycarbonate, for example, with a pore size of approximately 4.0 μm. In this embodiment, pores (holes) may be cylindrical and larger than those described above. The pores may be sized to allow small, formed components (e.g., platelets, microparticles, etc.) to pass, while the desired cells (e.g., white blood cells and larger red blood cells) are collected.
In a preferred embodiment, the housing 18 is stationary and the internal member 20 is a rotating spinner that is rotatable concentrically within the cylindrical housing 18. In such an embodiment, the housing 18 (or at least its upper and lower ends) are formed of non-magnetic material, while the internal member 20 includes an element (e.g., a metallic material) that interacts with a magnet of a spinning membrane separator drive unit to rotate the internal member 20 within the housing 18, as described above.
In embodiments utilizing a spinning membrane separator, the blood separation system may include a spinner support or spinning membrane separator drive unit for accommodating a generally cylindrical spinning membrane separator 16 of the fluid flow circuit. U.S. Pat. No. 5,194,145 describes an exemplary spinning membrane separator drive unit that would be suitable for incorporation into the blood separation system, but it should be understood that the spinning membrane separator drive unit may be differently configured without departing from the scope of the present disclosure.
In embodiments utilizing a centrifugal chamber, the blood separation system may also include a centrifugal separator. The particular configuration and operation of the centrifugal separator depends upon the particular configuration of the centrifugal separation chamber 36 of the fluid flow circuit. In one embodiment, the centrifugal separator is similar in structure and operation to that of the ALYX system manufactured by Fenwal, Inc. of Lake Zurich, Illinois, which is an affiliate of Fresenius Kabi AG of Bad Homburg, Germany, as described in greater detail in U.S. Pat. No. 8,075,468, which is incorporated herein by reference.
The system may also include a plurality of pumps to cause fluid to flow through the fluid flow circuit. The pumps may be differently or similarly configured and/or function similarly or differently from each other. The pumps may be configured as peristaltic pumps, which may be generally configured as described in U.S. Pat. No. 5,868,696. Particularly, a first pump may be associated with an inlet of a separation device and a second pump may be associated with an outlet of the separation device. In embodiments with a spinning membrane separator, the outlet may be the retentate outlet 32.
The system may include weight scales for product bags and may be provided with a plurality of hooks or supports that may support various components of the fluid flow circuit or other suitably sized and configured objects.
As shown in
The inlet sensor S1 and outlet sensor S2 may be optical sensors, which make an optical measurement. The optical measurements may include fluid absorption coefficient or scattering coefficient. Additionally, optical measurements may include transmission and reflection values. Also, the sensors may measure the optical density of the fluid. Depending on the specific type of fluid passing through the separator, the density may increase between the inlet sensor S1 and the outlet sensor S2. The optical sensor may compute the optical density by measuring light transmission, reflection, or a combination of the two or use the measured transmission or reflection values in comparison. The method is not limited by the optical sensing method for determining optical density. The controller may receive signals from the sensors that are indicative of the optical properties of fluid flowing into and out of the spinning membrane separator 16 and use the signals to optimize the separation procedure based upon that property or properties. In one embodiment, separated plasma flows through the tubing, in which case the inlet sensor S1 and outlet sensor S2 may be configured to determine the concentration of cellular blood components in the plasma. This may be done using an optical monitor of the type described in U.S. Pat. No. 8,556,793 (which is incorporated herein by reference) or by any other suitable device and/or method.
According to an aspect of the present disclosure, the blood separation system includes a controller 300, schematically shown in
As is also illustrated in
The at least one input 302 may include a number of different devices according to the embodiments described herein. For example, the input 302 could include a keyboard or keypad by which a user may provide information and/or instructions to the controller 300. Alternatively, the input 302 may be a touch screen, such as may be used in conjunction with a video display 308. The input could also include a reader or scanner, such as a barcode reader or scanner or an RFID reader. The assembly of the input/touch screen 302 and video display 308 may be one of the afore-mentioned structures to which the controller 300 is coupled from which the controller 300 receives information and to which the controller 300 provides commands. According to still other embodiments, the input 302 may be in the form of computer equipment that permits the blood separation system including the controller 300 to communicate (whether via wires, cables, etc. or wirelessly) with other systems over a local network, or with other cell processing systems or other computer equipment (e.g., a server) over local networks, wide area networks, or the Internet. According to such an embodiment, the input may include an internal transmitter/receiver device.
The controller is configured and/or programmed to execute at least one fluid processing application but, more advantageously, is configured and/or programmed to execute a variety of different fluid processing applications.
More particularly, in carrying out any one of these blood processing applications, the controller is configured and/or programmed to control the flow of a fluid through a separator and adjusts the speed of the flow into and out of the separator. This may include instructing the spinning membrane separator drive unit or the centrifugal separator to operate at a particular rotational speed and instructing a first pump to convey fluid through the inlet of the separator at a particular flow rate and instructing a second pump to convey fluid out of the outlet of the separator at a particular flow rate. Any known method of adjusting speed of the flow into and out of the separator may be used. Hence, while it may be described herein that a particular component of the blood separation system performs a particular function, it should be understood that that component is being controlled by the controller to perform that function.
Before, during, and after a procedure, the controller may receive readings from the sensors S1 and S2 and may have to adjust based on these readings.
For example, the controller may instruct one of the pumps to cause blood to flow into the separator at a different rate and/or for a separated blood component to be removed from the separator at a different rate and/or for the drive unit to be spun at a different speed.
Such control typically occurs regardless of whether the blood originates from a container or directly from a donor, and regardless of whether the components are directed into storage containers or returned to a donor or another living recipient.
The system, specifically the controller, may act to regulate the concentration of cellular content exiting the separator. A governing equation of separation by any separator is the mass balance relationship, which may be calculated as follows:
C
out
Q
out
=C
in
Q
in [Equation 1]
Cout is concentration of cellular content exiting the separator, Qout is flow rate of the fluid exiting the separator, Cin is the concentration of the cellular content entering the separator, and Qin is the flow rate of the fluid entering the separator. Equation 1 can be rearranged to solve for any parameter of interest. If the fluid inlet concentration and flow rate (Cin & Qin) are known and a target outlet concentration (Cout) is desired, then the relationship can be rearranged to solve for the outlet fluid flow rate (Qout) required to obtain a desired target outlet concentration (Cout) based on the known inlet concentration and flow rate (Cin& Qin), which may be calculated as follows:
Qout=(CinQin)/Cout [Equation 2]
If all parameters are accurate (ex: pumps are achieving targeted flow rates) then the system will obtain the desired/targeted outlet concentration. Reversely, if the fluid inlet concentration and outlet flow rate are known and a target outlet concentration is desired, then the relationship can be rearranged to solve for the inlet fluid flow rate required to obtain a desired target outlet concentration based on the known inlet concentration and outlet flow rate, which may be calculated as follows:
Q
in=(CoutQout)/Cin [Equation 3]
Again, if all parameters are accurate (ex: pumps are achieving targeted flow rates) then the system will obtain the desired/targeted outlet concentration.
Once a procedure begins, optical measurements, such as the optical density, of the inlet may be measured by optical sensor S1 on the inlet line and the optical density of the outlet may be measured by optical sensor S2 on the outlet line. The optical sensor may compute the optical density by measuring light transmission, reflection, or a combination of the two.
Using the measured optical densities, an outlet concentration can be calculated. There may be any of a number of errors which can cause an inaccuracy in the outlet concentration that is produced. Inaccuracy of the actual outlet concentration compared to the target outlet concentration is common and most often due to one or more of the assumed values being incorrect, such as pump driven flow rates not equaling target flow rate values.
In order to correct the system to achieve a target outlet concentration, the controller can adjust the inlet or outlet flow rates. This may be accomplished in a number of ways. Typically, the control of fluid into and out of the spinning membrane device has been accomplished by applying a first pump to the inlet line of the separator to supply a fluid source, and a second pump applied to either the outlet line for the retentate or the outlet line for the filtrate and adjusting the pump speed. The controller can also adjust the drive unit or centrifuge. The inlet or outlet flow rates may be adjusted by an amount calculated after measuring the ODin and ODout.
(Cin/Cout)=target concentration ratio [Equation 4]
The concentration ratio should be equal to the ratio of the Optical Density of the inlet (ODin) to the optical density of the outlet (ODout) shown in the following equation:
(Cin/Cout)=target concentration ratio=(ODin/ODout) [Equation 5]
Considering there is a known change in the optical density (OD) of the fluid with respect to a change in cellular concentration (optical density increases as concentration increases) and assuming (as suggested by known data) the ratio equals the concentration ratio, the relationships above can be reconstructed in terms on optical density (OD) as following:
OD
out
Q
out
=OD
inQin [Equation 6]
The system next needs to calculate the optimal outlet rate given the target concentration ratio and the inlet rate in the following equation:
Q
out-initial=target concentration ratio*Qin [Equation 7]
Then, once the procedure begins the measured optical density ratio (ODin-measured/ODout-measured), which may not equal the target concentration/optical density ratio, can be used to determine the measured outlet rate (Qout-measured):
Q
out-measured=(ODin-measured/ODout-measured)*Qin [Equation 8]
Once the measured outlet rate is calculated it is compared to the initial outlet rate to determine any inaccuracies present in the pump:
Q
out-diff
=Q
out-initial
−Q
out-measured [Equation 9]
Then, the system will then adjust the outlet rate (Qout-adjusted) in an attempt to move the measured optical density ratio (ODin-measured/ODout-measured), equal to the targeted optical density ratio/concentration ratio established:
Q
out-adjusted
=Q
out-initial
+Q
out-diff [Equation 10]
It may be possible that the actual inlet rate Qin does not equal the target rate that is held constant in the equations or for the adjusted outlet rate to still be inaccurate. To account for these inaccuracies the method works in a loop to ensure an outlet rate is achieved that produces a measured optical density ratio equal to the target optical density ratio. Once the measured ratio equals the target ratio, the outlet concentration will equal the desired/target concentration regardless of the actual flow rates values.
Instead of adjusting the outlet rate to obtain the desired outlet concentration, the inlet rate can be adjusted in a similar manner. Since the inlet rate is being adjusted the target concentration ratio will instead be calculated as follows:
(Cout/Cin)=target concentration ratio [Equation 11]
The concentration ratio should be equal to the ratio of the optical density of the outlet (ODout) to the optical density of the inlet (ODin) shown in the following equation:
(Cout/Cin)=target Concentration ratio=(ODout/ODin) [Equation 12]
The optimal inlet rate given the target concentration ratio and the outlet rate in the following equation:
Q
in-initial=target concentration rati*Qout [Equation 13]
Then, once the procedure begins the measured optical density ratio (ODout-measured/ODin-measured), which may not equal the target concentration/optical density ratio, can be used to determine the measured inlet rate (Qin-measured):
Q
in-measured=(ODout-measured/ODin-measured)*Qout [Equation 14]
Once the measured inlet rate is calculated it is compared to the initial inlet rate to determine any inaccuracies present in the system:
Q
in-diff
=Q
in-initial
−Q
in-measured [Equation 14]
Then, the system will then adjust the inlet rate Qin-adjusted in an attempt to move the measured optical density ratio (ODout-measured/ODin-measured), equal to the targeted optical density ratio/concentration ratio established:
Q
in-adjusted
=Q
in-initial
+Q
in-diff [Equation 15]
Example 1: Qin=30 mL/min; Cin=250 e3/uL; desired Cout=1500 e3/uL
Q
out-initial=Target Concentration Ratio*Qin=(⅙)×30 mL/min=5 mL/min
The system is set to an outlet rate of 5 mL/min. After some running time, optical densities are measured, and the actual ration is determined. ODin-measured=5 OD units; ODout-measured=37.5 OD units. The Qout-measured can be calculated:
Q
out-measured=(ODin-measured/ODout-measured)*Qin=( 5/37.5)*30 mL/min=4 mL/min
The measured optical density ratio does not equal the target value of (⅙). The system is, therefore, over-concentrating the cells and it is assumed that the Qout is pumping too slow (4 mL/min) instead of (5 mL/min). The Cout is:
C
out=(Cin/Qin)/Qout=(250*30)/4=1875 e3/uL
The outlet concentration is 1875 e3/uL versus the desired 1500 e3/uL and the outlet rate will have to be adjusted accordingly. The outlet rate difference is calculated:
Q
out-diff
=Q
out-initial
−Q
out-measured=5 mL/min−4 mL/min=1 mL/min
This amount is then added to the initial outlet rate and the new adjusted outlet rate for the system is calculated:
Q
out-adjusted
=Q
out-initial
+Q
out-diff=5 mL/min+1 mL/min=6 mL/min
The system (controller) will then adjust the outlet rate to 6 mL/min and after allowing time to correct, take additional optical measurements to determine if the concentration is on target. The system will keep testing and adjusting as needed to achieve the target concentration.
Thus, an improved fluid separation system and method have been provided. The system and method should provide for greater accuracy in controlling the outlet concentration from the separator by utilizing inlet and outlet optical sensors and adjusting components of the system to regulate the flow in and out of the separator.
Aspect 1. A method for separating a suspension of biological cells at a target outlet cell concentration using a system comprising a separator with an inlet for introducing the suspension of biological cells into the separator and a first outlet for flowing cell concentrate from the separator, a first optical sensor on the inlet, a second optical sensor on the first outlet, and a controller, the method comprising: setting a target outlet concentration and target ratio of inlet concentration to outlet concentration; determining an inlet rate and an inlet concentration; calculating an initial outlet rate based on the target ratio, measured inlet rate and measured inlet concentration; setting the initial outlet rate for the separator and operating the separator at this outlet rate; performing an optical measurement at the first and second optical sensors; comparing the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor to the target ratio; adjusting the separator to an adjusted outlet rate if the ratios are not equal; and performing steps e-g until the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor is equal to the target ratio, producing the target outlet cell concentration.
Aspect 2. The method of separating of Aspect 1, wherein the separator is a spinning membrane separator.
Aspect 3. The method of separating of Aspect 2, wherein the separator includes a first and second outlet, the first outlet for flowing retentate from the separator.
Aspect 4. The method of separating of Aspect 1, wherein the separator includes a centrifugal chamber.
Aspect 5. The method of separating of any of the preceding Aspects, wherein the optical measurement is optical density.
Aspect 6. The method of separating of any of the preceding Aspects, wherein the adjusting includes the altering the pump associated with the first outlet to adjust the outlet rate.
Aspect 7. The method of separating of any of the preceding Aspects, wherein the adjusting includes calculating the difference between the measured outlet rate and the initial outlet rate and adding the difference to the initial outlet rate to get the adjusted outlet rate.
A method for separating a suspension of biological cells at a target outlet cell concentration using a system comprising a separator with an inlet for introducing the suspension of biological cells into the separator and a first outlet for flowing cell concentrate from the separator, a first optical sensor on the inlet, a second optical sensor on the first outlet, and a controller, the method comprising: setting a target outlet concentration and target ratio of outlet concentration to inlet concentration; determining an outlet rate and an inlet concentration; calculating an initial inlet rate based on the target ratio, measured outlet rate and measured inlet concentration; setting the initial inlet rate for the separator and operating the separator at this inlet rate; performing an optical measurement at the first and second optical sensors; comparing the ratio of the optical measurement at the second optical sensor to the optical measurement at the first optical sensor to the target ratio; adjusting the separator to an adjusted inlet rate if the ratios are not equal; and performing steps e-g until the ratio of the optical measurement at the second optical sensor to the optical measurement at the first optical sensor is equal to the target ratio, producing the target outlet cell concentration.
Aspect 9. The method of separating of Aspect 8, wherein the separator is a spinning membrane separator.
Aspect 10. The method of separating of Aspect 9, wherein the separator includes a first and second outlet, the first outlet for flowing retentate from the separator.
Aspect 11. The method of separating of Aspect 8, wherein the separator includes a centrifugal chamber.
Aspect 12. The method of separating of any of Aspects 8-11, wherein the optical measurement is optical density.
Aspect 13. The method of separating of any of Aspects 8-12, wherein the adjusting includes the altering the pump associated with the first inlet to adjust the inlet rate.
Aspect 14. The method of separating of any of Aspects 8-13, wherein the adjusting includes calculating the difference between the measured inlet rate and the initial inlet rate and adding the difference to the initial inlet rate to get the adjusted inlet rate.
Aspect 15. A system for separating a suspension of biological cells comprising: (i) a fluid circuit comprising a separator with an inlet for introducing the suspension of biological cells into the separator and a first outlet for flowing cell concentrate from the separator; (ii) a hardware component comprising a first pump for flowing the suspension of biological cells to the inlet of the separator, a second pump for flowing the cell concentrate from a first outlet of the separator, a first optical sensor associated with the first outlet, a second optical sensor associated with the second outlet, and a programmable controller configured to: (a) set a target outlet concentration and set a target ratio of inlet concentration to outlet concentration; (b) determine an inlet rate and an inlet concentration; (c) calculate an initial outlet rate based on the target ratio, measured inlet rate and measured inlet concentration; (d) set the initial outlet rate for the separator and operate the separator at this outlet rate; (e) perform an optical measurement at the first and second optical sensors; (f) compare the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor to the target ratio; (g) adjust the separator to an adjusted outlet rate by adjusting the second pump if the ratios are not equal; and (h) perform steps e-g until the ratio of the optical measurement at the first optical sensor to the optical measurement at the second optical sensor is equal to the target ratio, producing the target outlet cell
Aspect 15. The system of Aspect 14, wherein the separator is a spinning membrane separator.
Aspect 16. The system of Aspect 15, wherein the separator includes a first and second outlet, the first outlet for flowing retentate from the separator.
Aspect 17. The system of Aspect 14, wherein the separator includes a centrifugal chamber.
Aspect 18. The system of Aspect 14, wherein the optical measurement is optical density.
Aspect 19. The system of any of Aspects 14-18, wherein the adjusting includes the altering the pump associated with the first outlet to adjust the outlet rate.
Aspect 20. The method of separating of any Aspects 14-19, wherein the adjusting includes calculating the difference between the measured outlet rate and the initial outlet rate and adding the difference to the initial outlet rate to get the adjusted outlet rate.
This application claims the benefit of and priority of U.S. Provisional Patent Application Ser. No. 63/391,415, filed Jul. 22, 2022, the contents of which are incorporated by reference herein.
| Number | Date | Country | |
|---|---|---|---|
| 63391415 | Jul 2022 | US |
