U.S. patent application number 17/275283 was filed with the patent office on 2022-02-10 for separation devices, associated methods, and systems.
The applicant listed for this patent is Global Life Sciences Solutions USA LLC. Invention is credited to Jason William CASTLE, Anindya Kanti De, Craig Patrick Galligan, Rachel Marie Gettings, Jared Timothy Hale, Erik Leeming Kvam, Matthew Jeremiah Misner, Christine Angela Morton, Vincent Francis Pizzi.
Application Number | 20220041976 17/275283 |
Document ID | / |
Family ID | |
Filed Date | 2022-02-10 |
United States Patent
Application |
20220041976 |
Kind Code |
A1 |
Misner; Matthew Jeremiah ;
et al. |
February 10, 2022 |
SEPARATION DEVICES, ASSOCIATED METHODS, AND SYSTEMS
Abstract
A system for isolating a target molecule from a bioprocess fluid
includes a single-use disposable separation device having a
plurality of perimeter-bonded layers defining one or more
mesofluidic channels of the separation device, wherein each layer
includes a biocompatible polymer material, wherein the separation
device is configured to separate at least a portion of particles
from the bioprocess fluid to generate a substantially clarified
bioprocess fluid, and a chromatography system fluidically coupled
at the outflow of the separation device in a configuration for
further processing the clarified bioprocess fluid.
Inventors: |
Misner; Matthew Jeremiah;
(Delanson, NY) ; Gettings; Rachel Marie;
(Niskayuna, NY) ; Morton; Christine Angela;
(Niskayuna, NY) ; Kvam; Erik Leeming; (Niskayuna,
NY) ; CASTLE; Jason William; (Esperance, NY) ;
De; Anindya Kanti; (Niskayuna, NY) ; Hale; Jared
Timothy; (Niskayuna, NY) ; Galligan; Craig
Patrick; (Niskayuna, NY) ; Pizzi; Vincent
Francis; (Niskayuna, NY) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Global Life Sciences Solutions USA LLC |
Marlborough |
MA |
US |
|
|
Appl. No.: |
17/275283 |
Filed: |
August 30, 2019 |
PCT Filed: |
August 30, 2019 |
PCT NO: |
PCT/EP2019/073198 |
371 Date: |
March 11, 2021 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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16128121 |
Sep 11, 2018 |
11028359 |
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17275283 |
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International
Class: |
C12M 1/00 20060101
C12M001/00; B01D 17/02 20060101 B01D017/02; B01D 21/00 20060101
B01D021/00; B01D 21/02 20060101 B01D021/02; B01D 21/24 20060101
B01D021/24; B01L 3/00 20060101 B01L003/00; C12M 1/32 20060101
C12M001/32; G01N 30/00 20060101 G01N030/00; C12M 1/26 20060101
C12M001/26 |
Claims
1. A method for clarifying a bioprocess fluid comprising particles
suspended in a cell culture fluid, the method comprising: flowing
an unclarified bioprocess fluid from a bioreactor through a
plurality of mesofluidic channels of a separation device comprising
a fluid inlet and a fluid outlet to separate at least a portion of
particles of the unclarified bioprocess fluid to generate a
substantially clarified bioprocess fluid; and collecting the
clarified bioprocess fluid from the fluid outlet of the separation
device; wherein a residence time of the bioprocess fluid between
the fluid inlet and fluid outlet of the separation device ranges
from 10 minutes to 40 minutes, and wherein the separation device is
operated at an angle less than 10.degree. relative to a work
surface.
2. The method of claim 1, wherein the separation device is operated
at an angle less than or equal to 5.degree. relative to the work
surface.
3. The method of claim 1, wherein the separation device is operated
at an angle of about 0.degree. relative to the work surface.
4. The method of claim 1, wherein the particles comprise cells,
aggregated cells, adhered cells on carriers, diatomaceous earth,
resin beads, or a combination thereof.
5. The method of claim 1, wherein the substantially clarified
bioprocess fluid comprises biotherapeutically active products,
cells, proteins, viruses, vaccines, DNA, RNA, or a combination
thereof.
6. The method of claim 1, wherein a capacity of the separation
device and a flow rate of the bioprocess fluid flowed through the
plurality of mesofluidic channels is configured to process up to
10,000 liters of the bioprocess fluid within the residence
time.
7. The method of claim 1, wherein a capacity of the separation
device and a flow rate of the bioprocess fluid flowed through the
plurality of mesofluidic channels is configured to process up to
4,000 liters of the bioprocess fluid within the residence time.
8. The method of claim 1, wherein a capacity of the separation
device and a flow rate of the bioprocess fluid flowed through the
plurality of mesofluidic channels is configured to process up to
2,000 liters of the bioprocess fluid within the residence time.
9. The method of claim 1, additionally comprising recovering the
separated particles from the plurality of mesofluidic channels of
the separation device subsequent to collecting the clarified
bioprocess fluid.
10. The method of claim 1, additionally comprising adding a
flocculant to the unclarified bioprocess fluid before flowing the
unclarified bioprocess fluid through the separation device to aid
in separation of the particles from the bioprocess fluid.
11. The method of claim 1, additionally comprising: lowering the pH
of the unclarified bioprocess fluid before flowing the unclarified
bioprocess fluid through the separation device, and raising the pH
of the clarified bioprocess fluid to a neutral pH after collecting
the unclarified bioprocess fluid from the separation device.
12. The method of claim 1, additionally comprising flushing the
separation device before a terminal capacity of the separation
device is reached, wherein flushing the separation device comprises
flowing a separate fluid through the separation device and removing
the particles separated in the separation device.
13. The method of claim 1, additionally comprising reversing a flow
from the outlet of the separation device such that a separate fluid
is flowed from the fluid outlet of the separation device to the
fluid inlet of the separation device before a terminal capacity of
the separation device is reached, and returning the separated
particles to the bioreactor or a separate container.
14. The method of claim 1, additionally comprising recovering the
separated particles captured in the separation device.
15. The method of claim 1, which is carried out in the system of
any one of claims 16-29.
16. A system for isolating a target molecule from a bioprocess
fluid, the system comprising: a single-use disposable separation
device comprising a plurality of perimeter-bonded layers defining
one or more mesofluidic channels of the separation device, wherein
each layer comprises a biocompatible polymer material, wherein the
separation device is configured to separate at least a portion of
particles from the bioprocess fluid to generate a substantially
clarified bioprocess fluid; and a secondary purification system
fluidically coupled to and outlet of the separation device
configured to further process the clarified bioprocess fluid.
17. The system of claim 16, wherein the layers comprise a top
layer, a bottom layer, and one or more intervening layers, and
wherein the perimeter-bonded layers define the one or more
mesofluidic channels in a stacked parallel configuration.
18. The system of claim 17, wherein the separation device comprises
a plurality of spacers disposed at ends of the layers, wherein the
spacers of each intervening layer comprise a hole, wherein each of
the top layer and the bottom layer comprise one spacer comprising a
hole and one spacer not comprising a hole, and wherein the spacer
of the top layer comprising the hole is disposed at an end of the
device opposite the spacer of the bottom layer comprising the
hole.
19. The system of claim 18, wherein the separation device comprises
a fluid inlet manifold and a fluid outlet manifold, wherein the
fluid inlet and the fluid outlet are formed from the holes of the
spacers, and wherein the one or more mesofluidic channels are
fluidically coupled to and disposed between the fluid inlet
manifold and the fluid outlet manifold.
20. The system of claim 19, wherein each mesofluidic channel of the
one or more mesofluidic channels of the separation device comprise
a height within a range of 2 millimeters to 20 millimeters, and
wherein the height of each mesofluidic channel is defined by the
spacers.
21. The system of claim 19, wherein each mesofluidic channel of the
one or more mesofluidic channels of the separation device comprise
a height within a range of 2 millimeters to 10 millimeters, such as
2 millimeters to 6 millimeters, and wherein the height of each
mesofluidic channel is defined by the spacers.
22. The system of claim 16, comprising a bioreactor fluidically
coupled to an inlet of the separation device and configured to flow
the bioprocess fluid to the separation device.
23. The system of claim 16, wherein the separation device comprises
a capacity of up to 2,000 L such that when the separation device is
provided with the bioprocess fluid at a particular flow rate, a
ratio of the capacity of the separation device to the flow rate of
the provided bioprocess fluid is within a range of 10 minutes to 40
minutes.
24. The system of claim 16, wherein the separation device comprises
multiple separation devices connected in parallel and/or in
series.
25. The system of claim 16, wherein the separation device comprises
multiple separation devices connected in parallel which are
fluidically coupled to the bioreactor, and wherein the parallel
separation devices are operated in an alternating arrangement such
that the parallel separation devices can be alternately supplied
with the bioprocess fluid.
26. The system of claim 16, wherein a residence time of the
bioprocess fluid within the separation device ranges from 10
minutes to 40 minutes.
27. The system of claim 16, wherein the secondary purification
system includes depth filtration, membrane filtration,
chromatography, centrifugation, or any combination thereof.
28. A system for isolating a target molecule from a bioprocess
fluid, the system comprising: a bioreactor; a separation device
fluidically coupled to the bioreactor at an inlet of the separation
device and configured to receive a flow of the bioprocess fluid
from the bioreactor and to separate a least a portion of particles
from the bioprocess fluid to generate a substantially clarified
bioprocess fluid, wherein the separation device comprises a
plurality of parallel mesofluidic channels for separation of the
particles, and wherein the separation device is operated at an
angle less than 10.degree. relative to a work surface; and one or
more additional purification subsystems fluidically coupled to an
outlet of the separation device and configured for further
processing of the clarified bioprocess fluid, wherein the
additional purification subsystems comprise chromatographic
separation, secondary depth filtration, a polishing membrane, or
any combination thereof.
29. The system of claim 28, wherein the separation device is a
configured to process the bioprocess fluid having a cell density of
at least 1 million cells/mL.
30. The system of claim 28, wherein a residence time of the
bioprocess fluid within the separation device ranges from 16
minutes to 30 minutes.
Description
BACKGROUND
[0001] The present disclosure relates to systems and devices
comprising mesofluidic channels useful for separating particulate
materials from fluids. In a particular aspect, the present
disclosure relates to a method for separating particulates using
the systems and devices provided herein.
[0002] Biopharmaceutical production is trending toward higher cell
densities and product titers such that single-use harvest systems
are becoming financially and logistically advantageous. Single-use
bioreactors for cell culture volumes greater than or equal to 2,000
L provide an economically attractive alternative to stainless steel
infrastructure as batch production titers continue to increase.
Many biopharmaceuticals are initially separated from producer cells
in a crude harvest step prior to downstream purification via
chromatography systems. Volumetrically scalable solutions for this
harvest step include centrifugation and/or depth filtration when a
protein or other product (e.g. virus) is produced. Depth filtration
has been adopted as a single-use harvest method to remove intact
cells and cellular debris via primary and secondary clarification,
respectively, however this process suffers from cell caking and
clogging as bioreactor cell densities gradually increase, which is
undesirable for manufacturing productivity. Additionally, the total
filtration area of depth filtration tends to scale proportionally
with cell density for primary harvest, which is undesirable for
inventory floor space and is technically and economically
prohibitive at cell densities greater than 30 million cells/mL.
Centrifugation may be a suitable alternative for large fixed-asset
(stainless steel) manufacturing sites, however, centrifugation may
be prohibitive in smaller single-use contexts due to capital
equipment expenditure, sterilization preparation time between
batches, and centrifugation equipment maintenance. Additionally,
centrifugation-based harvest may suffer from unsatisfactory product
loss when bioreactor feedstocks contain high cell densities (e.g.
solids exceeding 10% of the culture mass). Past attempts to address
cell separation typically employ inclination that includes
vertically flowing cell containing fluid at an angle between 30 and
80.degree. from horizontal toward a separation channel. Cell
separation is transverse to the vertical fluid flow through
separation channel for cells to flow into a separate chamber.
Separation is limited to the cells passing over the separation
channel amounting to a filtration device, prone to fouling, for
perfusion operations with flow rates below 40 L/day, which is not
applicable to batch cell culture primary clarification
operations.
[0003] As such, there exists a need to provide devices and methods
for efficient separation of cells and/or dispersed particulates
(including cell aggregates, adhered cells on carriers, resin beads
and diatomaceous earth) from fluids, especially from bioreactor
feedstocks with high cell densities. Fast and efficient separation
and collection of cells and/or particulates from large samples
(e.g., .gtoreq.2,000 L), without complex equipment, remains an
unmet need.
BRIEF DESCRIPTION
[0004] In one embodiment, a method for clarifying a bioprocess
fluid having particles suspended in a cell culture fluid includes
flowing an unclarified bioprocess fluid from a bioreactor through a
plurality of mesofluidic channels within a separation device to
separate at least a portion of particles from the unclarified
bioprocess fluid to generate a substantially clarified bioprocess
fluid, and collecting the clarified bioprocess fluid from an outlet
of the separation device, wherein a residence time of the
bioprocess fluid within the separation device ranges from 10
minutes to 40 minutes relative to the time at which all or a
portion of the fluid first enters the device.
[0005] In another embodiment, a system for isolating a target
molecule from a bioprocess fluid includes a single-use disposable
separation device having a plurality of perimeter-bonded layers
defining one or more mesofluidic channels of the separation device,
wherein each layer includes a biocompatible polymer material,
wherein the separation device is configured to separate at least a
portion of particles from the bioprocess fluid to generate a
substantially clarified bioprocess fluid, and a chromatography
system fluidically coupled at the outflow of the separation device
in a configuration for further processing the clarified bioprocess
fluid.
[0006] In another embodiment, a system for isolating a target
molecule from a bioprocess fluid includes a bioreactor, a
separation device fluidically coupled to the bioreactor at an inlet
of the separation device and configured to receive bioprocess fluid
from the bioreactor and to separate a least a portion of particles
from the bioprocess fluid to generate a substantially clarified
bioprocess fluid, wherein the separation device includes a
plurality of parallel mesofluidic channels for separation of the
particles, and wherein each mesofluidic channel of the plurality of
mesofluidic channels includes a height within a range of 2
millimeters to 20 millimeters, and one or more additional
purification subsystems fluidically coupled to an outlet of the
separation device and configured for further processing of the
clarified bioprocess fluid, wherein the additional purification
subsystems include chromatographic separation, secondary depth
filtration, a polishing membrane, or any combination thereof.
BRIEF DESCRIPTION OF THE DRAWINGS
[0007] These and other features, aspects, and advantages of the
present disclosure will become better understood when the following
detailed description is read with reference to the accompanying
drawings in which like characters represent like parts throughout
the drawings, wherein:
[0008] FIG. 1 illustrates a schematic diagram of an embodiment of a
bioprocessing system including a separation device, in accordance
with aspects of the present disclosure;
[0009] FIG. 2 illustrates a schematic representation of a side view
of an embodiment of the separation device of FIG. 1, in accordance
with aspects of the present disclosure;
[0010] FIG. 3 illustrates a schematic representation of a side view
of an embodiment of the separation device of FIG. 2 showing the
separation device at an angle, in accordance with aspects of the
present disclosure;
[0011] FIG. 4A illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
2 showing an inlet and outlet configuration, in accordance with
aspects of the present disclosure;
[0012] FIG. 4B illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0013] FIG. 4C illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0014] FIG. 4D illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0015] FIG. 4E illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0016] FIG. 4F illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0017] FIG. 4G illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0018] FIG. 4H illustrates a schematic cut away representation of a
perspective view of an embodiment of the separation device of FIG.
4A showing another inlet and outlet configuration, in accordance
with aspects of the present disclosure;
[0019] FIG. 5 illustrates a schematic representation of a side view
of an embodiment of a modular separation device including multiple
of the separation devices of FIG. 2, in accordance with aspects of
the present disclosure;
[0020] FIG. 6 illustrates a schematic representation of an
embodiment of alternating bioprocessing system including multiple
of the separation devices of FIG. 2, in accordance with aspects of
the present disclosure;
[0021] FIG. 7 is a flow chart of an embodiment of a method for
separating particles from a fluid utilizing the separation device
of FIG. 2, in accordance with aspects of the present
disclosure;
[0022] FIG. 8 illustrates a schematic representation of a
perspective view of an additional embodiment of a separation device
of FIG. 1, in accordance with aspects of the present
disclosure;
[0023] FIG. 9 illustrates a schematic representation of a partially
exploded view of an embodiment of the separation device of FIG. 8
showing layers of the separation device, in accordance with aspects
of the present disclosure;
[0024] FIG. 10 illustrates a schematic representation of a
perspective view of the layers at an inlet of the separation device
of FIG. 9, in accordance with aspects of the present
disclosure;
[0025] FIG. 11 illustrates a schematic representation of a
perspective view of the layers at an outlet of the separation
device of FIG. 9; and
[0026] FIG. 12 illustrates a schematic representation of a top view
of the separation device of FIG. 9, in accordance with embodiment
of the present disclosure.
DETAILED DESCRIPTION
[0027] One or more specific embodiments will be described below. In
an effort to provide a concise description of these embodiments,
not all features of an actual implementation are described in the
specification. It should be appreciated that in the development of
any such actual implementation, as in any engineering or design
project, numerous implementation-specific decisions must be made to
achieve the developers' specific goals, such as compliance with
system-related and business-related constraints, which may vary
from one implementation to another. Moreover, it should be
appreciated that such a development effort might be complex and
time consuming, but would nevertheless be a routine undertaking of
design, fabrication, and manufacture for those of ordinary skill
having the benefit of this disclosure.
[0028] In some embodiments discussed herein, a separation device
may be used for harvesting or clarifying cell culture fluid in a
biopharmaceutical process. In such processes, the target substance
to be recovered from the fluid containing particles such as cells
may be a clarified fluid, the separated particles, or a combination
thereof. With the foregoing in mind, FIG. 1 illustrates a
bioprocessing system 180 including a separation device 196 for
separating and recovering a clarified base fluid, separated
particles, or a combination thereof.
[0029] The bioprocessing system 180 may include a bioreactor 182 in
which a biological reaction or process is carried out, or any other
device or system that facilitates a biologically active
environment. In some embodiments, after a reaction has taken place
within the bioreactor 182, an unclarified solution of a base fluid
containing cells and/or other dispersed particulates may be flowed
from the bioreactor 182 to the separation device(s) 196. The device
196 may be used to separate the cells and/or other particulates out
of the base fluid. As such, as the solution is flowed through the
separation device at a defined flow rate, the device 196 may trap
or contain the cells and/or other particulates, such as cells,
aggregated cells, adhered cells on carriers, diatomaceous earth,
resin beads, or a combination thereof, that fall out of the
solution to generate a substantially clarified fluid, as discussed
in greater detail with respect to FIG. 2, which may contain the
target of the bioprocess. The clarified fluid may contain cells,
biotherapeutically active products, proteins (e.g. antibodies),
viruses, vaccines, deoxyribonucleic acid (DNA), ribonucleic acid
(RNA), or a combination thereof. In some embodiments, the clarified
fluid may exit the device 196 and may be flowed through one or more
additional devices 196 (e.g., a series of devices 196) or may be
flowed through one or more additional purification subsystems 184
(also called secondary purification systems) of the bioprocessing
system 180 to further clarify or purify the clarified fluid, such
as a chromatographic separation subsystem 186, a secondary depth
filtration system 188, a polishing membrane subsystem 190 (e.g.,
membrane filtration subsystem), a centrifugation subsystem 191, or
any other purification subsystem.
[0030] The device 196 may be a single-use disposable device, which
may already be sterile and therefore eliminate steps for cleaning
and sterilizing on the biopharmaceutical production floor. It can
e.g. be pre-sterilized by gamma irradiation. The device 196 may
each be made of rigid or flexible material, such as a rigid or
flexible plastic, or may be made of both rigid and flexible
materials. FIGS. 2-5 show separation devices with a relatively
rigid structure, while the devices illustrated below in FIG. 7-11
show separation devices with a relatively flexible structure. The
material used to form some or all of the separation device body or
interior may be any high density plastic or polymer, such as high
density polyethylene, polypropylene, or ethylene vinyl acetate
copolymers.
[0031] In some embodiments, if the cells and/or other particulates
that sediment out of the solution within the device 196 are the
intended product of the bioprocess using the bioprocessing system
180, the cells and/or other particulates may be recovered from the
device 196. Once the unclarified solution is flowed through the
device 196 such that the cells and/or other particulates sediment
from the solution, and before a terminal retention capacity of the
device is reached, a common or separate fluidic conduit fluidically
coupled to an inlet of the device 196 may be operated to flush out
product contained in the device to improve product recovery and
increased product yield.
[0032] In some embodiments, if the cells and/or other particulates
that sediment out of the solution within the device 196 are the
intended product of the bioprocess using the bioprocessing system
180, the cells and/or other particulates may be recovered from the
device 196. Once the unclarified solution is flowed through the
device 196 such that the cells and/or other particulates sediment
from the solution, and before a terminal retention capacity of the
device is reached, a common or separate fluidic conduit fluidically
coupled to an outlet of the device 196 may be operated to reverse
the flow within the device 196 from the outlet to an inlet of the
device. The reverse flow may return the cells and/or other
particulates retained within the device 196 (e.g., retentate) to
the bioreactor 182 and/or a separate sterile container 192
fluidically coupled to the device 196 and/or the bioreactor
182.
[0033] In some embodiments, if the cells and/or other particulates
that sediment out of the solution within the device 196 are the
intended product of the bioprocess using the bioprocessing system
180, the cells and/or other particulates may be recovered from the
device 196. Once the unclarified solution is flowed through the
device 196 such that the cells and/or other particulates sediment
from the solution, and before a terminal retention capacity of the
device is reached, the fluid of the retained cells and/or other
particulates may be exchanged with an alternate compatible fluid,
such as a buffer or media. Engagement of a common or separate
fluidic conduit fluidically coupled to an outlet of the device 196
may be operated to reverse the flow using the same or alternate
compatible fluid within the device 196 from the outlet to an inlet
of the device. The reverse flow may return the cells and/or other
particulates retained within the device 196 (e.g., retentate) to
the bioreactor 182 and/or a separate sterile container 192
fluidically coupled to the device 196 and/or the bioreactor
182.
[0034] Additionally or alternatively, in some embodiments, the
bioprocessing system 180 may be operated in a manner that may cause
the cells and/or other particulates within the unclarified solution
to sediment out of the unclarified solution more rapidly within the
device 196 and thus, increase the efficiency of the device 196 and
the bioprocessing system 180 as a whole. For example, in some
embodiments, the pH of the solution may be adjusted prior to
entering the device 196. A fluid or other material may be added vi
an inlet to the bioreactor 182 to adjust the pH, which may be
monitored. The pH may be lowered to, for example, pH 4.5-5 before
being flowed through the device 196. A lower pH may cause the cells
and/or other particles in the solution to accumulate (e.g.,
flocculate) into large aggregates, allowing the cells and/or other
particles to fall out of the solution more rapidly within the
separation device 196 to produce a more clarified fluid product.
The pH of the clarified fluid from the device 196 may be
neutralized back to the starting pH of the solution, for example pH
7, by addition of a base into the device 196 or an additional
storage bag 194, before recovery or before being further clarified
using one or more of the additional purification subsystems 184. In
some embodiments, additional particles or additives may be added to
the cell culture fluid (e.g., the unclarified solution) to aid in
improving settling performance of the device 196. For example, a
flocculant, such as poly(diallyldimethylammonium chloride) (PDADMC)
or diatomaceous earth (DE), may be added to the cell culture fluid.
The flocculant may aggregate the particles, as well as other debris
in the cell culture fluid, into larger particles, which may settle
faster based on the density difference between the larger particles
and the fluid of the cell culture fluid. This in turn may improve
separation performance of the device 196, especially at higher
particle densities (e.g., cell densities). In some embodiments, the
larger particles may be recovered from the device 196. In such
embodiments, a net charge of the added flocculant may also be used
to capture charged species in the cell culture fluid, such as DNA
or host-cell protein (HCP).
[0035] FIG. 2 illustrates an embodiment of the separation device
196 (e.g., a non-inclined settler configured to be operated in a
horizontal or substantially horizontal orientation) that may be
used to separate the cells and/or particles from a base fluid of
the solution. In preferred embodiments, the device 196
operationally functions through balancing the time a particle
resides in the device 196 as it flows through against the time it
takes for a particle to settle by gravity in the device to achieve
a settling efficiency. Specifically, if the flow rate of the
particle containing fluid through the device of a given volume
allows for a residence time that is greater than the particle
settling time, the particle will be captured. If the flow rate of
the particle containing fluid results in a residence time less than
the particle settling time, the particle will not be efficiently
retained. The residence time is simply calculated by dividing the
device volume by flow rate.
[0036] The device 196 may receive an input of a cell culture fluid
198 (e.g., the unclarified solution containing cells and/or other
particles suspended in a base fluid), such as a cell suspension, or
other fluid containing particles, via a fluid inlet 200. The device
196 may receive the cell culture fluid 198 from the bioreactor 182,
or other source, at a particular flow rate. The device 196 may be
an assisted gravity settler used to separate particles, such as
cells and/or other particles, from the cell culture fluid 198 to
allow for recovery of a clarified fluid 202 via a fluid outlet 204
of the device 196. A target product of the harvest process may be
contained within the recovered clarified fluid 202.
[0037] A body 205 of the device 196 may include a fluid inlet
manifold 206, multiple mesofluidic channels 208 (e.g., channels
having heights within the millimeter to centimeter range), and a
fluid outlet manifold 210. The fluid inlet manifold 206 may couple
the fluid inlet 200 to the multiple mesofluidic channels 208. The
device 196 may include any number of mesofluidic channels 208
(e.g., 2, 3, 4, 5, 6, etc.) arranged in a stacked or parallel
configuration, as shown in the illustrated embodiment, providing a
series of stacked mesofluidic channels in a separation portion 211
of the body 205 of the device 196. The stacked configuration of the
mesofluidic channels 208 allows for increased surface area for the
particles of the cell culture fluid 198 to settle, while also
allowing the cell culture fluid 198 to have an increased volume to
move through, which may allow the device 196 to efficiently process
increased volumes of cell culture fluid 198. Thus, the device 196
may sufficiently clarify the cell culture fluid 198 at varying
volumes having a high cell density (e.g., >20 million cells/mL).
The device 196 may have a capacity of 2,000 L, 4,000 L, or up to
10,000 L.
The mesofluidic channels 208 may range in height 212 from
millimeter to centimeter heights, such as between 2 mm and 20 mm (2
cm), or between 2 mm and 10 mm, or between 2 mm and 6 mm, in height
212. All of the mesofluidic channels 208 of the device 196 may have
the same height 212, or in some embodiments, the mesofluidic
channels 208 may vary in height 212 within the millimeter to
centimeter range. The mesofluidic channels 208 are each disposed
between and fluidically coupled to the fluid inlet manifold 206 and
the fluid outlet manifold 210. As such, each mesofluidic channel
208 may be coupled to the fluid inlet manifold 206 at a channel
inlet 214 of the mesofluidic channel 208 and coupled to the fluid
outlet manifold at a channel outlet 216. The fluid inlet manifold
206 and the fluid outlet manifold 210 may be disposed such that the
manifolds 206, 210 are positioned perpendicular to the flow path of
the mesofluidic channels 208. The fluid inlet manifold 206 and the
fluid outlet manifold 210 may each be sized such that the capacity
of the fluid inlet manifold 206 and the capacity of the fluid
outlet manifold 210 are greater than the capacity of each
mesofluidic channel 208 in order to distribute and collect the cell
culture fluid 198 from the mesofluidic channels 208. As such, the
device 196 may, in certain embodiments, be devoid of microfluidic
features. Consequently, the height 212 of the mesofluidic channels
208 from millimeters up to two centimeters may increase the total
capacity of the device 196.
[0038] In operation, the cell culture fluid 198 may be provided to
the device 196 at a particular flow rate. This is the flow rate
that the cell culture fluid 198 passes through the mesofluidic
channels 208. The cell culture fluid 198 may enter the fluid inlet
manifold 206 and may be distributed substantially evenly between
the multiple mesofluidic channels 208. As the cell culture fluid
198 traverses the mesofluidic channels 208, a density difference
between the particles contained in the cell culture fluid 198
(e.g., cells) and the surrounding fluid of the cell culture fluid
198 may cause the particles to settle and collect on a lower
interior surface 218 of each mesofluidic channel 208. Settling of
the particles of the cell culture fluid 198 on the lower interior
surface of the mesofluidic channels 208 may be further caused by a
separation force 220 acting on the higher density particles within
the cell culture fluid 198. The separation force 220 may be an
ambient gravitational force, such that no separate or additional
force is needed to cause settling of the particles within the
mesofluidic channels 208. Settling of the particles of the cell
culture fluid 198 within the mesofluidic channels 208 as the cell
culture fluid 198 flows through the device 196 may yield a
substantially clarified fluid layer 202 (e.g. >80% particle
removal) of the cell culture fluid 198 that can be recovered as an
output via the fluid outlet 204. As such, a product, such as a
protein, of the biopharmaceutical process within the fluid layer
202 of the cell culture fluid 198 may be recovered.
[0039] As used herein, the residence time describes the amount of
time that it takes for the cell culture fluid 198 to traverse the
device 196 from the fluid inlet to the fluid outlet of the device
196, and as such, the amount of time that the cell culture fluid
198 may be within the mesofluidic channels 208 to allow for the
particles of the cell culture fluid 198 to sediment. The residence
time of the device 196 is defined as the ratio of the total volume
of the device 196 to the flow rate of the cell culture fluid 198
through the device 196. The residence time for the device 196 may
range from around 10 minutes to 40 minutes or within smaller
ranges, such as from 16 minutes to 30 minutes, from 23 minutes to
27 minutes, or any other suitable range or combination of such
ranges. This range of residence time of the cell culture fluid 198
within the device 196 allows for settling of the particles to
provide a substantially clarified fluid layer 202 within an
efficient separation time period (e.g., less than 8 hours
processing time for 2,000 L).
[0040] Therefore, if a target volume of the cell culture fluid 198
to be processed and a capacity of the device 196 are known, the
flow rate of the cell culture fluid 198 can be set or adjusted to
provide a target residence time (e.g., 24 minutes, 25 minutes, 26
minutes, and so forth) within the above ranges. The residence time
within the above ranges may provide efficient settling of the
particles of the cell culture fluid 198, which may be a high cell
density cell culture fluid, and clarifying of the fluid layer 202
of the cell culture fluid 198 within a manageable time period, as
discussed in greater detail with reference to Tables 4 and 5. As
such, the device 196 may be scalable to a target volume to be
processed and/or to a particular harvest application.
[0041] The particles of the cell culture fluid 198 settle to the
lower interior surface 218 as the cell culture fluid 198 traverses
the mesofluidic channels 208 due to the density difference between
the particles and the fluid of the cell culture fluid and the
separation force 220 (e.g., ambient gravitational force).
Additionally, the device 196 may be utilized to recover the
clarified fluid layer 202 of the cell culture fluid 198. In
preferred embodiments, the device 196 does not include any
microporous or microfluidic features. Further, the device 196 may
be a single use device that may be disposed of after processing of
the cell culture fluid 198, as the clarified fluid layer 202 is
recovered via the outlet 204 of the device 196.
[0042] FIG. 3 illustrates the separation device 196 positioned at
an angle 230 relative to a work surface 232 and to a source 234 of
the separation force 220. In some embodiments, during processing of
the cell culture fluid 198, the device 196 may be positioned
substantially parallel (i.e., non-inclined) to the work surface 232
and the source 234 of the separation force 220, or at a 0.degree.
angle or at about a 0.degree. angle (e.g., 0.degree..+-.5.degree.)
relative to the work surface 232, as illustrated in FIG. 2. That
is, the work surface 232 may be a surface that is oriented
perpendicular to the separation force 234 (e.g., gravitational
force). Typically, the work surface 232 is a horizontal surface. In
some embodiments, during processing of the cell culture fluid 198,
the device 196 may be positioned at the angle 230 relative to the
work surface 232 and the source 234 of the separation force 220, as
illustrated in FIG. 3. The angle 232 may position or orient the
device such that the channel inlets 214 of the mesofluidic channels
208 are positioned lower than the channel outlets 216.
[0043] The device 196 may operate to substantially separate the
particles from the fluid layer 202 of the cell culture fluid 198
while not positioned at the angle 230 (e.g., at a 0.degree. angle
or about a 0.degree. angle). The density difference between the
particles and the fluid layer 202 of the cell culture fluid and the
separation force 220 may act to sufficiently separate the particles
from the fluid layer 202 even in the absence of an incline. In
embodiments where the device 196 is positioned at the angle 230,
the angle 230 may provide the benefit of helping to evacuate air
from the device 196 and not as a force for operation of the device
196.
[0044] The angle 230 may be an angle between substantially
0.degree.-30.degree., or an angle between substantially
0.degree.-10.degree., such as 10.degree., 5.degree., or about
0.degree. (e.g., 0.degree..+-.5.degree.). As such the separation
device 196 may be referenced herein as a non-inclined settler. In
contrast, inclined settlers are dependent upon the Boycott effect,
which may require operation angles around 30.degree. or greater to
achieve sedimentation. In some embodiments, the device 196 may be
positioned at the angle 230 throughout the separation process.
However, in some embodiments, the device 196 may be intermittently
or periodically tilted to the angle 230 to evacuate air from the
mesofluidic channels 208 to increase separation efficiency of the
device 196.
[0045] FIGS. 4A-4H illustrate embodiments of different
configurations of the fluid inlet(s) 200, the fluid inlet
manifold(s) 206, the fluid outlet manifold(s) 210, and the fluid
outlet(s) 204 of the device 196. In certain configurations of the
device 196, the device 196 may include one or more fluid inlets 200
and one or more fluid outlets 204 (e.g., 1, 2, 3). Additionally,
the device 196 may include one or more of the fluid inlet manifold
206 to couple the fluid inlet(s) 200 to the channel inlets 214, one
or more of the fluid outlet manifold 210 to couple the fluid
outlet(s) 204 to the channel outlets 216, or both the fluid inlet
manifold(s) 206 and the fluid outlet manifold(s) 210. Further, in
some configurations, the device 196 may include one or more lateral
inlet channels 236 that may distribute the cell culture fluid from
the one or more fluid inlet manifolds 206 between the channel
inlets 214 and/or one or more lateral outlet channels 238 that may
collect the clarified fluid layer 202 from the channel outlets 216
and distribute the clarified fluid layer 202 to the one or more
fluid outlet manifolds 210.
[0046] FIG. 4A illustrates a configuration of the device 196 having
multiple fluid inlet manifolds 206, each coupling one of the fluid
inlets 200 to the one or more channel inlets 214 of the mesofluidic
channels 208 of the separation portion 211. The cell culture fluid
198 flowed into the multiple fluid inlets 200 is distributed
between the one or more channel inlets 214 via the multiple fluid
inlet manifolds 206. Additionally, the device 196 includes multiple
fluid outlet manifolds 210, each coupled to the one or more channel
outlets 216 of the mesofluidic channels 208. The clarified fluid
layer 202 produced as the cells and/or other particles fall out of
the cell culture fluid 198 as it is flowed through the device 196
exits the mesofluidic channels 208 via the multiple fluid outlet
manifolds 210 and exits the device 196 via the respective fluid
outlets 204. Multiple fluid inlets 200 and fluid outlets 204 may
allow for an increased flow rate of the cell culture fluid 198
through the device, thus increasing the volume of cell culture
fluid 198 that the device 196 may efficiently process within a
particular time period.
[0047] FIG. 4B illustrates a configuration of the device 196 having
a single fluid inlet 200 coupled to a single fluid inlet manifold
206, as well as a single fluid outlet 204 coupled to a single fluid
outlet manifold 210. Additionally, the fluid inlet manifold 206 is
coupled to one or more lateral inlet channel 236. The lateral inlet
channel 236 may be disposed perpendicular to the fluid inlet
manifold 206 such that the cell culture fluid 198 that is flowed
into the fluid inlet manifold 206 is distributed to each of the
channel inlets 214 via the lateral inlet channel 236. Further, the
channel outlets 216 are coupled to the fluid outlet manifold 210
via the lateral outlet channel 238. The lateral outlet channel 238
may be disposed perpendicular to the mesofluidic channels 208 such
that the clarified fluid layer 202 from each channel outlet 216 is
collected in the lateral outlet channel 238 and distributed to the
single fluid outlet manifold 210 to exit the device 196. Inclusion
of the lateral inlet channel 236 and/or the lateral outlet channel
238 may provide for minimization of the profile of the device 196
while still allowing for substantially equal distribution of the
cell culture fluid 198 at a particular flow rate through the device
196.
[0048] FIG. 4C illustrates a configuration of the device 196 having
multiple fluid inlet manifolds 206 and fluid outlet manifolds 210
coupled to the lateral inlet channel 236 and the lateral outlet
channel 238, respectively. As with the configuration shown in FIG.
4B, the lateral inlet channel 236 may be disposed perpendicular to
the fluid inlet manifold 206 such that the cell culture fluid 198
that is flowed into the fluid inlet manifold 206 is distributed to
each of the channel inlets 214 via the lateral inlet channel 236.
Additionally, the lateral outlet channel 238 may be disposed
perpendicular to the mesofluidic channels 208 such that the
clarified fluid layer 202 from each channel outlet 216 is collected
in the lateral outlet channel 238 and distributed to the single
fluid outlet manifold 210 to exit the device 196. In some
configurations, such as the configuration shown in FIG. 4C, the
fluid inlet manifold(s) 206 may be disposed directly across from,
or in line with, the fluid outlet manifold(s) 210 on opposite ends
240 of the device 196.
[0049] FIG. 4D illustrates a configuration of the device 196 having
a single fluid inlet manifold 206 and a single fluid outlet
manifold 210 coupled to the lateral inlet channel 236 and the
lateral outlet channel 238, respectively. The configuration shown
in FIG. 4D is similar to that shown in 4B, except for the position
of the fluid inlet manifold 206 and the fluid outlet manifold 210
about the ends 240 relative to a side 242 of the device 196. While
both FIGS. 4B and 4D show configurations where the fluid inlet
manifold 206 and the fluid outlet manifold 210 are disposed
directly across from each other on the opposite ends 240 of the
device, FIG. 4D shows the fluid inlet manifold 206 and the fluid
outlet manifold 210 disposed adjacent to one of the sides 242
rather than disposed at a center position between the sides 242 of
the device, as shown in FIG. 4B.
[0050] FIG. 4E illustrates a configuration of the device 196 having
a single fluid inlet 200 and fluid inlet manifold 206, which is
coupled to the channel inlets 214 via the lateral inlet channel
236. Additionally, the device 196 includes multiple fluid outlets
204 each coupled to the one or more channel outlets 216 via a
respective one of multiple fluid outlet manifolds 210. In an
opposite configuration, FIG. 4F illustrates a configuration of the
device 196 having multiple fluid inlets 200 each coupled to the one
or more channel inlets 214 via a respective one of multiple fluid
inlet manifolds 206. Additionally, the device 196 shown in FIG. 4F
includes a single fluid outlet 204 and fluid outlet manifold 210
coupled to the one or more channel outlets via the lateral outlet
channel 238. In both configurations, the single fluid inlet
manifold 206 shown in FIG. 4E and the single fluid outlet manifold
210 shown in FIG. 4F are each disposed adjacent to a side 242 of
the device 196, rather than at a center position between each side
242 of the device 196. Further, as shown in both configurations of
FIGS. 4E and 4F, when multiple fluid inlet manifolds 206 and/or
multiple fluid outlet manifolds 210 are present, they may be
disposed equally spaced between the sides 242 of the device
196.
[0051] FIG. 4G illustrates a configuration of the device 196 having
multiple fluid inlets 200 each coupled to the one or more channel
inlets 214 of the device 196 via a respective one of multiple fluid
inlet manifolds 206. Additionally, the device 196 of FIG. 4G
includes multiple fluid outlets 204 and fluid outlet manifolds 210
coupled to the one or more channel outlets 216 via the lateral
outlet channel 238. While there are multiple fluid inlet manifolds
206 and multiple fluid outlet manifolds 210, the amount of each
present on the device 196 does not correspond. For example, the
device 196 of FIG. 4G includes three fluid inlet manifolds 206 and
only two fluid outlet manifolds 210. In such configurations, the
fluid inlet manifolds 206 and the fluid outlet manifolds 210 may
each be equally spaced between the sides 242 of the device 196,
however the fluid outlet manifolds 210 may not be disposed directly
across from the fluid inlet manifolds 206 on respective ends 240 of
the device 196.
[0052] FIG. 4H illustrates a configuration of the device 196 having
a single fluid inlet 200 and a respective single fluid inlet
manifold 206, as well as a single fluid outlet 204 and a respective
single fluid outlet manifold 210. Additionally, the fluid inlet
manifold 206 is coupled to the one or more channel inlets 214 via
the lateral inlet channel 236 and the fluid outlet manifold 210 is
coupled to the one or more channel outlets 216 via the lateral
outlet channel 238. In the configuration shown in FIG. 4H, the
fluid inlet manifold 206 is positioned along an end 240 adjacent to
one side 242 of the device 196. The fluid outlet manifold 210 is
positioned along an opposite end 240 adjacent to an opposite side
242 of the device 196, such that the fluid inlet manifold 206 and
the fluid outlet manifold 210 are not disposed directly across from
each other.
[0053] The alternative configurations of the device 196 shown in
FIGS. 4A-4H illustrate non-limiting examples of the device 196 and
are not meant to illustrate all possible configurations. The device
196 may include any suitable quantity of fluid inlets 200, fluid
inlet manifolds 200, fluid outlets 204, fluid outlet manifolds 210,
and may or may not include the lateral inlet channel 236 and/or the
lateral outlet channel 238. Varying amounts of fluid inlets 200 and
fluid outlets 204, as well as of the fluid inlet manifolds 206 and
the fluid outlet manifolds 210, may allow customization or
selection of a pressure drop across the device 196, and thus, may
vary the flow rate of the cell culture fluid 198 through the device
196. This may allow for customization of the device 196 based on a
target application. The fluidic path between the fluid inlet 200
and the fluid outlet 204 of the device 196 may be unidirectional in
a linear or serpentine configuration. Additionally, inclusion of
the lateral inlet channel 236 and/or the lateral outlet channel 238
may provide for minimization of the profile of the device 196 while
still allowing for substantially equal distribution of the cell
culture fluid 198 at a particular flow rate through the device
196.
[0054] FIG. 5 illustrates an embodiment of a modular separation
device 246 including two or more of the separation devices 196 as
modular subunits. In the illustrated embodiment, the one or more
fluid inlet manifolds 206 and the one or more fluid outlet
manifolds 210 of each device 196 may be coupled, respectively, such
that a length of the fluid inlet manifold 206 and the fluid outlet
manifold 210 is increased forming the fluid inlet manifold 206 and
the fluid outlet manifold 210 for the modular separation device
246. As each device 196 includes one or more mesofluidic channels
208 coupled between the fluid inlet manifold 206 and the fluid
outlet manifold 210, the modular separation device 246 will include
an increased number of the mesofluidic channels 208 as additional
device 196 are added.
[0055] Use of the devices 196 as modular subunits may provide the
modular separation device 246 with the particular capacity to allow
for efficient processing of the volume of a target cell culture
fluid 198. In some embodiments, the devices 196 (e.g., modular
subunits) may allow for increasing or decreasing the number of
mesofluidic channels 208, varying the position and/or amount of the
fluid inlet(s) 200 and/or the fluid outlet(s) 204, varying the
presence or absence of the fluid inlet manifold 206 and/or the
fluid outlet manifold 210, or any combination thereof. Modularity
of the modular separation device 246 using the devices 196 may
allow for use of the devices 196 based on a target application.
[0056] In some embodiments, the devices 196, including a device 296
discussed below with reference to FIGS. 8-12, and the modular
separation devices 246 can be operated in an alternating
arrangement, where one or more device is fluidically coupled to the
cell culture fluid to produce a substantially clarified product,
while an additional one or more devices are fluidically coupled to
recover the cells and/or other particulates to the reactor or
separate container. Such a process allows for semicontinuous or
continuous processing of cell culture fluid while recovering the
cells and/or other particulates. Additionally, such an arrangement
may allow for increased system processing capacity. As such, FIG. 6
illustrates an alternating bioprocess system 250 having two of the
devices 196 arranged for operation in parallel. Although discussed
in terms of two of the device 196, it should be understood that the
alternating bioprocess system 250 may be applicable to more than
two devices 196 and/or may include the modular separation devices
246.
[0057] In the alternating bioprocess system 250, the devices 196
may be arranged in a parallel operational configuration, each
fluidically coupled by the respective fluid inlet 200 the
bioreactor 182 or other source of the cell culture fluid 198. In
some embodiments, an inlet pump 252 may be used to pump the cell
culture fluid 198 to the fluid inlets 200 of the device 196. In
operation, the cell culture fluid may be flowed through a first
device 254 of the devices 196, while flow is blocked to a second
device 256 of the devices 196. The cell culture fluid may be flowed
through the mesofluidic channels 208 of the first device 254,
within which the cells and/or other particulates may sediment out
of the cell culture fluid. Before the terminal capacity of the
first device 254 is reached, the flow of the cell culture fluid
from the bioreactor may be routed to the second device 256 and
blocked from flowing into the first device 254.
[0058] In some embodiments, if the cells and/or other particulates
that sediment out of the cell culture fluid are an intended product
of the bioprocess, the first device 254 may be washed of the
settled cells and/or particulates using the same fluid or an
alternate compatible fluid 258, such as a buffer or purge air. The
fluid of the retained cells and/or other particulates may be
exchanged with the same or alternate compatible fluid 258 using a
common or separate fluidic conduit fluidically coupled to the
outlet of the first device 254, such that flow is reversed using
the same or alternate compatible fluid within the device 254 from
the fluid outlet 204 to the fluid inlet 200 of the first device
245. In some embodiments, the alternating bioprocess system 250 may
include a purge pump 260 may be used to create the reverse flow of
the alternate compatible fluid 258 into the fluid outlet 204 of the
first device 254. The reverse flow may return the cells and/or
other particulates retained within the first device 254 (e.g.,
retentate) to the bioreactor 182 and/or a separate sterile
container fluidically coupled to the device 196 and/or the
bioreactor 182 via collection line 262. The first device 254 may
then be ready to be used for additional separation. In some
embodiments, the first device 254 may be washed by flowing the
alternate compatible fluid 258 (e.g., buffer) through the first
device 254 using a common or separate fluidic conduit fluidically
coupled to the fluid inlet 200 of the first device 254. A buffer
pump 264 may be used to flow the alternate compatible fluid 258
through the first device 254.
[0059] The cell culture fluid from the bioreactor 182 may be flowed
through the second device 256 while the cells and/or other
particulates retained within the first device 254 are removed.
Before the terminal capacity of the second device 256 is reached,
the flow of the cell culture fluid from the bioreactor may be
routed to the first device 254 and blocked from flowing into the
second device 256. As such, the second device 256 may then be
washed of the retained cells and/or other particulates. Multiple
valves 266 may be used throughout the alternating bioprocess system
250 to control the flow of the cell culture fluid, the clarified
fluid, and the alternate compatible fluid. Thus, the first and
second devices 254, 256 may be used in an alternating arrangement
to increase efficiency and separation capacity by allowing for
semicontinuous or continuous processing of the cell culture
fluid.
[0060] FIG. 7 is a flow chart of an embodiment of a method 270 of
clarifying the cell culture fluid 198 using the device 196. Because
of the single use, disposable nature of the device 196, which may
have a capacity of 2,000 L, 4,000 L, or up to 10,000 L, in some
embodiments, the device 196 may be sterilized (e.g., gamma
sterilized) and/or packaged prior to use. At step 272, the device
196 may be provided having a particular capacity to allow for
efficient processing of a target cell culture fluid 198 volume. As
previously discussed, the device 196 may include multiple
mesofluidic channels 208 regularly stacked and arranged between the
fluid inlet manifold 206 and the fluid outlet manifold 210. The
quantity and size (e.g., height) of the mesofluidic channels 208
may account for the particular capacity of the device 196. In some
embodiments, the device 196 may be modular such that it includes
modular subunits. In such embodiments, the modular subunits may be
used to provide the device 196 with the particular capacity to
allow for efficient processing of the target cell culture fluid 198
volume. In some embodiments, the modular subunits may allow for
increasing or decreasing the number of mesofluidic channels,
varying the position and/or amount of the fluid inlet(s) 200 and/or
the fluid outlet(s) 204, varying the presence or absence of the
fluid inlet manifold 206 and/or the fluid outlet manifold 210, or
any combination thereof. In some embodiments, the device 196 may be
provided at a substantially 0.degree. angle 230 (e.g.,
0.degree..+-.5.degree.) relative to the work surface 232 and the
source 234 of the separation force 220. However, in some
embodiments, the device 196 may be provided at an angle 230 within
a range of 1.degree.-29.degree. or between 1.degree.-10.degree..
The angle 230 may not be necessary for operation of the device, for
example to create a separation force, but may only be used to
evacuate air from the device 196.
[0061] Next, at step 274, the unprocessed cell culture fluid 198
may be provided from a source, such as a bioreactor, as a cell
suspension containing particles (e.g., cells) suspended in the
fluid layer 202. The unprocessed cell culture fluid 198 may contain
any density of particles, including a high density of particles,
such as within a cell density range of 1-200 million particles/mL
(e.g., cells/mL). In some embodiments, additional particles may be
added to the cell culture fluid 198 to aid in improving settling
performance of the device 196. For example, a flocculant, such as
poly(diallyldimethylammonium chloride (PDADMC), may be added to the
cell culture fluid 198. The flocculant may aggregate the particles,
as well as other debris in the cell culture fluid 198, into larger
particles, which may settle faster based on the density difference
between the larger particles and the fluid of the cell culture
fluid 198. This in turn may improve separation performance of the
device 196, especially at higher particle densities (e.g., cell
densities). In some embodiments, the particles may be recovered
from the device 196. In such embodiments, a charge of the added
flocculant may also be used to capture charged species in the cell
culture fluid 198, such as DNA. In some embodiments, ion exchange
or affinity beads may be added to the cell culture fluid 198 to
capture a product or protein to be recovered. The beads may settle
within the device 198 and the beads and the product may be
recovered from the device. Therefore, in some embodiments, the
device 198 may include a port for recovering the settled
particles.
[0062] Next, at step 276, the unprocessed cell culture fluid 198
may be flowed through the mesofluidic channels 208 of the device
198 at a particular flow rate. The particular flow rate at which
the cell culture fluid 198 is flowed through the device 198 may be
determined based on the capacity of the device 198 in order to
provide a residence time (e.g. ratio of device capacity to the flow
rate) within the above described range to increase performance and
efficiency of the device 198. Next, at step 278, at least a portion
of the particles within the cell culture fluid 198 may be separated
from the fluid layer 202 of the cell culture fluid 198 over the
residence time as the cell culture fluid 198 flows through the
mesofluidic channels 208 of the device 198. As previously
discussed, the particles may settle to the lower interior surface
218 of the mesofluidic channels due to a density difference between
the particles and the fluid layer 220 of the cell culture fluid 198
and the separation force 220. In some embodiments, the separation
force 220 may be an ambient gravitational force. The device 196 may
allow for separation and retention within the device 196 of up to
approximately 90%-99.9% of the particles within the cell culture
fluid 198.
[0063] Next, at step 280, the stream of the fluid layer 202
substantially devoid of the particles may be collected via the
fluid outlet 204 of the device. The collected clarified fluid layer
202 may contain the target product of harvest process. Next, at
step 282, if the target product is collected in the clarified fluid
layer 202, the device 196 may be discarded, as the device 196 may
be a single use, disposable separation device. Therefore, the
device 196 may provide a single use, disposable separation device
that may allow for efficient clarification of a cell culture fluid
containing a wide particle density range. Additionally or
alternatively, in some embodiments, as previously discussed, the
flow through the separation device 196 may be reversed before a
terminal capacity of the device 196 is reached, at step 284.
Reversing the flow through the device 196 may allow for return of
the cells and/or other particles that fell out of the cell culture
fluid 198 as it was flowed through the device 196 to the bioreactor
or to a separate container for recovery. While the method 250 is
described for use of the device 196, it should be understood that
the method 250 may also be used for the embodiments of the
separation device discussed below with regard to FIGS. 8-12.
[0064] FIG. 8 illustrates an embodiment of a separation device 296
made from a flexible material (preferably fabricated with a gamma
compatible polymer, e.g. polyethylene or ethylene-vinyl acetate
copolymer), such that the separation device 296 forms a bag
configuration having one or more channels for separation of cells
and/or other particles from the cell culture fluid 198. The device
296 may be a single-use device that may be discarded after use for
separation. The device 296 may receive an input of a cell culture
fluid 198 (e.g., the unclarified solution containing cells and/or
other particles suspended in a base fluid) via a fluid inlet 300.
The device 296 may receive the cell culture fluid 198 from the
bioreactor 182, or other source, at a particular flow rate. A body
305 of the device 296 may include one or more fluid inlet manifolds
306, one or more mesofluidic channels 308 (e.g., channels having
heights within the millimeter to centimeter range), and one or more
fluid outlet manifolds 310. The fluid inlet manifold 306 may couple
the fluid inlet 300 to the one or more mesofluidic channels 308.
The device 296 may include any number of mesofluidic channels 308
(e.g., 1, 2, 3, 4, 5, 6, etc.) arranged in a stacked or parallel
configuration providing a series of stacked mesofluidic channels in
a separation portion 311 of the body 305 of the device 296.
[0065] The one or more mesofluidic channels 308 may each range in
height from millimeter to centimeter heights, such as between 2 mm
and 20 mm (2 cm) in height. The one or more mesofluidic channels
308 are each disposed between and fluidically coupled to the fluid
inlet manifold 306 and the fluid outlet manifold 310. The fluid
inlet manifold 306 and the fluid outlet manifold 310 may be
disposed such that the manifolds 306, 310 are positioned
perpendicular to the flow path of the one or more mesofluidic
channels 308. The structure of the device 296, including the fluid
inlet manifold 306 and the fluid outlet manifold 310, may be formed
from perimeter-bonded flexible plastic or polymer layers, as
discussed in greater detail with respect to FIGS. 9-11.
[0066] Similar to the device 196 discussed above, in operation, the
cell culture fluid 198 may be provided to the device 296 at a
particular flow rate. This is the flow rate that the cell culture
fluid 198 passes through the mesofluidic channels 308. The cell
culture fluid 198 may enter the fluid inlet manifold 306 and may be
distributed substantially evenly between the one or more
mesofluidic channels 308. As the cell culture fluid 198 traverses
the one or more mesofluidic channels 308, a density difference
between the cells and/or other particles contained in the cell
culture fluid 198 (e.g., cells) and the surrounding fluid of the
cell culture fluid 198 may cause the cells and/or other particles
to settle and collect on a lower interior surface of each
mesofluidic channel 308.
[0067] Settling of the cells and/or other particles of the cell
culture fluid 198 within the one or more mesofluidic channels 308
may be further caused by the separation force 320 acting on the
higher density particles within the cell culture fluid 198. The
separation force 320 may be an ambient gravitational force, such
that no separate or additional force is needed to cause settling of
the cells and/or other particles within the one or more mesofluidic
channels 308. Settling of the particles of the cell culture fluid
198 within the mesofluidic channels 308 as the cell culture fluid
198 flows through the device 196 may yield the substantially
clarified fluid layer 202 (e.g., substantially cell and/or particle
free fluid layer) of the cell culture fluid 198 that can be
recovered as an output via the fluid outlet 304. As such, a
product, such as a protein, of the biopharmaceutical process within
the fluid layer 202 of the cell culture fluid 198 may be
recovered.
[0068] As noted above, the residence time of the device 296, as
used herein, is defined as the ratio of the total volume of the
device 196, 296 to the flow rate of the cell culture fluid 198
through the device 196, 296. The residence time for the device 296
may range from around 10 minutes to 40 minutes or within smaller
ranges, such as from 16 minutes to 30 minutes, from 23 minutes to
27 minutes, or any other suitable range or combination of such
ranges. This range of residence time of the cell culture fluid 198
within the device 296 allows for efficient settling of the
particles to provide a substantially clarified fluid layer 202
within an efficient separation time period. Therefore, if a target
volume of the cell culture fluid 198 to be processed and a capacity
of the device 296 are known, the flow rate of the cell culture
fluid 198 can be set or adjusted to provide a target residence time
(e.g., 24 minutes, 25 minutes, 26 minutes, and so forth) within the
above ranges. The residence time within the above ranges may
provide efficient settling of the particles of the cell culture
fluid 198, which may be a high cell density cell culture fluid
(e.g., 1 million to 20 million cells/mL), and clarifying of the
fluid layer 202 of the cell culture fluid 198 within a manageable
time period, as discussed in greater detail with reference to
Tables 4 and 5. As such, the device 296 may be scalable to a target
volume to be processed and/or to a particular harvest
application.
[0069] FIG. 9 illustrates a partial exploded view of the separation
device 296 showing two layers 330 used to form the device 296. The
device 296 may be formed from perimeter-bonded layers 330 of
biocompatible film or polymer. Each layer 330 may have a chevron
shape, as shown in the illustrated embodiment, or other polygonal
shape. As such, the layers 330 may be angled toward the fluid inlet
manifold 306 and the fluid outlet manifold 310. Each end 331 of
each layer 330 includes a spacer 332, which may be made of a
thicker material than the layers 330. Some of the spacers 332 may
include a hole 333 through the spaces 332, which is made during
fabrication. The spacers are heat-welded to each end 331 of the
layers 330. The holes 333 of the spacers 332 form manifolds (e.g.,
conduits) when the layers are perimeter-bonded into the device 296,
and the space between the spacers 332 form the mesofluidic channels
308.
[0070] The device 296 may include a bottom layer 334, one or more
intervening layers 336, and a top layer (not shown). The
illustrated embodiment shows the bottom layer 334 bonded along one
side to one intervening layer 336 via a perimeter bond 338. The
bottom layer 336 and the top layer may each include only one spacer
332 having the hole 333, while the intervening layers 336 each
include spacers 332 having the hole 333 on both ends 331 of the
layers 336. The bottom layer 334 may include one spacer 332 with
the hole 333 at one end 331 of the bottom layer 334 and may include
one spacer 332 without the hold 333 at the opposite end 331 of the
bottom layer 334. The top layer may also include one spacer 332
with the hole 333 at one end 331 and may include one spacer 332
without the hold 333 at the opposite end 331, however the spacer
332 including the hole 333 of the bottom layer 334 is on the
opposite end 331 as the spacer 332 including the hole 333 of the
top layer. That is, the bottom layer is oriented 180.degree.
relative to the top layer. This orientation provides for the fluid
inlet manifold 306 and the fluid outlet manifold 310 when the
layers 330 are perimeter-bonded together, such that no flow can be
directed out of the device 296 without first flowing through the
one or more mesofluidic channels 308.
[0071] FIG. 10 illustrates the layers 330 at the end 331 forming
the fluid inlet manifold 306 of the device 296. To form the fluid
inlet manifold 306 when the layers 330 are bonded together via the
perimeter bond 338, the bottom layer 334 contains the spacer 332
having the hole 333 on the end 331 of the device 296 that includes
the fluid inlet manifold 306. A top layer 344 contains the spacer
332 without the hole 333 on the end 331 of the device 296 that
includes the fluid inlet manifold 306, and the one or more
intervening layers 336 contain the spacer 332 having the hole 333
on the end 331 of the device 296 that includes the fluid inlet
manifold 306. As such, when the layers 330 are perimeter-bonded
together, the hole 333 of the bottom layer 334 is the fluid inlet
300 of the device 296 and the stacked mesofluidic channels 308 are
formed between the layers 330. For example, in the illustrated
embodiment, the device 296 contains three mesofluidic channels 308
formed between the bottom layer 334 and the adjacent intervening
layer 336, between the two intervening layers 336, and between the
top layer 344 and the adjacent intervening layer 336.
[0072] In operation, the cell culture fluid 198 may be flowed into
the device 296 via the fluid inlet 300 and into the fluid inlet
manifold 306. The cell culture fluid 198 may only enter the
mesofluidic channels 308 in the direction of the flow into the
device 296 because the spacer 332 without the hole 333 of the top
layer 344 will block the flow from continuation in the fluid inlet
manifold 306. The fluid inlet manifold 306 will substantially
equally distribute the cell culture fluid 198 between the
mesofluidic channels.
[0073] FIG. 11 illustrates the layers 330 at the end 331 forming
the fluid outlet manifold 310 of the device 296. To form the fluid
outlet manifold 310 when the layers 330 are bonded together via the
perimeter bond 338, the top layer 344 contains the spacer 332
having the hole 333 on the end 331 of the device 296 that includes
the fluid outlet manifold 310. The bottom layer 334 contains the
spacer 332 without the hole 333 on the end 331 of the device 296
that includes the fluid outlet manifold 310, and the one or more
intervening layers 336 contain the spacer 332 having the hole 333
on the end 331 of the device 296 that includes the fluid inlet
manifold 310. As such, when the layers 330 are perimeter-bonded
together, the hole 333 of the top layer 344 is the fluid outlet 304
of the device 296 and the stacked mesofluidic channels 308 are
formed between the layers 330. For example, in the illustrated
embodiment, the device 296 contains three mesofluidic channels 308
formed between the bottom layer 334 and the adjacent intervening
layer 336, between the two intervening layers 336, and between the
top layer 344 and the adjacent intervening layer 336.
[0074] In operation, after the cell culture fluid 198 is flowed
through the mesofluidic channels 308 of the device 296 to allow the
cells and/or particles to separate from the base fluid layer, the
clarified fluid layer 202 may exit the mesofluidic channels 308 and
flow into the fluid outlet manifold 310. The fluid outlet manifold
310 may collect the clarified fluid layer 202 flowed from each
mesofluidic channel 308 and may direct the clarified fluid layer
202 out of the deice 296 via the fluid outlet 304 in the spacer 332
of the top layer 344. As such, the cells and/or other particles
that fell out of the cell culture fluid 198 may remain within the
mesofluidic channels 308 formed from the perimeter-bonded layers
330 and the clarified cell culture fluid 202 may be recovered from
the fluid outlet of the device 296.
[0075] FIG. 12 illustrates a top view of an embodiment of the
device 296. As previously discussed, the spacer 332 of the top
layer 344 which forms part of the fluid inlet manifold 306 does not
include the hole 333, while the spacer 332 of the top layer 344
which forms part of the fluid outlet manifold 310 includes the hole
333, which also forms the fluid outlet 304 of the device 296. In
some embodiments, the holes 333 of the spacers 332 may include a
partial gap 350 to increase ease of flow from the fluid inlet
manifold 306 into the one or more mesofluidic channels 308 and into
the fluid outlet manifold 310 from the one or more mesofluidic
channels 308. The spacers 332 may be thicker than the material of
the layer 330. As such, a thickness of the spacers 332 may define
the height of each mesofluidic channel 308. Additionally, in some
embodiments, one or more plates may be aligned with the spacers at
the fluid inlet channel 306 and/or the fluid outlet channel 310
above and/or below the device 196 to compress the spacers to a
particular predefined mesofluidic channel height.
Examples
TABLE-US-00001 [0076] TABLE 4 Experimental conditions for
processing cell culture fluid using three different size devices.
Narrow Wide Narrow Narrow Narrow 5 Stack Experimental 5 5 Film 5 5
w/0.03 wt % Conditions Stack Stack Single Stack Stack pDADMAC
Process Angle Degrees 5 5 12.5 5 5 25 Target Flow mL/min 86 8 2.6 8
8 8 Rate Actual Flow mL/min 85.7 7.9 2.7 7.9 7.9 7.9 Rate Device
Volume mL 2,000 200 65 200 200 200 Residence min 23.3 25.4 24.1
25.4 25.4 25.4 Time Feed Cell cells/mL 42M 42M 42M 28M 57M 50M
Concentration Feed Viability % 99.6 99.6 99.6 39.7% 17.1% 48.6%
Feed Turbidity NTU 1,592 1,592 1,592 2,140 2,889 7,064
[0077] Experimental conditions and results of processing of cell
culture fluid using three embodiments of the separation device
(e.g., separation devices 196 and 246) are shown in Table 4 above
and Table 5 below. The cell culture fluid 198, in this case a CHO
cell suspension, was processed through a device having five
relatively wide mesofluidic channels disposed in a series stack, a
device having five relatively narrow mesofluidic channels disposed
in a series stack, and a device having only one flexible
mesofluidic channel (discussed in greater detail with reference to
FIG. 20).
[0078] An internal monoclonal CHO cell line modified to produce a
mAb (Hyclone CHO producing Herceptin) was grown in ActiPro.TM.
media in various cultures. 500 mL shake flasks (150 rpm, 7.5% CO2,
37 C) were used to achieve 10-20 million cells per mL whereas
higher cell densities (30-40 million cells/mL) were cultured in a
fed batch 10 L stirred tank reactor (BioFlow.TM. 310: 150 rpm, pH,
DO, and temp control). Concentrated cell densities above 40 million
cells/mL were obtained via centrifugation of harvested cells into a
pellet and resuspending in reduced volumes with spent media. The
container holding the cells for harvesting was always stirred to
insure homogenous cell densities. Several sized separation devices
were used for separation. In all cases, a peristaltic pump (Cole
Parmer Master Flex L/S, with either Easy Load (Model 7517-00) or
Easy Load II (model 77202-60) pump heads) was used to negatively
displace the cells from the reactor into the tubing and then
positively displace cells into the harvester. To avoid variable
cell settling in the tube between the pump and harvester, the
tubing distance was minimized as much as possible and kept level.
Additionally, if the separation device had multiple fluid inlets or
outlets, care was taken to level the fluid inlet manifolds and the
fluid outlet manifolds such that even flow would enter and exit
each of the ports.
[0079] As shown in Table 4, the device having five relatively wide
mesofluidic channels disposed in a series stack (e.g., wide 5
stack) had a device volume of 2,000 L and the flow rate of the cell
culture fluid through the device of 85.7 mL/min, thus resulting in
a residence time of the cell culture fluid within the device of
23.3 minutes. The device having five relatively narrow mesofluidic
channels disposed in a series stack had a device volume of 200 mL
and the flow rate of the cell culture fluid through the device of
7.9 mL/min, thus resulting in a residence time of the cell culture
fluid within the device of 25.4 minutes. Further, device having
only one flexible mesofluidic channel had a device volume of 65 mL
and the flow rate of the cell culture fluid through the device of
2.7 mL/min, thus resulting in a residence time of the cell culture
fluid within the device 196 of 24.1 minutes.
TABLE-US-00002 TABLE 5 Empirical results for cell culture
processing using three different size devices. Wide Narrow Narrow
Narrow Narrow Experimental 5 5 Film 5 5 5 Results Stack Stack
Single Stack Stack Stack pDADMAC Wt % 0 0 0 0 0 0.03 Effluent NTU
77.3 69.1 64.6 139 242.5 3.89 Turbidity Effluent Cell MM/mL 0.66M
0.044M 0.11M 0.90M 1.44M <LOD Concentration Total Cells MM
24,6147 58,711 16,684 24,040 23,734 19,750 Captured % Cells % 97.2
99.9 98.3 97 97.5 ~100% Captured Volume mL 6001 1412 402 986 487
395 Processed
[0080] These processing conditions show that the device may have a
capacity or device volume of up to 2,000 L that may be processed at
time. As shown in Table 5, each of the devices described
efficiently separate the particles (e.g. cells) from the fluid
layer of the cell culture fluid and provide a retention of the
cells within the device between 97.2%-99.9%. As such, the residence
time for each device 196, within the range previously discussed
with reference to FIG. 2, was able to efficiently clarify the cell
culture fluid that was provided to each device, at a particular
residence time within the previously discussed ranges when provided
the cell culture medium and a particular flow rate relative to the
device capacity. Thus, the device may provide cell removal from the
cell culture fluid 198 at retention rates similar to
centrifugation, but with a device that is simpler and may be
disposable.
[0081] While only certain features of the present disclosure have
been illustrated and described herein, many modifications and
changes will occur to those skilled in the art. It is, therefore,
to be understood that the appended embodiments are intended to
cover all such modifications and changes as fall within the scope
of the disclosure.
* * * * *