U.S. patent application number 11/227904 was filed with the patent office on 2007-08-23 for devices and methods for enrichment and alteration of cells and other particles.
Invention is credited to Ravi Kapur, Mehmet Toner.
Application Number | 20070196820 11/227904 |
Document ID | / |
Family ID | 37071048 |
Filed Date | 2007-08-23 |
United States Patent
Application |
20070196820 |
Kind Code |
A1 |
Kapur; Ravi ; et
al. |
August 23, 2007 |
Devices and methods for enrichment and alteration of cells and
other particles
Abstract
The invention features a device for the deterministic separation
of analytes coupled to a reservoir containing a reagent that alters
a magnetic propert of the analyte. Exemplary methods include the
enrichment of a sample in a desired analyte (e.g., using
deterministic separation) or the alteration of a desired analyte in
the device. The devices and methods may be advantageously employed
to enrich for rare cells, e.g., fetal cells or epithelial cells,
present in a sample, e.g., maternal blood.
Inventors: |
Kapur; Ravi; (US) ;
Toner; Mehmet; (US) |
Correspondence
Address: |
CLARK & ELBING LLP
101 FEDERAL STREET
BOSTON
MA
02110
US
|
Family ID: |
37071048 |
Appl. No.: |
11/227904 |
Filed: |
September 15, 2005 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
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60668415 |
Apr 5, 2005 |
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60704067 |
Jul 29, 2005 |
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Current U.S.
Class: |
435/5 ;
435/287.2; 435/7.21 |
Current CPC
Class: |
B01L 2400/043 20130101;
B01L 2200/0647 20130101; Y10T 436/25 20150115; Y10T 137/8593
20150401; B01L 3/502753 20130101; G01N 2035/00237 20130101; G01N
1/40 20130101; B33Y 80/00 20141201; B01L 3/502761 20130101; B01L
2400/0487 20130101; B01L 2400/0472 20130101; B01L 2300/0864
20130101; B01L 2400/0409 20130101; B01L 2300/0816 20130101; B03C
1/30 20130101; B01L 2400/0415 20130101; B01L 2400/086 20130101;
Y10T 137/0318 20150401; B01L 3/502746 20130101; B03C 1/32 20130101;
B01L 2400/0406 20130101; G01N 33/5044 20130101; Y10T 436/25375
20150115; C12M 47/06 20130101; C12M 47/04 20130101; G01N 1/4077
20130101; B03C 2201/18 20130101 |
Class at
Publication: |
435/005 ;
435/007.21; 435/287.2 |
International
Class: |
C12Q 1/70 20060101
C12Q001/70; G01N 33/567 20060101 G01N033/567; C12M 3/00 20060101
C12M003/00 |
Claims
1. A device for producing a sample enriched in an analyte, said
device comprising: (a) a first channel comprising a structure that
deterministically deflects particles having a hydrodynamic size
above a critical size in a direction not parallel to the average
direction of flow in said structure, wherein said particles are
analyte particles or are a non-analyte component of said sample;
and (b) a reservoir fluidly coupled to an output of said first
channel through which said analyte passes into said reservoir,
wherein said reservoir comprises a reagent that alters a magnetic
property of said analyte.
2. The device of claim 1, wherein said first channel is a
microfluidic channel.
3. The device of claim 1, wherein said structure comprises an array
of obstacles that form a network of gaps, wherein a fluid passing
through said gaps is divided unequally into a major flux and a
minor flux so that the average direction of the major flux is not
parallel to the average direction of fluidic flow in said
channel.
4. The device of claim 3, wherein said array of obstacles comprises
first and second rows, wherein the second row is displaced
laterally relative to the first row so that fluid passing through a
gap in the first row is divided unequally into two gaps in the
second row.
5. The device of claim 1, wherein said analyte has a hydrodynamic
size greater than said critical size.
6. The device of claim 1, wherein said analyte has a hydrodynamic
size smaller than said critical size.
7. The device of claim 1, further comprising a magnetic force
generator capable of generating a magnetic field.
8. The device of claim 7, wherein said magnetic force generator
comprises a region of magnetic obstacles disposed in a second
channel.
9. The device of claim 8, wherein at least a portion of said
magnetic obstacles comprise a permanent magnet.
10. The device of claim 8, wherein at least a portion of said
magnetic obstacles comprise a non-permanent magnet.
11. The device of claim 8, wherein said obstacles are ordered in a
two-dimensional array.
12. The device of claim 8, wherein said second channel is a
microfluidic channel.
13. The device of claim 1, wherein said reservoir further comprises
a second channel comprising a magnet.
14. The device of claim 1, wherein said reagent alters an intrinsic
magnetic property of said one or more analytes.
15. The device of claim 14, wherein said reagent comprises sodium
nitrite.
16. The device of claim 1, wherein said reagent binds to said one
or more analytes.
17. The device of claim 16, wherein said reagent comprises a
magnetic particle.
18. The device of claim 17, wherein said magnetic particle
comprises an antibody or an antigen-binding fragment thereof.
19. The device of claim 18, wherein said antibody is anti-CD71,
anti-CD36, anti-CD45, anti-GPA, anti-antigen i, anti-CD34, or
anti-fetal hemoglobin.
20. The device of claim 16, wherein said reagent comprises
holo-transferrin.
21. A method for producing a sample enriched in a first analyte
relative to a second analyte, said method comprising: (a) applying
at least a portion of said sample to a device comprising a
structure that deterministically deflects particles having a
hydrodynamic size above a critical size in a direction not parallel
to the average direction of flow in said structure, thereby
producing a second sample enriched in said first analyte and
comprising said second analyte; (b) combining said second sample
with a reagent that alters a magnetic property of said first
analyte to produce an altered first analyte; and (c) applying a
magnetic field to said second sample, wherein said magnetic field
generates a differential force to physically separate said altered
first analyte from said second analyte, thereby producing a sample
enriched in said first analyte.
22. The method of claim 21, wherein said reagent binds to said
first analyte.
23. The method of claim 21, wherein said reagent alters an
intrinsic magnetic property of said first analyte.
24. The method of claim 23, wherein said reagent comprises sodium
nitrite.
25. The method of claim 21, wherein said reagent comprises a
magnetic particle that binds to or is incorporated into said first
analyte.
26. The method of claim 25, wherein said magnetic particle
comprises an antibody or an antigen-binding fragment thereof.
27. The method of claim 26, wherein said antibody is anti-CD71,
anti-GPA, anti-antigen i, anti-CD45, anti-CD34, or anti-fetal
hemoglobin.
28. The method of claim 21, wherein said analyte has a hydrodynamic
size greater than said critical size.
29. The method of claim 21, wherein said analyte has a hydrodynamic
size smaller than said critical size.
30. The method of claim 21, wherein said sample comprises a
maternal blood sample.
31. The method of claim 21, wherein said first analyte is a cell,
an organelle, or a virus.
32. The method of claim 31, wherein said cell is a bacterial cell,
a fetal cell, or a blood cell.
33. The method of claim 32, wherein said blood cell is a fetal red
blood cell.
34. The method of claim 31, wherein said organelle is a
nucleus.
35. A method of producing a sample enriched in red blood cells
relative to a second blood component, said method comprising: (a)
contacting a sample comprising red blood cells with a reagent that
oxidizes iron to produce oxidized hemoglobin; and (b) applying a
magnetic field to said sample, wherein said red blood cells having
oxidized hemoglobin are attracted to said magnetic field to a
greater extent than said second blood component, thereby producing
said sample enriched in said red blood cells.
36. The method of claim 35, wherein said red blood cells are fetal
red blood cells.
37. The method of claim 36, wherein said second blood component is
a maternal blood cell.
38. The method of claim 35, wherein prior to said step (a), said
sample is enriched for said red blood cells.
39. The method of claim 38, wherein said enriching is performed by
applying at least a portion of said sample to a device comprising a
structure that deterministically deflects particles having a
hydrodynamic size above a critical size in a direction not parallel
to the average direction of flow in said structure.
40. The method of claim 39, wherein fetal red blood cells are
enriched relative to maternal red blood cells.
41. A device for producing a sample enriched in red blood cells,
said device comprising: (a) an analytical device that enriches said
red blood cells based on size, shape, deformability, or affinity;
and (b) a reservoir comprising a reagent that oxidizes iron,
wherein said reagent increases the magnetic responsiveness of said
red blood cells.
42. The device of claim 41, wherein said analytical device
comprises a first channel comprising a structure that
deterministically deflects particles having a hydrodynamic size
above a critical size in a direction not parallel to the average
direction of flow in said structure.
43. The device of claim 41, wherein said reagent is sodium nitrite.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] The present application claims the benefit of U.S.
Provisional Application Ser. Nos. 60/668,415, filed Apr. 5, 2005
and 60/704,067, filed Jul. 29, 2005, each of which is hereby
incorporated by reference in its entirety.
BACKGROUND OF THE INVENTION
[0002] The invention relates to the fields of cell separation,
medical diagnostics, and microfluidic devices.
[0003] Clinically or environmentally relevant information may often
be present in a sample, but in quantities too low to detect. Thus,
various enrichment or amplification methods are often employed in
order to increase the detectability of such information.
[0004] For cells, different flow cytometry and cell sorting methods
are available, but these techniques typically employ large and
expensive pieces of equipment, which require large volumes of
sample and skilled operators. These cytometers and sorters use
methods like electrostatic deflection, centrifugation, fluorescence
activated cell sorting (FACS), and magnetic activated cell sorting
(MACS) to achieve cell separation. These methods often suffer from
the inability to enrich a sample sufficiently to allow analysis of
rare components of the sample. Furthermore, such techniques may
result in unacceptable losses of such rare components, e.g.,
through inefficient separation or degradation of the
components.
[0005] Thus, there is a need for new devices and methods for
enriching samples.
SUMMARY OF THE INVENTION
[0006] In a first aspect, the invention provides a device for
producing a sample enriched in an analyte that includes a first
channel (e.g., a microfluidic channel) including a structure that
deterministically deflects particles having a hydrodynamic size
above a critical size in a direction not parallel to the average
direction of flow in the structure, wherein said particles are
analyte particles or are a non-analyte component of the sample; and
a reservoir fluidly coupled to an output of the first channel
through which the analyte passes into the reservoir, the reservoir
including a reagent that alters a magnetic property of the analyte.
In a first embodiment, the structure includes an array of obstacles
that form a network of gaps, where a fluid passing through the gaps
is divided unequally into a major flux and a minor flux so that the
average direction of the major flux is not parallel to the average
direction of fluidic flow in the channel. In the first embodiment,
the array of obstacles may include first and second rows, where the
second row is displaced laterally relative to the first row so that
fluid passing through a gap in the first row is divided unequally
into two gaps in the second row. The analyte may have a
hydrodynamic size greater than or smaller than the critical size.
The device may include a magnetic force generator capable of
generating a magnetic field, and may further include a region of
magnetic obstacles (e.g., obstacles including a permanent magnet or
obstacles including a non-permanent magnet) disposed in a second
channel (e.g., a microfluidic channel). The magnetic obstacles may
be ordered in a two-dimensional array. The reservoir of the device
may further include a second channel including a magnet. The
reagent (e.g., sodium nitrite) may alter an intrinsic magnetic
property of one or more analytes. In one embodiment, the reagent,
e.g., holo-transferrin or a magnetic particle, may bind to the one
or more analytes. A magnetic particle may further include an
antibody (e.g., anti-CD71, anti-CD36, anti-CD45, anti-GPA,
anti-antigen i, anti-CD34, anti-fetal hemoglobin, anti-EpCAM,
anti-E-cadherin, or anti-Muc-1) or an antigen-binding fragment
thereof.
[0007] In a second aspect, the invention provides a method for
producing a sample enriched in a first analyte relative to a second
analyte that includes applying at least a portion of the sample to
a device including a structure that deterministically deflects
particles having a hydrodynamic size above a critical size in a
direction not parallel to the average direction of flow in the
structure, thereby producing a second sample enriched in the first
analyte and including the second analyte; combining the second
sample with a reagent that alters a magnetic property of the first
analyte to produce an altered first analyte; and applying a
magnetic field to the second sample, where the magnetic field
generates a differential force to physically separate the altered
first analyte from the second analyte, thereby producing a sample
enriched in the first analyte. The reagent may bind to the first
analyte. In another embodiment, the reagent (e.g., sodium nitrite)
may alter an intrinsic magnetic property of the first analyte. In
yet another embodiment, the reagent may include a magnetic particle
that binds to or is incorporated into the first analyte. The
magnetic particle may include an antibody (e.g., anti-CD71,
anti-GPA, anti-antigen i, anti-CD45, anti-CD34, anti-fetal
hemoglobin, anti-EpCAM, anti-E-cadherin, or anti-Muc-1) or an
antigen-binding fragment thereof. The analyte may have a
hydrodynamic size greater than or less than said critical size. The
sample may be a maternal blood sample. The first analyte may be a
cell (e.g., bacterial cell, a fetal cell, or a blood cell such as a
fetal red blood cell), an organelle (e.g., a nucleus), or a
virus.
[0008] In a third aspect, the invention provides a method of
producing a sample enriched in red blood cells relative to a second
blood component (e.g., maternal blood cells) that includes
contacting the sample including red blood cells (e.g., fetal red
blood cells) with a reagent that oxidizes iron to produce oxidized
hemoglobin; and applying a magnetic field to the sample, where the
red blood cells having oxidized hemoglobin are attracted to the
magnetic field to a greater extent than the second blood component,
thereby producing the sample enriched in the red blood cells. The
method may further include performing prior to the contacting step,
a step that enriches the sample with red blood cells (e.g.,
enriching fetal blood cells are enriched relative to maternal red
blood cells), for example, by applying at least a portion of the
sample to a device including a structure that deterministically
deflects particles having a hydrodynamic size above a critical size
in a direction not parallel to the average direction of flow in the
structure.
[0009] In a fourth aspect, the invention provides a device for
producing a sample enriched in red blood cells that includes an
analytical device that enriches the red blood cells based on size,
shape, deformability, or affinity; and a reservoir including a
reagent that oxidizes iron, where the reagent (e.g., sodium
nitrite) increases the magnetic responsiveness of the red blood
cells. The analytical device may include a first channel that
includes a structure that deterministically deflects particles
having a hydrodynamic size above a critical size in a direction not
parallel to the average direction of flow in the structure.
[0010] In a fifth aspect, the invention provides a reagent that
includes a plurality of magnetic particles coupled to one or more
binding moieties (e.g., an antibody such as a monoclonal antibody)
that selectively binds GPA, fetal hemoglobin, CD34, CD45, CD71,
EGFR, or EpCAm.
[0011] In a sixth aspect, the invention provides a method for
separating one or more cells of interest from a mixture of cells
that includes combining the mixture of cells with a reagent of the
fifth aspect and incubating the mixture of cells and the reagent
for a time sufficient to allow the binding moieties to selectively
bind the one or more cells of interest in the mixture, and apply a
magnetic field to the mixture thereby separating cells that bound
the magnetic particles from cells that did not bind the magnetic
particles. The method may further include a step of enriching the
mixture of cells for the one or more cells of interest. The
enriching step may include performing size-based separation with an
array of obstacles or selectively lysing one or more cells that is
not a cell of interest.
[0012] By "analyte" is meant a molecule, other chemical species,
e.g., an ion, or particle. Exemplary analytes include cells,
viruses, nucleic acids, proteins, carbohydrates, and small organic
molecules.
[0013] By "biological particle" is meant any species of biological
origin that is insoluble in aqueous media on the time scale of
sample acquisition, preparation, storage, and analysis. Examples
include cells, particulate cell components, viruses, and complexes
including proteins, lipids, nucleic acids, and carbohydrates.
[0014] By "biological sample" is meant any sample of biological
origin or containing, or potentially containing, biological
particles. Preferred biological samples are cellular samples.
[0015] By "blood component" is meant any component of whole blood,
including host red blood cells, white blood cells, and platelets.
Blood components also include the components of plasma, e.g.,
proteins, lipids, nucleic acids, and carbohydrates, and any other
cells that may be present in blood, e.g., because of current or
past pregnancy, organ transplant, or infection.
[0016] By "cellular sample" is meant a sample containing cells or
components thereof. Such samples include naturally occurring fluids
(e.g., blood, lymph, cerebrospinal fluid, urine, cervical lavage,
and water samples), portions of such fluids, and fluids into which
cells have been introduced (e.g., culture media, and liquefied
tissue samples). The term also includes a lysate.
[0017] By "capture moiety" is meant a chemical species to which an
analyte binds. A capture moiety may be a compound coupled to a
surface or the material making up the surface. Exemplary capture
moieties include antibodies, oligo- or polypeptides, nucleic acids,
other proteins, synthetic polymers, and carbohydrates.
[0018] By "channel" is meant a gap through which fluid may flow. A
channel may be a capillary, a conduit, or a strip of hydrophilic
pattern on an otherwise hydrophobic surface wherein aqueous fluids
are confined.
[0019] By "component" of cell is meant any component of a cell that
may be at least partially isolated upon lysis of the cell. Cellular
components may be organelles (e.g., nuclei, peri-nuclear
compartments, nuclear membranes, mitochondria, chloroplasts, or
cell membranes), polymers or molecular complexes (e.g., lipids,
polysaccharides, proteins. (membrane, trans-membrane, or
cytosolic), nucleic acids (native, therapeutic, or pathogenic),
viral particles, or ribosomes), or other molecules (e.g., hormones,
ions, cofactors, or drugs). By "component" of a cellular sample is
meant a subset of cells contained within the sample.
[0020] By "enriched sample" is meant a sample containing an analyte
that has been processed to increase the relative amount of the
analyte relative to other analytes typically present in a sample.
For example, samples may be enriched by increasing the amount of
the analyte of interest by at least 10%, 25%, 50%, 75%, 100% or by
a factor of at least 1000, 10,000, 100,000, or 1,000,000.
[0021] By "depleted sample" is meant a sample containing an analyte
that has been processed to decrease the amount of the analyte
relative to other analytes typically present in a sample. For
example, samples may be depleted by decreasing the amount of the
analyte of interest by at least 5%, 10%, 25%, 50%, 75%, 90%, 95%,
97%, 98%, 99%, or even 100%.
[0022] By "exchange buffer" in the context of a sample (e.g., a
cellular sample) is meant a medium distinct from the medium in
which the sample is originally suspended, and into which one or
more components of the sample are to be exchanged.
[0023] By "flow-extracting boundary" is meant a boundary designed
to remove fluid from an array.
[0024] By "flow-feeding boundary" is meant a boundary designed to
add fluid to an array.
[0025] By "gap" is meant an opening through which fluids and/or
particles may flow. For example, a gap may be a capillary, a space
between two obstacles wherein fluids may flow, or a hydrophilic
pattern on an otherwise hydrophobic surface wherein aqueous fluids
are confined. In a preferred embodiment of the invention, the
network of gaps is defined by an array of obstacles. In this
embodiment, the gaps are the spaces between adjacent obstacles. In
a preferred embodiment, the network of gaps is constructed with an
array of obstacles on the surface of a substrate.
[0026] By "hydrodynamic size" is meant the effective size of a
particle when interacting with a flow, obstacles (e.g., posts), or
other particles. The obstacles or other particles may be in a
microfluidic structure. It is used as a general term for particle
volume, shape, and deformability in the flow.
[0027] By "intracellular activation" is meant activation of second
messenger pathways, leading to transcription factor activation, or
activation of kinases or other metabolic pathways. Intracellular
activation through modulation of external cell membrane antigens
can also lead to changes in receptor trafficking.
[0028] By "labeling reagent" is meant a reagent that is capable of
binding to an analyte, being internalized or otherwise absorbed,
and being detected, e.g., through shape, morphology, color,
fluorescence, luminescence, phosphorescence, absorbance, magnetic
properties, or radioactive emission.
[0029] By "metabolome" is meant the set of compounds within a cell,
other than proteins and nucleic acids, that participate in
metabolic reactions and that are required for the maintenance,
growth or normal function of a cell.
[0030] By "microfluidic" is meant having at least one dimension of
less than 1 mm.
[0031] By "obstacle" is meant an impediment to flow in a channel,
e.g., a protrusion from one surface. For example, an obstacle may
refer to a post outstanding on a base substrate or a hydrophobic
barrier for aqueous fluids. In some embodiments, the obstacle may
be partially permeable. For example, an obstacle may be a post made
of porous material, wherein the pores allow penetration of an
aqueous component but are too small for the particles being
separated to enter.
[0032] By "shrinking reagent" is meant a reagent that decreases the
hydrodynamic size of a particle. Shrinking reagents may act by
decreasing the volume, increasing the deformability, or changing
the shape of a particle.
[0033] By "swelling reagent" is meant a reagent that increases the
hydrodynamic size of a particle. Swelling reagents may act by
increasing the volume, reducing the deformability, or changing the
shape of a particle.
[0034] By "substantially larger" is meant at least 2-fold, 3-fold,
5-fold, 10-fold, 25-fold, 50-fold, or even 100-fold larger.
[0035] By "substantially smaller" is meant at least 2-fold, 3-fold,
5-fold, 10-fold, 25-fold, 50-fold, or even 100-fold smaller.
[0036] Other features and advantages will be apparent from the
following description and the claims.
BRIEF DESCRIPTION OF THE DRAWINGS
[0037] FIGS. 1A-1E are schematic depictions of an array that
separated cells based on deterministic lateral displacement: (A)
illustrates the lateral displacement of subsequent rows; (B)
illustrates how fluid flowing through a gap is divide unequally
around obstacles in subsequent rows; (C) illustrates how an analyte
with a hydrodynamic size above the critical size is displaced
laterally in the device; (D) illustrates an array of cylindrical
obstacles; and (E) illustrates an array of elliptical
obstacles.
[0038] FIG. 2 is a schematic description illustrating the unequal
division of the flux through a gap around obstacles in subsequent
rows.
[0039] FIG. 3 is a schematic depiction of how the critical size
depends on the flow profile, which is parabolic in this
example.
[0040] FIG. 4 is an illustration of how shape affects the movement
of analytes through a device.
[0041] FIG. 5 is an illustration of how deformability affects the
movement of analytes through a device.
[0042] FIG. 6 is a schematic depiction of deterministic lateral
displacement. Analytes having a hydrodynamic size above the
critical size move to the edge of the array, while analytes having
a hydrodynamic size below the critical size pass through the device
without lateral displacement.
[0043] FIG. 7 is a schematic depiction of a three stage
deterministic device.
[0044] FIG. 8 is a schematic depiction of the maximum size and
cut-off size for the device of FIG. 7.
[0045] FIG. 9 is a schematic depiction of a bypass channel.
[0046] FIG. 10 is a schematic depiction of a bypass channel.
[0047] FIG. 11 is a schematic depiction of a three stage
deterministic device having a common bypass channel.
[0048] FIG. 12 is a schematic depiction of a three stage, duplex
deterministic device having a common bypass channel.
[0049] FIG. 13 is a schematic depiction of a three stage
deterministic device having a common bypass channel, where the flow
through the device is substantially constant.
[0050] FIG. 14 is a schematic depiction of a three stage, duplex
deterministic device having a common bypass channel, where the flow
through the device is substantially constant.
[0051] FIG. 15 is a schematic depiction of a three stage
deterministic device having a common bypass channel, where the
fluidic resistance in the bypass channel and the adjacent stage are
substantially constant.
[0052] FIG. 16 is a schematic depiction of a three stage, duplex
deterministic device having a common bypass channel, where the
fluidic resistance in the bypass channel and the adjacent stage are
substantially constant.
[0053] FIG. 17 is a schematic depiction of a three stage
deterministic device having two, separate bypass channels.
[0054] FIG. 18 is a schematic depiction of a three stage
deterministic device having two, separate bypass channels, which
are in arbitrary configuration.
[0055] FIG. 19 is a schematic depiction of a three stage, duplex
deterministic device having three, separate bypass channels.
[0056] FIG. 20 is a schematic depiction of a three stage
deterministic device having two, separate bypass channels, wherein
the flow through each stage is substantially constant.
[0057] FIG. 21 is a schematic depiction of a three stage, duplex
deterministic device having three, separate bypass channels,
wherein the flow through each stage is substantially constant.
[0058] FIG. 22 is a schematic depiction of a flow-extracting
boundary.
[0059] FIG. 23 is a schematic depiction of a flow-feeding
boundary.
[0060] FIG. 24 is a schematic depiction of a flow-feeding boundary,
including a bypass channel.
[0061] FIG. 25 is a schematic depiction of two flow-feeding
boundaries flanking a central bypass channel.
[0062] FIG. 26 is a schematic depiction of a device having four
channels that act as on-chip flow resistors.
[0063] FIGS. 27 and 28 are schematic depictions of the effect of
on-chip resistors on the relative width of two fluids flowing in a
device.
[0064] FIG. 29 is a schematic depiction of a duplex device having a
common inlet for the two outer regions.
[0065] FIG. 30A is a schematic depiction of a multiple arrays on a
device. FIG. 30B is a schematic depiction of multiple arrays with
common inlets and product outlets on a device.
[0066] FIG. 31 is a schematic depiction of a multi-stage device
with a small footprint.
[0067] FIG. 32 is a schematic depiction of blood passing through a
device.
[0068] FIG. 33 is a graph illustrating the hydrodynamic size
distribution of blood cells.
[0069] FIGS. 34A-34D are schematic depictions of moving an analyte
from a sample to a buffer in a single stage (A), three stage (B),
duplex (C), or three stage duplex (D) deterministic device.
[0070] FIG. 35A is a schematic depiction of a two stage
deterministic device employed to move a particle from blood to a
buffer to produce three products. FIG. 35B is a schematic graph of
the maximum size and cut off size of the two stages. FIG. 35C is a
schematic graph of the composition of the three products.
[0071] FIG. 36 is a schematic depiction of a two stage
deterministic device for alteration, where each stage has a bypass
channel.
[0072] FIG. 37 is a schematic depiction of the use of fluidic
channels to connect two stages in a device.
[0073] FIG. 38 is a schematic depiction of the use of fluidic
channels to connect two stages in a device, wherein the two stages
are configured as a small footprint array.
[0074] FIG. 39A is a schematic depiction of a two stage
deterministic device having a bypass channel that accepts output
from both stages. FIG. 39B is a schematic graph of the size range
of product achievable with this device.
[0075] FIG. 40 is a schematic depiction of a two stage
deterministic device for alteration having bypass channels that
flank each stage and empty into the same outlet.
[0076] FIG. 41 is a schematic depiction of a deterministic device
for the sequential movement and alteration of particles.
[0077] FIG. 42A is a photograph of a deterministic device that may
be incorporated into a device of the invention. FIGS. 42B-42E are
depictions the mask used to fabricate a device that may be
incorporated into the invention. FIG. 42F is a series of
photographs of the device containing blood and buffer.
[0078] FIGS. 43A-43F are typical histograms generated by the
hematology analyzer from a blood sample and the waste (buffer,
plasma, red blood cells, and platelets) and product (buffer and
nucleated cells) fractions generated by the device of FIG. 42.
[0079] FIGS. 44A-44D are depictions the mask used to fabricate a
deterministic device that may be incorporated into a device of the
invention.
[0080] FIGS. 45A-45D are depictions the mask used to fabricate a
deterministic device that may be incorporated a device of into the
invention.
[0081] FIG. 46A is a micrograph of a sample enriched in fetal red
blood cells. FIG. 46B is a micrograph of maternal red blood cell
waste.
[0082] FIG. 47 is a series of micrographs showing the positive
identification of male fetal cells (Blue=nucleus, Red=X chromosome,
Green=Y chromosome).
[0083] FIG. 48 is a series of micrographs showing the positive
identification of sex and trisomy 21.
[0084] FIGS. 49A-49D are depictions the mask used to fabricate a
deterministic device that may be incorporated into a device of the
invention.
[0085] FIGS. 50A-50G are electron micrographs of the device of FIG.
49.
[0086] FIGS. 51A-51D are depictions the mask used to fabricate a
deterministic device that may be incorporated into a device of the
invention.
[0087] FIGS. 52A-52F are electron micrographs of the device of FIG.
51.
[0088] FIGS. 53A-53F are electron micrographs of the device of FIG.
45.
[0089] FIGS. 54A-54D are depictions the mask used to fabricate a
deterministic device that may be incorporated a device of into the
invention.
[0090] FIGS. 55A-55S are electron micrographs of the device of FIG.
54.
[0091] FIGS. 56A-56C are electron micrographs of the device of FIG.
44.
[0092] FIG. 57A is a schematic illustration of a deterministic
device that may be incorporated into a device of the invention and
its operation. FIG. 57B is an illustration of the device of FIG.
57A and a further-schematized representation of this device.
[0093] FIGS. 58A and 58B are illustrations of two distinct
configurations for joining two deterministic devices together. In
FIG. 58A, a cascade configuration is shown, in which outlet 1 of
one device is joined to a sample inlet of a second device. In FIG.
58B, a bandpass configuration is shown, in which outlet 2 of one
device is joined to a sample inlet of a second device.
[0094] FIG. 59 is an illustration of an enhanced method of size
separation in which target cells are labeled with immunoaffinity
beads.
[0095] FIG. 60 is an illustration of a method for performing size
fractionation and for separating free labeling reagents, e.g.,
antibodies, from bound labeling reagents by using a device that may
be incorporated into the invention.
[0096] FIG. 61 is an illustration of a method shown in FIG. 60. In
this case, non-target cells may copurify with target cells, but
these non-target cells do not interfere with quantification of
target cells.
[0097] FIG. 62 is an illustration of a method for separating large
cells from a mixture and producing a concentrated sample of these
cells.
[0098] FIG. 63 is an illustration of a method for lysing cells
inside a device of the invention and separating whole cells from
organelles and other cellular components.
[0099] FIG. 64 is an illustration of two devices arrayed in a
cascade configuration and used for performing size fractionation
and for separating free labeling reagent from bound labeling
reagents by using a device of the invention.
[0100] FIG. 65 is an illustration of two devices arrayed in a
cascade configuration and used for performing size fractionation
and for separating free labeling reagent from bound labeling
reagents by using a device of the invention. In this figure, phage
is utilized for binding and detection rather than antibodies.
[0101] FIG. 66 is an illustration of two devices arrayed in a
bandpass configuration.
[0102] FIG. 67 is a graph of cell count versus hydrodynamic cell
diameter for a microfluidic separation of normal whole blood.
[0103] FIG. 68 is a set of histograms from input, product, and
waste samples generated with a Coulter "A.sup.C-T diff" clinical
blood analyzer. The x-axis depicts cell volume in femtomoles.
[0104] FIG. 69 is a pair of representative micrographs from product
and waste streams of fetal blood processed with a cell enrichment
module, showing clear separation of nucleated cells and red blood
cells.
[0105] FIG. 70 is a pair of images showing cells fixed on a cell
enrichment module with paraformaldehyde and observed by
fluorescence microscopy. Target cells are bound to the obstacles
and floor of the capture module.
[0106] FIG. 71A is a graph of cell count versus hydrodynamic cell
diameter for a microfluidic separation of normal whole blood. FIG.
71B is a graph of cell count versus hydrodynamic cell diameter for
a microfluidic separation of whole blood including a population of
circulating tumor cells. FIG. 71C is the graph of FIG. 71B,
additionally showing a size cutoff that excludes most native blood
cells. FIG. 71D is the graph of FIG. 71C, additionally showing that
the population of cells larger than the size cutoff may include
endothelial cell, endometrial cells, or trophoblasts indicative of
a disease state.
[0107] FIG. 72 is a schematic illustration of a method that
features isolating and counting large cells within a cellular
sample, wherein the count is indicative of a patient's disease
state, and subsequently further analyzing the large cell
subpopulation.
[0108] FIG. 73A is a design for a preferred deterministic device
that may be incorporated into the invention. FIG. 73B is a table of
design parameters corresponding to FIG. 73A.
[0109] FIG. 74 is a cross-sectional view of a magnetic separation
device useful in a device of the invention and associated process
flow for cell isolation followed by release for off-line analysis
according to the present invention.
[0110] FIG. 75 is a schematic of the fabrication and
functionalization of a magnetic separation device. The magnetized
posts enable post-packaging modification of the device.
[0111] FIG. 76 is a schematic of an application of a magnetic
separation device to capture and release CD71+ cells from a complex
mixture, such as blood, using monoclonal antibodies to the
transferrin (CD71) receptor.
[0112] FIG. 77 is a schematic representation of an application of a
magnetic separation device to capture and release CD71+ cells from
a complex mixture, such as blood, using holotransferrin.
Holotransferrin is rich in iron content, commercially available,
and has higher affinity constants and specificity of interaction
with the CD71 receptor than its counterpart monoclonal
antibody.
[0113] Figures are not necessarily to scale.
DETAILED DESCRIPTION OF THE INVENTION
[0114] The invention provides analytical devices and methods useful
for enriching analytes in a sample. In one embodiment, the
invention provides a device that includes a channel that
deterministically deflects particles based on hydrodynamic size and
a reservoir containing a reagent capable of altering a magnetic
property of the particle. The invention also provides a method for
producing a sample enriched in a first analyte relative to a second
analyte by applying the sample to a device that includes a channel
that deterministically deflects particles based on hydrodynamic
size, thereby producing a second sample enriched in the first
analyte, and combining the second sample with a reagent that alters
a magnetic property of the first analyte, and applying a magnetic
field thereby separating the first analyte from the second analyte.
The methods and devices of the present invention may be used to
enrich samples for analytes such as red blood cells (e.g., fetal
red blood cells). Examples of fluid samples that are contemplated
by the present invention include biological fluid samples, such as,
whole blood, sweat, tears, ear flow, sputum, lymph, bone marrow
suspension, lymph, urine, saliva, semen, vaginal flow,
cerebrospinal fluid, brain fluid, ascites, milk, secretions of the
respiratory, intestinal and genitourinary tracts, and amniotic
fluid. Moreover, any other biological sample (e.g., a biopsy
sample) which may be solubilized is also contemplated by the
systems and methods herein. Analytes in biological fluid samples
include, but are not limited to, foreign organisms such as
bacteria, viruses, and protozoans.
Analytical Devices
[0115] The devices and methods of the invention may be employed in
connection with any analytical device. Examples include affinity
columns, cell counters, particle sorters, e.g., fluorescent
activated cell sorters, capillary electrophoresis, microscopes,
spectrophotometers, sample storage devices, and sample preparation
devices. Microfluidic devices are of particular interest in
connection with the systems described herein.
[0116] Exemplary analytical devices include devices useful for
size, shape, or deformability based separation of particles,
including filters, sieves, and deterministic separation devices,
e.g., those described in International Publication Nos. 2004/029221
and 2004/113877, Huang et al. Science 304, 987-990 (2004), U.S.
Publication No. 2004/0144651, U.S. Pat. Nos. 5,837,115 and
6,692,952, and U.S. Application Nos. 60/703,833 and 60/704,067;
devices useful for affinity capture, e.g., those described in
International Publication No. 2004/029221 and U.S. application Ser.
No. 11/071,679; devices useful for preferential lysis of cells in a
sample, e.g., those described in International Publication No.
2004/029221, U.S. Pat. No. 5,641,628, and U.S. Application No.
60/668,415; and devices useful for arraying cells, e.g., those
described in International Publication No. 2004/029221, U.S. Pat.
No. 6,692,952, and U.S. application Ser. Nos. 10/778,831 and
11/146,581. Two or more devices, either the same or different
devices, may be combined in series or integrated into a single
device, e.g., as described in International Publication No.
2004/029221.
[0117] In particular embodiments, the analytical device may be used
to enrich various analytes in a sample, e.g., for collection or
further analysis. Rare cells or components thereof can be retained
in the device, or otherwise enriched, compared to other cells as
described, e.g., in International Publication No. 2004/029221.
Exemplary rare cells include, depending on the sample, fetal cells
(e.g., fetal red blood cells); stem cells (e.g., undifferentiated);
cancer cells; immune system cells (host or graft); epithelial
cells; connective tissue cells; bacteria; fungi; viruses; and
pathogens (e.g., bacterial or protozoa). Such rare cells may be
isolated from samples including bodily fluids, e.g., blood, or
environmental sources, e.g., water or air samples. Fetal red blood
cells may be enriched from maternal peripheral blood, e.g., for the
purpose of determining sex and identifying aneuploidies or genetic
characteristics, e.g., mutations, in the developing fetus. Cancer
cells may also be enriched from peripheral blood for the purpose of
diagnosis and monitoring therapeutic progress. Bodily fluids or
environmental samples may also be screened for pathogens, e.g., for
coliform bacteria, blood borne illnesses such as sepsis, or
bacterial or viral meningitis. Rare cells also include cells from
one organism present in another organism, e.g., cells from a
transplanted organ. Analytes retained or otherwise enriched in the
device may, for example, be labeled, e.g., with fluorescent or
radioactive probes, subjected to chemical or genetic analysis (such
as fluorescent in situ hybridization), if biological, cultured, or
otherwise observed or probed.
[0118] Analytical devices may or may not include microfluidic
channels, i.e., may or may not be microfluidic devices. The
dimensions of the channels of the device into which analytes are
introduced may depend on the size or type of analytes employed.
Preferably, a channel in an analytical device has at least one
dimension (e.g., height, width, length, or radius) of no greater
than 10, 9.5, 9, 8.5, 8, 7.5, 7, 6.5, 6, 5.5, 5, 4.5, 4, 3.5, 3,
2.5, 2, 1.5, or 1 mm. Microfluidic devices employed in the systems
and methods described herein preferably have at least one dimension
of less than 1, 0.9, 0.8, 0.7, 0.6, 0.5, 0.4, 0.3, 0.2, 0.1, or
even 0.05 mm. The preferred dimensions of an analytical device can
be determined by one skilled in the art based on the desired
application.
[0119] Additional Components
[0120] In addition to an analytical device and a reservoir
containing a reagent capable of altering a magnetic property of an
analyte, devices of the invention may include additional elements,
e.g., for isolating, collection, manipulation, or detection. Such
elements are known in the art. For example, a device of the
invention (e.g., a device incorporating a deterministic device) may
also include components for other types of separation, including
affinity, magnetic, electrophoretic, centrifugal, and
dielectrophoretic separation. Devices of the invention may also
include a component for two-dimensional imaging of the output from
the device, e.g., an array of wells or a planar surface.
Preferably, devices described herein are employed in conjunction
with an affinity enrichment.
[0121] Devices of the invention may also be employed in conjunction
with other enrichment devices, either on the same device or in
different devices. Other enrichment techniques are described, e.g.,
in International Publication Nos. 2004/029221 and 2004/113877, U.S.
Pat. No. 6,692,952, and U.S. application Ser. Nos. 11/071,270,
11/071,679, and 60/668,415, each of which is incorporated by
reference.
Deterministic Separation
[0122] In certain embodiments, the analytical device is a device
that allows deterministic separation of an analyte based on the
hydrodynamic size of the analyte. Such devices will employ a
channel, e.g., a microfluidic channel, containing a structure that
enables deterministic separation. In one example, the channel
includes one or more arrays of obstacles that allow deterministic
lateral displacement of components of fluids. Such devices are
described, e.g., in Huang et al. Science 304, 987-990 (2004) and
U.S. Publication No. 20040144651, and U.S. Application No.
60/414,258. These devices may further employ an array of a network
of gaps, wherein a fluid passing through a gap is divided unequally
into subsequent gaps. In one embodiment, fluid passing through a
gap is divided unequally even though the gaps are identical in
dimensions. A flow carries particles to be separated through the
array of gaps. The flow is aligned at a small angle (flow angle)
with respect to a line-of-sight of the array. Particles having a
hydrodynamic size larger than a critical size migrate along the
line-of-sight in the array, whereas those having a hydrodynamic
size smaller than the critical size follow the flow in a different
direction. Flow in the device occurs under laminar flow
conditions.
[0123] The critical size is a function of several design
parameters. With reference to the obstacle array in FIG. 1, each
row of obstacles is shifted horizontally with respect to the
previous row by .DELTA..lamda., where .lamda. is the
center-to-center distance between the obstacles (FIG. 1A). The
parameter .DELTA..lamda./.lamda. (the "bifurcation
ratio,".epsilon.) determines the ratio of flow bifurcated to the
left of the next obstacle. In FIG. 1, .epsilon. is 1/3, for the
convenience of illustration. In general, if the flux through a gap
between two obstacles is .phi., the minor flux is .epsilon..phi.,
and the major flux is (1-.epsilon..phi.) (FIG. 2). In this example,
the flux through a gap is divided essentially into thirds (FIG.
1B). While each of the three fluxes through a gap weaves around the
array of obstacles, the average direction of each flux is in the
overall direction of flow. FIG. 1C illustrates the movement of an
analyte sized above the critical size (e.g., 4, 5, 6, 7, 8, 9, 10,
11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27,
28, 29, or 30 microns) through the array. Such analytes move with
the major flux, being transferred sequentially to the major flux
passing through each gap.
[0124] Referring to FIG. 2, the critical size is approximately
2R.sub.critical, where R.sub.critical is the distance between the
stagnant flow line and the obstacle. If the center of mass of a
particle, e.g., a cell, falls within R.sub.critical, the particle
would follow the major flux and move along the line-of-sight of the
array. R.sub.critical can be determined if the flow profile across
the gap is known (FIG. 3); it is the thickness of the layer of
fluids that would make up the minor flux. For a given gap size, d,
R.sub.critical can be tailored based on the bifurcation ratio,
.epsilon.. In general, the smaller .epsilon., the smaller
R.sub.critical.
[0125] In an array for deterministic lateral displacement,
particles of different shapes behave as if they have different
sizes (FIG. 4). For example, lymphocytes are spheres of .about.5
.mu.m diameter, and erythrocytes are biconcave disks of .about.7
.mu.m diameter, and .about.1.5 .mu.m thick. The long axis of
erythrocytes (diameter) is larger than that of the lymphocytes, but
the short axis (thickness) is smaller. If erythrocytes align their
long axes to a flow when driven through an array of obstacles by
the flow, their hydrodynamic size is effectively their thickness
(.about.1.5 .mu.m), which is smaller than lymphocytes. When an
erythrocyte is driven through an array of obstacles by a
hydrodynamic flow, it tends to align its long axis to the flow and
behave like a .about.1.5 .mu.m-wide particle, which is effectively
"smaller" than lymphocytes. The method and device may therefore
separate analytes according to their shapes, although the volumes
of the analytes could be the same. In addition, analytes having
different deformabilities behave as if they have different sizes
(FIG. 5). For example, two analytes having the same undeformed
shape may be separated by deterministic lateral displacement, as
one analyte may deform more readily than the other analyte when it
contacts an obstacle in the array and changes shape. Thus,
separation in the device may be achieved based on any parameter
that affects hydrodynamic size including the physical dimensions,
the shape, and the deformability of the analyte.
[0126] Referring to FIG. 6, feeding a mixture of analytes, e.g.,
cells, of different hydrodynamic sizes from the top of the array
and collecting the analytes at the bottom, as shown schematically,
can produce two products, an output containing analytes larger than
the critical size, 2R.sub.critical, and an output containing cells
smaller than the critical size. Either output or both outputs may
be collected, e.g., when fractionating a sample into two or more
sub-samples. Analytes larger than the gap size will get trapped
inside the array. Therefore, an array has a working size range.
Cells have to be larger than a cut-off size (2R.sub.critical) and
smaller than a maximum pass-through size (array gap size) to be
directed into the major flux. The "size range" of an array is
defined as the ratio of maximum pass-through size to cut-off
size.
[0127] Separation of Free, Unreacted Reagent from Altered
Analyte
[0128] Deterministic devices may be employed in order to separate
free, unreacted reagent from the altered analyte. As shown in FIG.
60, a labeling reagent such as an antibody may be pre-incubated
with an analyte (e.g., a cellular sample) prior to introduction to
or within the deterministic device. Desirably, the reagent
specifically reacts with the analyte of interest, e.g., a cell
population such as epithelial cells. Exemplary labeling reagents
include antibodies, quantum dots, phage, aptamers,
fluorophore-containing molecules, enzymes capable of carrying out a
detectable chemical reaction, sodium nitrite, or functionalized
beads. Generally, the reagent is smaller than the. analyte (e.g., a
cell) of interest, or the analyte of interest bound to a bead;
thus, when the sample combined with the reagent is introduced to
the device, unreacted reagent moves through the device undeflected,
while an altered analyte (e.g., an analyte bound to the reagent) is
deflected, thereby separating the unreacted reagent from the
altered analyte. Advantageously, this method achieves both size
separation and separation of free, unreacted reagent from the
analyte. Additionally, this method of separation facilitates
downstream sample analysis, if desired, without the need for a
release step or a potentially destructive method of analysis, as
described below.
[0129] FIG. 61 shows a particular case in which the enriched,
labeled sample contains a population of non-target cells that
co-separate with the target cells due to similar size. The
non-target cells do not interfere with downstream sample analysis
that relies on detection of the bound labeling reagent, because
this reagent binds selectively to the cells of interest.
[0130] Array Design
[0131] Deterministic separation may be achieved using an array of
gaps and obstacles in a channel. Exemplary configurations of such
arrays, bypass channels, and boundaries are described as
follows.
[0132] Single-stage array. In one embodiment, a single stage
contains an array of obstacles, e.g., cylindrical posts (FIG. 1D).
In certain embodiments, the array has a maximum pass-through size
that is several times larger than the cut-off size, e.g., when
separating white blood cells from red blood cells. This result may
be achieved using a combination of a large gap size d and a small
bifurcation ratio .epsilon.. In preferred embodiments, the
.epsilon. is at most 1/2, e.g., at most 1/3, 1/10, 1/30, 1/100,
1/300, or 1/1000. In such embodiments, the obstacle shape may
affect the flow profile in the gap; however, the obstacles can be
compressed in the flow direction, in order to make the array short
(FIG. 1E). Single stage arrays may include bypass channels as
described herein.
[0133] Multiple-stage arrays. In another embodiment, multiple
stages are employed to separate analytes over a wide size range. An
exemplary device is shown in FIG. 7. The device shown has three
stages, but any number of stages may be employed, and an array can
have as many stages as desired. Typically, the cut-off size in the
first stage is larger than the cut-off in the second stage, and the
first stage cut-off size is smaller than the maximum pass-through
size of the second stage (FIG. 8). The same is true for the
following stages. The first stage will deflect (and remove)
analytes, e.g., that would cause clogging in the second stage,
before they reach the second stage. Similarly, the second stage
will deflect (and remove) analytes that would cause clogging in the
third stage, before they reach the third stage.
[0134] As described, in a multiple-stage array, large analytes,
e.g., cells, that could cause clogging downstream are deflected
first, and these deflected analytes need to bypass the downstream
stages to avoid clogging. Thus, devices of the invention may
include bypass channels that remove output from an array. Although
described here in terms of removing analytes above the critical
size, a bypass channel may also be employed to remove output from
any portion of the array.
[0135] Different designs for bypass channels are as follows.
[0136] Single bypass channels. In this design, all stages share one
bypass channel, or there is only one stage. The physical boundary
of the bypass channel may be defined by the array boundary on one
side and a sidewall on the other (FIGS. 9-11). Single bypass
channels may also be employed with duplex arrays (FIG. 12).
[0137] Single bypass channels may also be designed, in conjunction
with an array, to maintain constant flux through a device (FIG.
13). As shown, the bypass channel has varying width designed
maintain constant flux through all the stages, so that the flow in
the channel does not interfere with the flow in the arrays. Such a
design may also be employed with an array duplex (FIG. 14). Single
bypass channels may also be designed in conjunction with the array
in order to maintain substantially constant fluidic resistance
through all stages (FIG. 15). Such a design may also be employed
with an array duplex (FIG. 16.)
[0138] Multiple bypass channels. In this design (FIG. 17), each
stage has its own bypass channel, and the channels are separated
from each other by sidewalls. Large analytes, e.g., cells are
deflected into the major flux to the lower right corner of the
first stage and then into in the bypass channel (bypass channel 1
in FIG. 17). Smaller cells that would not cause clogging in the
second stage proceed to the second stage, and cells above the
critical size of the second stage are deflected to the lower right
corner of the second stage and into in another bypass channel
(bypass channel 2 in FIG. 17). This design may be repeated for as
many stages as desired. In this embodiment, the bypass channels are
not fluidically connected, allowing for collection or other
manipulation of multiple fractions. The bypass channels do not need
to be straight or be physically parallel to each other (FIG. 18).
Multiple bypass channels may also be employed with duplex arrays
(FIG. 19).
[0139] Multiple bypass channels may be designed, in conjunction
with an array to maintain constant flux through a device (FIG. 20).
In this example, bypass channels are designed to remove an amount
of flow so the flow in the array is not perturbed, i.e.,
substantially constant. Such a design may also be employed with an
array duplex (FIG. 21). In this design, the center bypass channel
may be shared between the two arrays in the duplex.
[0140] Optimal boundary design. If the array were infinitely large,
the flow distribution would be the same at every gap. The flux
.phi. going through a gap would be the same, and the minor flux
would be .epsilon..phi. for every gap. In practice, the boundaries
of the array perturb this infinite flow pattern. Portions of the
boundaries of arrays may be designed to generate the flow pattern
of an infinite array. Boundaries may be flow-feeding, i.e., the
boundary injects fluid into the array or flow-extracting, i.e., the
boundary extracts fluid from the array.
[0141] A preferred flow-extracting boundary widens gradually to
extract .epsilon..phi. (represented by arrows in FIG. 22) from each
gap at the boundary (d=24 .mu.m, .epsilon.=1/60). For example, the
distance between the array and the sidewall gradually increases to
allow for the addition of .epsilon..phi. from each gap to the
boundary. The flow pattern inside this array is not affected by the
bypass channel because of the boundary design.
[0142] A preferred flow-feeding boundary narrows gradually to feed
exactly .epsilon..phi. (represented by arrows in FIG. 23) into each
gap at the boundary (d=24 .mu.m, .epsilon.=1/60). For example, the
distance between the array and the sidewall gradually decreases to
allow for the removal of .epsilon..phi. to each gap from the
boundary. Again, the flow pattern inside this array is not affected
by the bypass channel because of the boundary design.
[0143] A flow-feeding boundary may also be as wide as or wider than
the gaps of an array (FIG. 24) (d=24 .mu.m, .epsilon.=1/60). A wide
boundary may be desired if the boundary serves as a bypass channel,
e.g., to allow for collection of analytes. A boundary may be
employed that uses part of its entire flow to feed the array and
feeds .epsilon..phi. into each gap at the boundary (represented by
arrows in FIG. 24).
[0144] FIG. 25 shows a single bypass channel in a duplex array
(.epsilon.=1/10, d=8 .mu.m). The bypass channel includes two
flow-feeding boundaries. The flux across the dashed line 1 in the
bypass channel is .PHI..sub.bypass. A flow .phi. joins
.PHI..sub.bypass from a gap to the left of the dashed line. The
shapes of the obstacles at the boundaries are adjusted so that the
flows going into the arrays are .epsilon..phi. at each gap at the
boundaries. The flux at dashed line 2 is again
.PHI..sub.bypass.
[0145] On-chip Flow Resistor for Defining and Stabilizing Flow
[0146] Deterministic separation may also employ fluidic resistors
to define and stabilize flows within an array and to also define
the flows collected from the array. FIG. 26 shows a schematic of
planar device; a sample, e.g., blood, inlet channel, a buffer inlet
channel, a waste outlet channel, and a product outlet channel are
each connected to an array. The inlets and outlets act as flow
resistors. FIG. 26 also shows the corresponding fluidic resistances
of these different device components.
[0147] Flow Definition within the Array
[0148] FIGS. 27 and 28 show the currents and corresponding widths
of the sample and buffer flows within the array when the device has
a constant depth and is operated with a given pressure drop. The
flow is determined by the pressure drop divided by the resistance.
In this particular device, I.sub.blood and I.sub.buffer are
equivalent, and this determines equivalent widths of the blood and
buffer streams in the array.
[0149] Definition of Collection Fraction
[0150] By controlling the relative resistance of the product and
waste outlet channels, one can modulate the collection tolerance
for each fraction. For example, in this particular set of
schematics, when R.sub.product is greater than R.sub.waste, a more
concentrated product fraction will result at the expense of a
potentially increased loss to and dilution of waste fraction.
Conversely, when R.sub.product is less than R.sub.waste, a more
dilute and higher yield product fraction will be collected at the
expense of potential contamination from the waste stream.
[0151] Flow Stabilization
[0152] Each of the inlet and outlet channels can be designed so
that the pressure drops across the channels are appreciable to or
greater than the fluctuations of the overall driving pressure. In
typical cases, the inlet and outlet pressure drops are 0.001 to
0.99 times the driving pressure.
[0153] Multiplexed Deterministic Arrays
[0154] Deterministic separation may be achieved using multiplexed
deterministic arrays. Putting multiple arrays on one device
increases sample-processing throughput, and allows for parallel
processing of multiple samples or portions of the sample for
different fractions or manipulations. Multiplexing is further
desirable for preparative applications. The simplest multiplex
device includes two devices attached in series, i.e., a cascade.
For example, the output from the major flux of one device may be
coupled to the input of a second device. Alternatively, the output
from the minor flux of one device may be coupled to the input of
the second device.
[0155] Duplexing. Two arrays can be disposed side-by-side, e.g., as
mirror images (FIG. 29). In such an arrangement, the critical size
of the two arrays may be the same or different. Moreover, the
arrays may be arranged so that the major flux flows to the boundary
of the two arrays, to the edge of each array, or a combination
thereof. Such a multiplexed array may also contain a central region
disposed between the arrays, e.g., to collect analytes above the
critical size or to alter the sample, e.g., through buffer
exchange, reaction, or labeling.
[0156] Multiplexing on a device. In addition to forming a duplex,
two or more arrays that have separated inputs may be disposed on
the same device (FIG. 30A). Such an arrangement could be employed
for multiple samples, or the plurality of arrays may be connected
to the same inlet for parallel processing of the same sample. In
parallel processing of the same sample, the outlets may or may not
be fluidically connected. For example, when the plurality of arrays
has the same critical size, the outlets may be connected for high
throughput samples processing. In another example, the arrays may
not all have the same critical size or the analytes in the arrays
may not all be treated in the same manner, and the outlets may not
be fluidically connected.
[0157] Multiplexing may also be achieved by placing a plurality of
duplex arrays on a single device (FIG. 30B). A plurality of arrays,
duplex or single, may be placed in any possible three-dimensional
relationship to one another.
[0158] Exemplary multiple stage devices. In addition to those
described above, the following exemplary multiple stage
deterministic devices may also be included in devices of the
invention. For example, FIG. 58A shows the "cascade" configuration,
in which outlet 1 of one device is joined to a sample inlet of a
second device. This allows for an initial separation step using the
first device so that the sample introduced to the second device is
already enriched for cells of interest. The two devices may have
either identical or different critical sizes, depending on the
intended application.
[0159] In FIG. 60, an unlabeled cellular sample is introduced to
the first device in the cascade via a sample inlet, and a buffer
containing labeling reagent is introduced to the first device via
the fluid inlet. Epithelial cells are deflected and emerge from the
center outlet in the buffer containing labeling reagent. This
enriched labeled sample is then introduced to the second device in
the cascade via a sample inlet, while buffer is added to the second
device via the fluid inlet. Further enrichment of target cells and
separation of free labeling reagent is achieved, and the enriched
sample may be further analyzed. Alternatively, labeling reagent may
be added directly to the sample emerging from the center outlet of
the first device before introduction to the second device. The use
of a cascade configuration may allow for the use of a smaller
quantity or a higher concentration of labeling reagent at less
expense than the single-device configuration of FIG. 60; in
addition, any nonspecific binding that may occur is significantly
reduced by the presence of an initial separation step using the
first device.
[0160] An alternative configuration of two or more device stages is
the "bandpass" configuration. FIG. 58B shows this configuration, in
which outlet 2 of one device is joined to a sample inlet of a
second device. This allows for an initial separation step using the
first device so that the sample introduced to the second device
contains cells that remained undeflected within the first device.
This method may be useful when the cells of interest are not the
largest cells in the sample; in this instance, the first stage may
be used to reduce the number of large non-target cells by
deflecting them to the center outlet. As in the cascade
configuration, the two devices may have either identical or
different critical sizes, depending on the intended application.
For example, different critical sizes are appropriate for an
application requiring the separation of epithelial cells, in
comparison with an application requiring the separation of smaller
endothelial cells.
[0161] In FIG. 66, a cellular sample pre-incubated with labeling
reagent is introduced to a sample inlet of the first device of the
bandpass configuration, and a buffer is introduced to the first
device via the fluid inlet. The first device is disposed in such a
manner that large, non-target cells are deflected and emerge from
the center outlet, while a mixture of target cells, small
non-target cells, and labeling reagent emerge from outlet 2 of the
first device. This mixture is then introduced to the second device
via a sample inlet, while buffer is added to the second device via
the fluid inlet. Enrichment of target cells and separation of free
labeling reagent is achieved, and the enriched sample may be
further analyzed. Non-specific binding of labeling reagent to the
deflected cells in the first stage is acceptable in this method, as
the deflected cells and any bound labeling reagent are removed from
the system.
[0162] In any of the multiple deterministic device configurations
described above, the devices and the connections joining them may
be integrated into a single device. For example, a single cascade
device including two or more stages is possible, as is a single
bandpass device including two or more stages. The output of the
multiple stages is then coupled to the input of the reservoir.
[0163] Small-footprint arrays. Deterministic devices may also
feature a small footprint. Reducing the footprint of an array can
lower cost, and reduce the number of collisions with obstacles to
eliminate any potential mechanical damage or other effects to
analytes. The length of a multiple stage array can be reduced if
the boundaries between stages are not perpendicular to the
direction of flow. The length reduction becomes significant as the
number of stages increases. FIG. 31 shows a small-footprint
three-stage array.
[0164] Reservoir Containing a Reagent That Alters a Magnetic
Property
[0165] An analytical device (e.g., a deterministic device) is
coupled to, or otherwise includes, a reservoir containing a reagent
(e.g., magnetic particles having a binding moiety or sodium
nitrite) capable of altering a magnetic property of an analyte
(e.g., a cell such as a red blood cell). The reservoir may include
a channel, e.g., a microfluidic channel, a tube, or any other
container capable of receiving the analyte and contacting it with
the reagent. The reservoir may be separable from the analytical
device or may be integrated with it. Mixing of the reagent with the
analyte may occur by any means including diffusion, mechanical
mixing, or turbulent flow. The reagent may be stored dry in the
reservoir and liquefied upon introduction of a sample or stored in
solution and mixed with the sample. In another embodiment, the
reagent is added continuously or in a discrete bolus to the
reservoir concomitant with the delivery of the sample.
[0166] The reservoir may also include structures that allow for the
separation of the altered analyte from the unreacted reagent. For
example, deterministic separation may be employed for this purpose
as described herein. Alternatively, filters, rinses, or other means
may be employed. Such a structure may or may not be included as
part of the reservoir or analytical device.
[0167] The reservoir may also include an apparatus useful in
enriching or depleting a sample in the magnetically altered
analyte. Such devices are described herein and include channels
(e.g., microfluidic channels) which, in some embodiments include a
magnetic field generator or a channel containing a magnet such as a
MACS column (e.g., an MS or LD column from Miltenyi Biotec, Inc.,
Auburn, Calif.).
[0168] In one embodiment, the reservoir includes a channel having a
magnetic region to which a magnetic particle can magnetically
attach, thereby creating a textured surface with which an analyte
passing through the channel can come into contact. Through the
appropriate choice of magnetic particle size and shape relative to
the dimensions of the channel, a texture that enhances interactions
between an analyte and the bound magnetic particles can be
provided. The magnetic particles may be coated with appropriate
capture moieties such as antibodies (e.g., anti-CD71, anti-CD36,
anti-CD45, anti-GPA, anti-antigen i, anti-CD34, anti-fetal
hemoglobin, anti-EpCAM, anti-E-cadherin, or anti-Muc-1) that can
bind to an analyte through affinity mechanisms. The magnetic
particles can be disposed uniformly throughout a device or in
spatially resolved regions. In addition, magnetic particles may be
used to create structure within the device. For example, two
magnetic regions on opposite sides of a channel can be used to
attract magnetic particles to form a "bridge" linking the two
regions. The magnetic particles can be magnetically attached to
hard magnetic regions of the channel or to soft magnetic regions
that are actuated to produce a magnetic field.
[0169] In another embodiment, the sample is treated with a reagent
that includes magnetic particles prior to application of a magnetic
field. As described above, the magnetic particles may be coated
with appropriate capture moieties such as antibodies to which an
analyte can bind. Application of a magnetic field to the treated
sample will selectively bind an analyte bound to magnetic particles
in the reservoir.
[0170] In yet another embodiment, a sample is combined with a
reagent that alters an intrinsic magnetic property of an analyte.
The altered analyte may be rendered more magnetically responsive,
less magnetically responsive, or may be rendered magnetically
unresponsive by the reagent as compared to the unaltered analyte.
In one example, a sample (e.g., a maternal blood sample that has,
for example, been depleted of maternal red blood cells) containing
fetal red blood cells (fRBCs) is treated with sodium nitrite,
thereby causing oxidation of fetal hemoglobin contained within the
fRBCs. This oxidation alters the magnetic responsiveness of the
fetal hemoglobin relative to other components of the sample, e.g.,
maternal white blood cells, thereby allowing separation of the
fRBCs. Any cell containing magnetically responsive components such
as iron found in hemoglobin (e.g., adult or fetal), myoglobin, or
cytochromes (e.g., cytochrome C) may be modified to alter intrinsic
magnetic responsiveness of an analyte such as a cell, or a
component thereof (e.g., an organelle).
[0171] For any of the above embodiments, any source of a magnetic
field may be employed in the invention and may include hard
magnets, soft magnets, or a combination thereof. In one embodiment,
a spatially nonuniform permanent magnet or electromagnet may be
used to create organized and in some cases periodic arrays of
magnetic particles within an otherwise untextured microfluidic
channel (Deng et al. Applied Physics Letters, 78, 1775 (2001)). An
electromagnet may be employed to create a non-uniform magnetic
field in a device. The non-uniform filed creates regions of higher
and lower magnetic field strength, which, in turn, will attract
magnetic particles in a periodic arrangement within the device.
Other external magnetic fields may be employed to create magnetic
regions to which magnetic particles attach. A hard magnetic
material may also be used in the fabrication of the device, thereby
obviating the need for electromagnets or external magnetic fields.
In one embodiment, the device contains a plurality of channels
having magnetic regions, e.g., to increase volumetric throughput.
Further, these channels may be stacked vertically.
[0172] In the above embodiments, an analyte bound to a magnet can
be released from defined locations within the channel, e.g., by
increasing the overall flow rate of the fluid flowing through the
device, decreasing the magnetic field, or through some combination
of the two.
[0173] An example of a reservoir is shown in FIG. 74, which
illustrates a reservoir geometry and functional process flow to
isolate and then release target analytes, e.g., cells or molecules,
from a complex mixture. As shown, the reservoir contains obstacles
that extend from one channel surface toward the opposing channel
surface. The obstacles may or may not extend the entire distance
across the channel. In the present example, the obstacles are
magnetic (e.g., contain hard or soft magnetic materials or are
locations of high magnetic field in a non-uniform field) and
attract and retain magnetic particles, which may be coated with
capture moieties or may be cells attracted to a magnetic field. The
geometry of the reservoir, the distribution, shape, size of the
obstacles and the flow parameters can be altered to optimize the
efficiency of the enrichment of an analyte of interest, for
example, by attracting an analyte bound to a magnetic particle with
a capture moiety (e.g., as described in International Publication
No. 2004/029221). In one specific example, an anodic lidded silicon
wafer with microtextured magnetic obstacles of varying shapes
(cylindrical, rectangular, trapezoidal, or pleomorphic) and size
(10-999 microns) are arranged uniquely (spacing and density varied
across equilateral triangular, diagonal, and random array
distribution) to maximize the collision frequency of analytes,
altered or not, with the obstacles within the confines of a
continuous perfusion flow stream. The exact geometry of the
magnetic obstacles and the distribution of obstacles may depend on
the type of analytes being isolated, enriched, or purified.
[0174] FIG. 75 illustrates an example of reservoir fabrication and
functionalization. The magnetized obstacles enable post-packaging
modification of the reservoir. This is a very significant
improvement over existing art. The incompatibility of semiconductor
processing parameters (high heat, or solvent sealers to bond the
lid) with capture moieties (sensitive to temperature and inorganic
and organic solvents) makes this device universal and compatible
for functionalization with all capture moieties. Retention of the
capture moieties on the obstacles (e.g., posts) by use of magnetic
fields, is an added advantage over prior art that uses complex
surface chemistry for immobilization. The reservoir enables the end
user to easily and rapidly charge the reservoir with a capture
moiety, or mixture of capture moieties, of choice thereby
increasing the versatility of use. On-demand and `just-in-time` one
step functionalization is enabled by this reservoir, thereby
circumventing issues of on-the-shelf stability of the capture
moieties if they were chemically cross-linked at production. The
capture moieties that can be loaded and retained on the obstacles
include, but not limited to, all of the cluster of differentiation
(CD) receptors on mammalian cells, synthetic and recombinant
ligands for cell receptors, and any other organic, inorganic
molecule, or compound of interest that can be attached to any
magnetic particle.
Reagents Capable of Altering a Magnetic Property
[0175] Such reagents include any reagent that is capable of
altering a magnetic property of an analyte in a sample. The exact
nature of the reagent will depend on the nature of the analyte.
Exemplary reagents include agents that oxidize or reduce transition
metals, magnetic beads capable of binding to an analyte, or
reagents that are capable of chelating or otherwise binding iron,
or other magnetic materials or particles. Specific reagents include
sodium nitrite. The reagent may act to alter the magnetic
properties of an analyte to enable or increase its attraction to a
magnetic field, to enable or increase its repulsion to a magnetic
field, or to eliminate a magnetic property such that the analyte is
unaffected by a magnetic field.
[0176] Any particle that responds to a magnetic field may be
employed in the devices and methods of the invention. Desirable
particles are those that have surface chemistry that can be
chemically or physically modified, e.g., by chemical reaction,
physical adsorption, entanglement, or electrostatic interaction.
Magnetic particles of the present invention can come in any size
and/or shape. In some embodiments, a magnetic particle has a
diameter of less than 500 nm, 400 nm, 300 nm, 200 nm, 100 nm, 90
nm, 80 nm, 70 nm, 60 nm or 50 nm. In some embodiments, a magnetic
particle has a diameter that is between 10-1000 nm, 20-800 nm,
30-600 nm, 40-400 nm, or 50-200 nm. In some embodiments, a magnetic
particle has a diameter of more than 10 nm, 50 nm, 100 nm, 200 nm,
500 nm, 1000 nm, or 5000 nm. The magnetic particles can be dry in
liquid form. Mixing of a fluid sample with a second liquid medium
containing magnetic particles can occur by any means known in the
art.
[0177] Capture moieties can be bound to magnetic particles by any
means known in the art. Examples include chemical reaction,
physical adsorption, entanglement, or electrostatic interaction.
The capture moiety bound to a magnetic particle will depend on the
nature of the analyte targeted. Examples of capture moieties
include, without limitation, proteins (such as antibodies, avidin,
and cell-surface receptors), charged or uncharged polymers (such as
polypeptides, nucleic acids, and synthetic polymers), hydrophobic
or hydrophilic polymers, small molecules (such as biotin, receptor
ligands, and chelating agents), and ions. Such capture moieties can
be used to specifically bind cells (e.g., bacterial, pathogenic,
fetal cells, fetal blood cells, cancer cells, and blood cells),
organelles (e.g., nuclei), viruses, peptides, protein, polymers,
nucleic acids, supramolecular complexes, other biological molecules
(e.g., organic or inorganic molecules), small molecules, ions, or
combinations or fragments thereof. Specific examples of capture
moieties include anti-CD71, anti-CD36, anti-GPA, anti-EpCAM,
anti-E-cadherin, anti-Muc-1, and holo-transferrin. In another
embodiment, the capture moiety is fetal cell specific.
Magnetic Separation
[0178] Once a magnetic property of an analyte has been altered,
that alteration may be used to effect an isolation, enrichment, or
depletion of the analyte relative to other constituents of a
sample. The isolation, enrichment, or depletion may include
positive selection, i.e., a desired analyte is attracted to a
magnetic field, or it may employ negative selection, i.e., a
desired analyte is not attracted to the magnetic field. In either
case, the population of analytes containing the desired analytes
may be collected for analysis or further processing.
[0179] The device used to perform the magnetic separation may be
any device that can produce a magnetic field. In one embodiment, a
MACS column is used to effect separation of the magnetically
altered analyte. If the analyte is rendered magnetically responsive
by the reagent (e.g., using any reagent described herein), it may
bind to the MACS column, thereby permitting enrichment of the
desired analyte relative to other constituents of the sample.
[0180] In another embodiment, separation may be achieved using a
device, typically microfluidic, that contains a plurality of
magnetic obstacles. If an analyte in the sample is modified to be
magnetically responsive (e.g., through a reagent that enhances an
intrinsic magnetic property of the analyte or by binding of a
magnetically responsive particle to the analyte), the analyte may
bind to the obstacles, thereby permitting enrichment of the bound
analyte. Alternatively, negative selection may be employed. In this
example, the desired analyte may be rendered magnetically
unresponsive, or an undesired analyte may be rendered magnetically
responsive or bound to a magnetically responsive particle. In this
case, an undesired analyte or analytes will be retained on the
obstacles whereas the desire analyte will not, thus enriching the
sample in the desired analyte.
[0181] Magnetic regions of the device can be fabricated with either
hard or soft magnetic materials, such as, but not limited to, rare
earth materials, neodymium-iron-boron, ferrous-chromium-cobalt,
nickel-ferrous, cobalt-platinum, and strontium ferrite. Portions of
the device may be fabricated directly out of magnetic materials, or
the magnetic materials may be applied to another material. The use
of hard magnetic materials can simplify the design of a device
because they are capable of generating a magnetic field without
other actuation. Soft magnetic materials, however, enable release
and downstream processing of bound analytes simply by demagnetizing
the material. Depending on the magnetic material, the application
process can include cathodic sputtering, sintering, electrolytic
deposition, or thin-film coating of composites of polymer
binder-magnetic powder. A preferred embodiment is a thin film
coating of micromachined obstacles (e.g., silicon posts) by spin
casting with a polymer composite, such as polyimide-strontium
ferrite (the polyimide serves as the binder, and the strontium
ferrite as the magnetic filler). After coating, the polymer
magnetic coating is cured to achieve stable mechanical properties.
After curing, the device is briefly exposed to an external
induction field, which governs the preferred direction of permanent
magnetism in the device. The magnetic flux density and intrinsic
coercivity of the magnetic fields from the obstacles can be
controlled by the % volume of the magnetic filler.
[0182] In another embodiment, an electrically conductive material
is micropatterned on the outer surface of an enclosed microfluidic
device. The pattern may consist of a single, electrical circuit
with a spatial periodicity of approximately 100 microns. By
controlling the layout of this electrical circuit and the magnitude
of the electrical current that passes through the circuit, one can
develop periodic regions of higher and lower magnetic strength
within the enclosed microfluidic device.
[0183] The magnetic field can be adjusted to influence supra and
paramagnetic particles with magnetic mass susceptibility ranging
from 0.1-200.times.10.sup.-6 m.sup.3/kg. The paramagnetic particles
of use can be classified based on size: particulates (1-5 .mu.m in
the size of a cell diameter); colloidal (on the order of 100 nm);
and molecular (on the order of 2-10 nm). The fundamental force
acting on a paramagnetic entity is: F b = 1 2 .times. .mu. o
.times. .DELTA..chi. .times. .times. V G .times. .gradient. B 2
##EQU1## where F.sub.b is the magnetic force acting on the
paramagnetic entity of volume V.sub.b, .DELTA..chi. is the
difference in magnetic susceptibility between the magnetic bead,
.chi.b, and the surrounding medium, .chi.f, .mu..sub.o is the
magnetic permeability of free space, B is the external magnetic
field, and .gradient. is the gradient operator. The magnetic field
can be controlled and regulated to enable attraction and retention
of a wide spectrum of particulate, colloidal, and molecular
paramagnetic entities typically coupled to capture moieties. Uses
of Devices of the Invention
[0184] As described, the invention features analytical devices for
the enrichment of analytes such as particles, including bacteria,
viruses, fungi, cells, cellular components, viruses, nucleic acids,
proteins, and protein complexes. In addition to altering a magnetic
property, a device may also be used to effect various manipulations
on analytes in a sample. Such manipulations include enrichment or
concentration of an analyte, including size-based fractionization,
or alteration of the analyte itself or the fluid carrying the
analyte. Preferably, a device is employed to enrich rare analytes
from a heterogeneous mixture or to alter a rare analyte, e.g., by
exchanging the liquid in the sample or by contacting an analyte
with a reagent. Such devices allow for a high degree of enrichment
with limited stress on a potentially fragile analyte such a cell,
where devices of the invention provide reduced mechanical lysis or
intracellular activation of cells.
[0185] Although primarily described in terms of cells, the devices
of the invention may be employed with any analyte whose size allows
for separation in a device of the invention.
[0186] Deterministic devices, and other analytical devices, may be
employed in concentrated samples, e.g., where analytes are
touching, hydrodynamically interacting with each other, or exerting
an effect on the flow distribution around another analyte. For
example, a deterministic device can separate white blood cells from
red blood cells in whole blood from a human donor. Human blood
typically contains .about.45% of cells by volume. Cells are in
physical contact and/or coupled to each other hydrodynamically when
they flow through the array. FIG. 32 shows schematically that cells
densely packed inside an array can physically interact with each
other.
[0187] As described, the devices and methods of the invention may
involve separating from a sample one or more analytes based on an
intrinsic magnetic property of the one or more analytes. In one
embodiment, the sample is treated with a reagent that alters a
magnetic property of the analyte. The alteration may be mediated by
a magnetic particle or may be mediated by a reagent that alters an
intrinsic magnetic property of the analyte. A magnetically altered
analyte may then bind to a surface of the device, and desired
analytes (e.g., rare cells such as fetal cells, pathogenic cells,
cancer cells, or bacterial cells) in a sample may be retained in
the device. Thus, the analyte of interest may then bind to the
surfaces of the device. In another embodiment, desired analytes are
retained in the device through size-, shape- or deformability-based
mechanisms. In another embodiment, negative selection is employed,
where a desired analyte is not bound to the device. Any of the
embodiments may uses a MACS column for retention of an analyte
(e.g., an analyte bound to a magnetic particle).
[0188] In embodiments of the invention using positive selection, it
is desirable that at least 60%, 70%, 80%, 90%, 95%, 98%, or 99% of
the analytes are retained in the device. The surfaces of the device
are desirably designed to minimize nonspecific binding of
non-target analytes. For example, at least 99%, 98%, 95%, 90%, 80%,
or 70% of non-target analytes are not retained in the device. The
selective retention in the device can result in the separation of a
specific analyte population from a mixture, e.g., blood, sputum,
urine, and soil, air, or water samples.
[0189] The selective retention of analytes may be obtained by
introduction of magnetic particles (e.g., attached to obstacles
present in the device or manipulated to create obstacles to
increase surface area for an analyte to interact with to increase
the likelihood of binding) into a device of the invention. Capture
moieties may be bound to the magnetic particles to effect specific
binding of a target analyte. In another embodiment, the magnetic
particles may be disposed such as to only allow analytes of a
selected size, shape, or deformability to pass through the device.
Combinations of these embodiments are also envisioned. For example,
a device may be configured to retain certain analytes based on size
and others based on binding. In addition, a device may be designed
to bind more than one analyte of interest, e.g., in a serial,
parallel, or interspersed arrangement of regions within a device or
where two or more capture moieties are disposed on the same
magnetic particle or on adjacent particles, e.g., bound to the same
obstacle or region. Further, multiple capture moieties that are
specific for the same analyte (e.g., anti-CD71 and anti-CD36) may
be employed in the device, either on the same or different magnetic
particles, e.g., disposed on the same or different obstacle or
region.
[0190] The flow conditions in the device are typically such that
the analytes are very gently handled in the device to prevent
damage. Positive pressure or negative pressure pumping or flow from
a column of fluid may be employed to transport analytes into and
out of the microfluidic devices of the invention. The device
enables gentle processing, while maximizing the collision frequency
of each analyte with one or more of the magnetic particles. The
target analytes interact with any capture moieties on collision
with the magnetic particles. The capture moieties can be
co-localized with obstacles as a designed consequence of the
magnetic field attraction in the device. This interaction leads to
capture and retention of the target analytes in defined locations.
Captured analyte can be released by demagnetizing the magnetic
regions retaining the magnetic particles. For selective release of
analytes from regions, the demagnetization can be limited to
selected obstacles or regions. For example, the magnetic field can
be designed to be electromagnetic, enabling turn-on and turn-off
off the magnetic fields for each individual region or obstacle at
will. In other embodiments, the particles can be released by
disrupting the bond between the analyte and the capture moiety,
e.g., through chemical cleavage or interruption of a noncovalent
interaction, or by decreasing the magnetic responsiveness of the
bound analyte. For example, some ferrous particles are linked to
monoclonal antibody via a DNA linker; the use of DNAse can cleave
and release the analytes from the ferrous particle. Alternatively,
an antibody fragmenting protease (e.g., papain) can be used to
engineer selective release. Increasing the sheer forces on the
magnetic particles can also be used to release magnetic particles
from magnetic regions, especially hard magnetic regions. In other
embodiments, the captured analytes are not released and can be
analyzed or further manipulated while retained.
[0191] FIG. 76 illustrates an example of a reservoir designed to
capture and isolate cells expressing the transferrin receptor from
a complex mixture. Monoclonal antibodies to CD71 receptor are
readily available off-the-shelf covalently coupled to magnetic
materials, such as, but not limited to, ferrous doped polystyrene
and ferroparticles or ferro-colloids (e.g., from Miltenyi and
Dynal). The mAB to CD71 bound to magnetic particles is flowed into
the reservoir. The antibody-coated particles are attracted to the
obstacles (e.g., posts), floor, and walls and are retained by the
strength of the magnetic field interaction between the particles
and the magnetic field. The particles between the obstacles and
those loosely retained with the sphere of influence of the local
magnetic fields away from the obstacles, are removed by a rinse
(the flow rate can be adjusted such that the hydrodynamic shear
stress on the particles away from the obstacles is larger than the
magnetic field strength).
[0192] FIG. 77 is a preferred embodiment for application of the
reservoir to capture and release CD71+ cells from a complex
mixture, e.g., blood, using holo-transferrin. Holo-transferrin is
rich in iron content, commercially available, and has higher
affinity constants and specificity of interaction with the CD71
receptor than its counterpart monoclonal antibody. The iron coupled
to the transferrin ligand serves the dual purpose of retaining the
conformation of the ligand for binding with the cell receptor, and
as a molecular paramagnetic element for retaining the ligand on the
obstacles.
[0193] In addition to the above embodiments, devices of the
invention can be used for isolation and detection of blood borne
pathogens, bacterial and viral loads, airborne pathogens
solubilized in aqueous medium, pathogen detection in food industry,
and environmental sampling for chemical and biological hazards.
Additionally, the magnetic particles can be co-localized with a
capture moiety and a candidate drug compound. Capture of a cell of
interest can further be analyzed for the interaction of the
captured cell with the immobilized drug compound. A device can thus
be used to both isolate sub-populations of cells from a complex
mixture and assay their reactivity with candidate drug compounds
for use in the pharmaceutical drug discovery process for high
throughput and secondary cell-based screening of candidate
compounds. In other embodiments, receptor-ligand interaction
studies for drug discovery can be accomplished in the device by
localizing the capture moiety, i.e., the receptor, on a magnetic
particle, and flowing in a complex mixture of candidate ligands (or
agonists or antagonists). The ligand of interest is captured, and
the binding event can be detected, e.g., by secondary staining with
a fluorescent probe. This embodiment enables rapid identification
of the absence or presence of known ligands from complex mixtures
extracted from tissues or cell digests or identification of
candidate drug compounds.
[0194] Enrichment
[0195] In one embodiment, devices of the invention are employed to
produce a sample enriched in a desired analyte, e.g., based at
least in part on hydrodynamic size. Applications of such enrichment
include concentrating of an analyte such as particle including rare
cells, and size fractionization, e.g., size filtering (selecting
analytes in a particular size range). Devices may also be used to
enrich components of cells such as organelles (e.g., nuclei).
Desirably, the devices and methods of the invention retain at least
1%, 10%, 30%, 50%, 75%, 80%, 90%, 95%, 98%, or 99% of the desired
particles compared to the initial mixture, while potentially
enriching the desired particles by a factor of at least 1, 10, 100,
1,000, 10,000, 100,000, or even 1,000,000 relative to one or more
non-desired particles. The enrichment may also result in a dilution
of the enriched analytes compared to the original sample, although
the concentration of the enriched analytes relative to other
particles in the sample has increased. Preferably, the dilution is
at most 90%, e.g., at most 75%, 50%, 33%, 25%, 1 0%, or 1%.
[0196] In another embodiment, a device of the invention is used to
produce a sample enriched in a rare analyte. In general, a rare
analyte is an analyte that is present as less than 10%, 9%, 8%, 7%,
6%, 5%, 4%, 3%, 2%, 1%, 0.1%, 0.01%, 0.001%, 0.0001%, 0.00001%, or
0.000001% of all analytes in a sample or whose mass is less than
10%, 9%, 8%, 7%, 6%, 5%, 4%, 3%, 2%, 1%, 0.1%, 0.01%, 0.001%,
0.0001%, 0.00001%, or 0.000001% of total mass of a sample of a
sample. Exemplary rare analytes include, depending on the sample,
fetal cells, stem cells (e.g., undifferentiated), cancer cells,
immune system cells (host or graft), epithelial cells, connective
tissue cells, bacteria, fungi, viruses, and pathogens (e.g.,
bacterial or protozoa). Such rare analytes may be isolated from
samples including bodily fluids, e.g., blood, or environmental
sources, e.g., pathogens in water samples. Fetal red blood cells
may be enriched from maternal peripheral blood, e.g., for the
purpose of determining sex and identifying aneuploidies or genetic
characteristics, e.g., mutations, in the developing fetus.
Circulating tumor cells, which are of epithelial cell type and
origin, may also be enriched from peripheral blood for the purpose
of diagnosis and monitoring therapeutic progress. Circulating
endothelial cells may also be similarly enriched from peripheral
blood.
[0197] Bodily fluids or environmental samples may also be screened
for pathogens, e.g., for coliform bacteria, blood borne illnesses
such as sepsis, or bacterial or viral meningitis. Rare cells also
include cells from one organism present in another organism, e.g.,
in cells from a transplanted organ.
[0198] In addition to enrichment of a rare analyte, a device may be
employed for preparative applications. An exemplary preparative
application includes generation of cell packs from blood. In one
example, a device may be configured to produce fractions enriched
in platelets, red blood cells, and white cells by deterministic
deflection. By using multiplexed or multistage deterministic
devices, all three cellular fractions may be produced in parallel
or in series from the same sample. In other embodiments, the device
may be employed to separate nucleated from non-nucleated cells,
e.g., from cord blood sources.
[0199] Using devices which incorporate deterministic deflection is
advantageous in situations where the particles being enriched are
subject to damage or other degradation. As described herein,
deterministic devices may be designed to enrich analytes (e.g., a
cell) with a minimum number of collisions between the analyte and
obstacles. This minimization reduces mechanical damage to the
analytes (e.g., a cell) and, in the case of cells, also prevents
intracellular activation caused by the collisions. Gentle handling
preserves the limited number of rare analytes in a sample, in the
case of cells, prevents rupture leading to contamination or
degradation by intracellular components, and prevents maturation or
activation of cells, e.g., stem cells or platelets. In preferred
embodiments, the analyte is enriched such that fewer than 30%, 10%,
5%, 1%, 0.1%, or even 0.01% are damaged (e.g., activated or
mechanically lysed).
[0200] FIG. 33 shows a typical size distribution of cells in human
peripheral blood. The white blood cells range from .about.4 .mu.m
to .about.18 .mu.m, whereas the red blood cells are .about.1.5
.mu.m (short axis). A deterministic device designed to separate
white blood cells from red blood cells typically has a cut-off size
of 2 to 4 .mu.m and a maximum pass-through size of greater than 18
.mu.m.
[0201] In an alternative embodiment, a deterministic device may
function as a detector for abnormalities in red blood cells. The
deterministic principle of sorting enables a predictive outcome of,
for example, % of enucleated cells deflected in the device. In a
disease state, such as malarial infection or sickle cell anemia,
the distortion in shape and flexibility of the red cells would
significantly change the % cells deflected. This change can be
monitored as a first level sentry to alert to the potential of a
diseased physiology to be followed by microscopy examination of
shape and size of red cells to assign the disease. The method is
also generally applicable monitoring for any change in flexibility
of particles in a sample.
[0202] In an alternative embodiment, a deterministic device may
function as a detector for platelet aggregation. The deterministic
principle of sorting enables a predictive outcome of % free
platelets deflected in the device. Activated platelets would form
aggregates and the aggregates would be deflected. This change can
be monitored as a first level sentry to alert the compromised
efficacy of a platelet pack for reinfusion. The method is also
generally applicable monitoring for any change in size, e.g.,
through agglomeration, of particles in a sample.
[0203] FIG. 57A shows the operation of a deterministic device for
purposes of enrichment. A cellular sample is added through a sample
inlet of the device, and buffer medium is added through the fluid
inlet. Cells below the critical size move through the device
undeflected, emerging from the edge outlets in their original
sample medium. Cells above the critical size, e.g., epithelial
cells, are deflected and emerge from the center outlet contained in
the buffer medium added through the fluid inlet. Operation of the
device thus produces samples enriched in cells above and below the
critical size. Because epithelial cells are among the largest cells
in the bloodstream, the size and geometry of the gaps of the device
may be chosen so as to direct virtually all other cell types to the
edge outlets, while producing a sample from the center outlet that
is substantially enriched in epithelial cells after a single pass
through the device.
[0204] A deterministic device included in the invention need not be
duplexed as shown in FIG. 57A in order to operate as described
herein. The schematized representation shown in FIG. 57B may
represent either a duplexed device or a single array.
[0205] Enrichment may be enhanced in numerous ways. For example,
target analytes (e.g., cells) may be labeled with beads (e.g.,
immunoaffinity beads), thereby increasing their size (as depicted
in FIG. 59). In the case of epithelial cells, this may further
increase their size, resulting in an even more efficient
separation. Alternatively, the size of smaller analytes (e.g.,
cells) may be increased to the extent that they become the largest
objects in the sample or occupy a unique size range in comparison
to the other components of the sample, or so that they copurify
with other analytes. Beads may be made of polystyrene, magnetic
material, or any other material that can be adhered to an analyte
(e.g., cells). Desirably, such beads are neutrally buoyant so as
not to disrupt the flow of labeled cells through a deterministic
device.
[0206] Alteration
[0207] In other embodiments, in addition to enrichment, an analyte
of interest may be contacted with an altering reagent that may
chemically or physically alter the analyte or the fluid in the
sample. Such applications may include purification, buffer
exchange, labeling (e.g., immunohistochemical, magnetic, and
histochemical labeling, cell staining, and flow in-situ
fluorescence hybridization (FISH)), cell fixation, cell
stabilization, cell lysis, and cell activation.
[0208] Such methods may allow for the transfer of analytes from a
sample into a different liquid (e.g., buffer exchange). FIG. 34A
shows this effect schematically for a single stage deterministic
device, FIG. 34B shows this effect for a multistage deterministic
device, FIG. 34C shows this effect for a duplex array of
deterministic devices, and FIG. 34D shows this effect for a
multistage duplex array of deterministic devices. By using such
methods, analytes (e.g., blood cells) may be enriched in the
sample. Such transfers of an analyte from one liquid to another may
be also employed to effect a series of alterations, e.g., Wright
staining blood on-chip. Such a series may include reacting an
analyte with a first reagent and then transferring the particle to
a wash buffer, and then another reagent.
[0209] FIGS. 35A-35C illustrates a further example of alteration in
a two stage deterministic device having two bypass channels. In
this example, the larger analytes are moved from blood to buffer
and collected in stage 1, intermediate sized analytes are moved
from blood to buffer in stage 2, and smaller analytes that are not
moved from the blood in stage are collected also collected. FIG.
35B illustrates the size cut-off of the two stages, and FIG. 35C
illustrates the size distribution of the three fractions
collected.
[0210] FIG. 36 illustrates an example of alteration in a two stage
deterministic device having bypass channels that are disposed
between the lateral edge of the array and the channel wall. FIG. 37
illustrates a deterministic device similar to that in FIG. 36,
except that the two stages are connected by fluidic channels. FIG.
38 illustrates alteration in a deterministic device having two
stages with a small footprint. FIGS. 39A-39B illustrates alteration
in a device in which the output from the first and second stages is
captured in a single channel. FIG. 40 illustrates another device
for use in the methods of the invention.
[0211] FIG. 41 illustrates the use of a deterministic device to
perform multiple, sequential alterations on an analyte. In this
device an analyte is moved from the sample into a regent that
reacts with the analyte, and the altered analyte is then moved into
a buffer, thereby removing the unreacted reagent or reaction
byproducts. Additional steps may be added (e.g., steps described
herein).
[0212] Enrichment and alteration may also be combined. For example,
desired cells may be contacted with a lysing reagent and cellular
components, e.g., nuclei, are enriched based on size. In another
example, analytes may be contacted with particulate labels, e.g.,
magnetic beads, which bind to the analytes. Unbound particulate
labels may be removed based on size.
[0213] Buffer Exchange
[0214] Deterministic devices may also be employed for purposes of
buffer exchange. To achieve this result, a protocol similar to that
used for enrichment is followed: a cellular sample is added through
a sample inlet of a deterministic device, and the desired final
buffer medium is added through a fluid inlet. As described above,
cells above the critical size are deflected in the device and enter
the buffer.
[0215] Concentration
[0216] Devices of the invention may also be employed in order to
concentrate a cellular sample of interest. In one example shown in
FIG. 62, a cellular sample is introduced to the sample inlet of a
deterministic device. By reducing the volume of buffer introduced
into the fluid inlet so that this volume is significantly smaller
than the volume of the cellular sample, concentration of target
cells in a smaller volume results. This concentration step may
improve the results of any downstream analysis performed.
[0217] Cell Lysis
[0218] Devices of the invention may also be employed for purposes
of cell lysis. To achieve this in a deterministic device, a
protocol similar to that used for enrichment is followed: a
cellular sample is added through a sample inlet of the device (FIG.
63), and lysis buffer is added through the fluid inlet. As
described above, cells above the critical size are deflected and
enter the lysis buffer, leading to lysis of these cells. As a
result, the sample emerging from the center outlet includes lysed
cell components including organelles, while undeflected whole cells
emerge from the other outlet. Thus, the device provides a method
for selectively lysing target cells.
[0219] Downstream Analysis
[0220] A key prerequisite for many diagnostic assays is the removal
of a free or unreacted altering reagent from the sample to be
analyzed. In one embodiment, the reagent is a labeling reagent. As
described above, deterministic devices are able to separate free
labeling reagent from labeling reagent bound to an analyte (e.g., a
cell). It is then possible to perform a bulk measurement of the
reacted sample without significant levels of background
interference from free labeling reagent. In one example,
fluorescent antibodies selective for a particular epithelial cell
marker such as EpCAM are used. The fluorescent moiety may include
Cy dyes, Alexa dyes, or other fluorophore-containing molecules. The
resulting labeled sample is then analyzed by measuring the
fluorescence of the resulting sample of labeled enriched analytes
such as cells using a fluorimeter. Alternatively, a
chromophore-containing label may be used in conjunction with a
light spectrometer. The measurements obtained may be used to
quantify the number of target analytes such as cells in a
sample.
[0221] Many other methods of measurement and labeling reagents are
useful in the methods and devices of the invention. Labeling
antibodies may possess covalently bound enzymes that cleave a
substrate, altering its absorbance at a given wavelength; the
extent of cleavage is then quantified with a spectrometer.
Colorimetric or luminescent readouts are possible, depending on the
substrate used. Advantageously, the use of an enzyme label allows
for significant amplification of the measured signal, lowering the
threshold of detectability.
[0222] Quantum dots, e.g., Qdots.RTM. from QuantumDot Corp., may
also be utilized as a labeling reagent that is covalently bound to
a capture moiety such as an antibody. Qdots are resistant to
photobleaching and may be used in conjunction with two-photon
excitation measurements.
[0223] Another possible labeling reagent useful in the methods of
the invention is phage. Phage display is a technology in which
binding peptides are displayed by engineered phage strains having
strong binding affinities for a target, e.g., a protein found on
the surface of cells of interest. The peptide sequence
corresponding to a given phage is encoded in that phage's DNA.
Thus, phage are useful labeling reagents in that they are small
relative to an analyte such as a cell and thus may be easily
separated, and they additionally carry DNA that may be analyzed and
quantified using PCR or similar techniques, enabling a quantitative
determination of the number of cells present in an enriched bound
sample.
[0224] FIG. 65 depicts the use of phage as a labeling reagent in
which two deterministic device stages are arrayed in a cascade
configuration. The method depicted in FIG. 65 fits the general
description of FIG. 64, with the exception of the labeling reagent
employed.
[0225] Downstream analysis may include an accurate determination of
the number of desired analytes (e.g., cells) in the sample being
analyzed. In order to produce accurate quantitative results, the
amount of the target of a labeling reagent (e.g., a surface antigen
on a cell of interest) typically has to be known or predictable
(e.g., based on expression levels in a cell), and the binding of
the labeling reagent should also proceed in a predictable manner,
free from interfering substances. Thus, a device (e.g., a
deterministic devices) or method that produces a highly enriched
cellular samples prior to introduction of a labeling reagent are
particularly useful. In addition, labeling reagents that allow for
amplification of the signal produced are preferred in the case of a
rare desired analyte (e.g., epithelial cells in a blood sample).
Reagents that allow for signal amplification include enzymes and
phage. Other labeling reagents that do not allow for convenient
amplification but nevertheless produce a strong signal, such as
quantum dots, are also desirable.
[0226] When the devices and methods of the invention are used to
enrich cells contained in a sample, further quantification and
molecular biology analysis may be performed on the same set of
cells. The gentle treatment of the cells in the devices of the
invention, coupled with the described methods of bulk measurement,
maintain the integrity of the cells so that further analysis may be
performed if desired. For example, techniques that destroy the
integrity of the cells may be performed subsequent to bulk
measurement; such techniques include DNA or RNA analysis, proteome
analysis, or metabolome analysis. An example of such analysis is
PCR, in which the cells are lysed and levels of particular DNA
sequences are amplified. Such techniques are particularly useful
when the number of target cells isolated is very low.
[0227] Cancer Diagnosis
[0228] Epithelial cells exfoliated from solid tumors have been
found in the circulation of patients with cancers of the breast,
colon, liver, ovary, prostate, and lung. In general, the presence
of circulating tumor cells (CTCs) after therapy has been associated
with tumor progression and spread, poor response to therapy,
relapse of disease, and/or decreased survival. Therefore,
enumeration of CTCs offers a means to stratify patients for
baseline characteristics that predict initial risk and subsequent
risk based upon response to therapy.
[0229] Unlike tumor-derived cells in bone marrow, which can be
dormant and long-lived, CTCs, which are of epithelial cell type and
origin, have a short half-life of approximately one day, and their
presence indicates a recent influx from a proliferating tumor
(Patel et al., Ann Surg, 235:226-231, 2002). Therefore, CTCs can
reflect the current clinical status of patient disease and
therapeutic response. The enumeration and characterization of CTCs
has potential value in assessing cancer prognosis and in monitoring
therapeutic efficacy for early detection of treatment failure that
can lead to disease relapse. In addition, CTC analysis may detect
early relapse in presymptomatic patients who have completed a
course of therapy; at present, individuals without measurable
disease are not eligible to participate in clinical trials of
promising new treatments (Braun et al., N Engl J Med, 351:824-826,
2004).
[0230] The devices and methods of the invention may be used to
evaluate cancer patients and those at risk for cancer. For example,
a blood sample is drawn from the patient and introduced to a
deterministic device of the invention with a critical size chosen
appropriately to separate epithelial cells from other blood cells.
The number of epithelial cells in the blood sample is determined
using a method described herein. For example, the cells may be
labeled with an antibody that binds to EpCAM, and the antibody may
have a covalently bound fluorescent label, or be bound to a
magnetic particle. A bulk measurement may then be made of the
enriched sample produced by the device, and from this measurement,
the number of epithelial cells present in the initial blood sample
may be determined. Microscopic techniques may be used to visually
quantify the cells in order to correlate the bulk measurement with
the corresponding number of labeled cells in the blood sample.
[0231] By making a series of measurements over days, weeks, months,
or years, one may track the level of epithelial cells present in a
patient's bloodstream as a function of time. In the case of
existing cancer patients, this provides a useful indication of the
progression of the disease and assists medical practitioners in
making appropriate therapeutic choices based on the increase,
decrease, or lack of change in circulating epithelial cells in the
patient's bloodstream. For those at risk of cancer, a sudden
increase in the number of cells detected may provide an early
warning that the patient has developed a tumor. This early
diagnosis, coupled with subsequent therapeutic intervention, is
likely to result in an improved patient outcome in comparison to an
absence of diagnostic information.
[0232] Diagnostic methods include making bulk measurements of
labeled epithelial cells isolated from blood, as well as techniques
that destroy the integrity of the cells. For example, PCR may be
performed on a sample in which the number of target cells isolated
is very low; by using primers specific for particular cancer
markers, information may be gained about the type of tumor from
which the analyzed cells originated. Additionally, RNA analysis,
proteome analysis, or metabolome analysis may be performed as a
means of diagnosing the type or types of cancer present in the
patient.
[0233] One important diagnostic indicator for lung cancer and other
cancers is the presence or absence of certain mutations in
epidermal growth factor receptor (EGFR). EGFR consists of an
extracellular ligand-binding domain, a transmembrane portion, and
an intracellular tyrosine kinase (TK) domain. The normal
physiologic role of EGFR is to bind ErbB ligands, including
epidermal growth factor (EGF), at the extracellular binding site to
trigger a cascade of downstream intracellular signals leading to
cell proliferation, survival, motility and other related
activities. Many non-small cell lung tumors with EGFR mutations
respond to small molecule EGFR inhibitors, such as gefitinib
(Iressa; AstraZeneca), but often eventually acquire secondary
mutations that make them drug resistant. Using the devices and
methods of the invention, one may monitor patients taking such
drugs by taking frequent samples of blood and determining the
number of epithelial cells in each sample as a function of time.
This provides information as to the course of the disease. For
example, a decreasing number of circulating epithelial cells over
time suggests a decrease in the severity of the disease and the
size of the tumor or tumors. Immediately following quantification
of epithelial cells, these cells may be analyzed by PCR to
determine what mutations may be present in the EFGR gene expressed
in the epithelial cells. Certain mutations, such as those clustered
around the ATP-binding pocket of the EGFR TK domain, are known to
make the cancer cells susceptible to gefitinib inhibition. Thus,
the presence of these mutations supports a diagnosis of cancer that
is likely to respond to treatment using gefitinib. However, many
patients who respond to gefitinib eventually develop a second
mutation, often a methionine-to-threonine substitution at position
790 in exon 20 of the TK domain, which renders them resistant to
gefitinib. By using the devices and method of the invention, one
may test for this mutation as well, providing further diagnostic
information about the course of the disease and the likelihood that
it will respond to gefitinib or similar compounds.
[0234] Sample Preparation
[0235] Samples may be employed in the methods described herein with
or without manipulation, e.g., stabilization and removal of certain
components. In one embodiment, the sample is enriched in the cells
of interest prior to introduction to a device of the invention.
Methods for enriching cell populations are described herein and
known in the art, e.g., affinity mechanisms, agglutination, and
size, shape, and deformability based enrichments. Some samples may
be diluted or concentrated prior to introduction into the
device.
[0236] In one embodiment, reagents are added to the sample, to
selectively or nonselectively increase the hydrodynamic size of the
particles within the sample. This modified sample is, for example,
then pumped through a deterministic device. Because the particles
are swollen and have an increased hydrodynamic diameter, it will be
possible to use deterministic devices with larger and more easily
manufactured gap sizes. In a preferred embodiment, the steps of
swelling and size-based enrichment are performed in an integrated
fashion on a deterministic device. Suitable reagents include any
hypotonic solution, e.g., deionized water, 2% sugar solution, or
neat non-aqueous solvents. Other reagents include beads, e.g.,
magnetic or polymer, that bind selectively (e.g., through
antibodies or avidin-biotin) or non-selectively.
[0237] In another embodiment, reagents are added to the sample to
selectively or nonselectively decrease the hydrodynamic size of the
particles within the sample. Nonuniform decrease in particles in a
sample will increase the difference in hydrodynamic size between
particles. For example, nucleated cells are separated from
enucleated cells by hypertonically shrinking the cells. The
enucleated cells can shrink to a very small particle, while the
nucleated cells cannot shrink below the size of the nucleus.
Exemplary shrinking reagents include hypertonic solutions.
[0238] In an alternative embodiment, affinity functionalized beads
are used to increase the hydrodynamic size of an analyte of
interest relative to other analytes present in a sample, thereby
allowing for the operation of a deterministic device with a larger
and more easily manufactured gap size.
[0239] Fluids may be driven through a device either actively or
passively. Fluids may be pumped using electric field, a centrifugal
field, pressure-driven fluid flow, an electro-osmotic flow, or
capillary action. In preferred embodiments, the average direction
of the field will be parallel to the walls of the channel that
includes the deterministic device.
[0240] Any of the following exemplary deterministic devices and
methods may be incorporated into devices of the invention.
EXAMPLES
Example 1
A Silicon Device Multiplexing 14 3-stage Array Duplexes
[0241] FIGS. 42A-42E show an exemplary device, characterized as
follows.
[0242] Dimension: 90 mm.times.34 mm.times.1 mm
[0243] Array design: 3 stages, gap size=18, 12 and 8 .mu.m for the
first, second and third stage, respectively. Bifurcation
ratio=1/10. Duplex; single bypass channel
[0244] Device design: multiplexing 14 array duplexes; flow
resistors for flow stability
[0245] Device fabrication: The arrays and channels were fabricated
in silicon using standard photolithography and deep silicon
reactive etching techniques. The etch depth is 150 .mu.m. Through
holes for fluid access are made using KOH wet etching. The silicon
substrate was sealed on the etched face to form enclosed fluidic
channels using a blood compatible pressure sensitive adhesive
(9795, 3M, St Paul, Minn.).
[0246] Device Packaging: The device was mechanically mated to a
plastic manifold with external fluidic reservoirs to deliver blood
and buffer to the device and extract the generated fractions.
[0247] Device Operation: An external pressure source was used to
apply a pressure of 2.4 PSI to the buffer and blood reservoirs to
modulate fluidic delivery and extraction from the packaged
device.
[0248] Experimental conditions: human blood from consenting adult
donors was collected into K.sub.2EDTA vacutainers (366643, Becton
Dickinson, Franklin Lakes, N.J.). The undiluted blood was processed
using the exemplary device described above (FIG. 42F) at room
temperature and within 9 hrs of draw. Nucleated cells from the
blood were separated from enucleated cells (red blood cells and
platelets), and plasma delivered into a buffer stream of calcium
and magnesium-free Dulbecco's Phosphate Buffered Saline (14190-144,
Invitrogen, Carlsbad, Calif.) containing 1% Bovine Serum Albumin
(BSA) (A8412-100ML, Sigma-Aldrich, St Louis, Mo.).
[0249] Measurement techniques: Complete blood counts were
determined using a Coulter impedance hematology analyzer
(COULTER.RTM. Ac.cndot.T diff.TM., Beckman Coulter, Fullerton,
Calif.).
[0250] Performance: FIGS. 43A-43F shows typical histograms
generated by the hematology analyzer from a blood sample and the
waste (buffer, plasma, red blood cells, and platelets) and product
(buffer and nucleated cells) fractions generated by the device.
Table 1 shows the performance over 5 different blood samples:
TABLE-US-00001 TABLE 1 Performance Metrics Sample RBC Platelet WBC
number Throughput removal removal loss 1 4 mL/hr 100% 99% <1% 2
6 mL/hr 100% 99% <1% 3 6 mL/hr 100% 99% <1% 4 6 mL/hr 100%
97% <1% 5 6 mL/hr 100% 98% <1%
Example 2
A Silicon Device Multiplexing 14 Single-Stage Array Duplexes
[0251] FIGS. 44A-44D show an exemplary device, characterized as
follows.
[0252] Dimension: 90 mm.times.34 mm.times.1 mm
[0253] Array design: 1 stage, gap size=24 .mu.m. Bifurcation
ratio=1/60. Duplex; double bypass channel
[0254] Device design: multiplexing 14 array duplexes; flow
resistors for flow stability
[0255] Device fabrication: The arrays and channels were fabricated
in silicon using standard photolithography and deep silicon
reactive etching techniques. The etch depth is 150 .mu.m. Through
holes for fluid access are made using KOH wet etching. The silicon
substrate was sealed on the etched face to form enclosed fluidic
channels using a blood compatible pressure sensitive adhesive
(9795, 3M, St Paul, Minn.).
[0256] Device Packaging: The device was mechanically mated to a
plastic manifold with external fluidic reservoirs to deliver blood
and buffer to the device and extract the generated fractions.
[0257] Device Operation: An external pressure source was used to
apply a pressure of 2.4 PSI to the buffer and blood reservoirs to
modulate fluidic delivery and extraction from the packaged
device.
[0258] Experimental conditions: human blood from consenting adult
donors was collected into K.sub.2EDTA vacutainers (366643, Becton
Dickinson, Franklin Lakes, N.J.). The undiluted blood was processed
using the exemplary device described above at room temperature and
within 9 hrs of draw. Nucleated cells from the blood were separated
from enucleated cells (red blood cells and platelets), and plasma
delivered into a buffer stream of calcium and magnesium-free
Dulbecco's Phosphate Buffered Saline (14190-144, Invitrogen,
Carlsbad, Calif.) containing 1% Bovine Serum Albumin (BSA)
(A8412-100ML, Sigma-Aldrich, St Louis, Mo.).
[0259] Measurement techniques: Complete blood counts were
determined using a Coulter impedance hematology analyzer
(COULTER.RTM. Ac.cndot.T diff.TM., Beckman Coulter, Fullerton,
Calif.).
[0260] Performance: The device operated at 17 mL/hr and achieved
>99% red blood cell removal, >95% nucleated cell retention,
and >98% platelet removal.
Example 3
Separation of Fetal Cord Blood
[0261] FIG. 45 shows a schematic of the device used to separate
nucleated cells from fetal cord blood.
[0262] Dimension: 100 mm.times.28 mm.times.1 mm
[0263] Array design: 3 stages, gap size=18, 12 and 8 .mu.m for the
first, second and third stage, respectively. Bifurcation ratio
1/10. Duplex; single bypass channel.
[0264] Device design: multiplexing 10 array duplexes; flow
resistors for flow stability.
[0265] Device fabrication: The arrays and channels were fabricated
in silicon using standard photolithography and deep silicon
reactive etching techniques. The etch depth is 140 .mu.m. Through
holes for fluid access are made using KOH wet etching. The silicon
substrate was sealed on the etched face to form enclosed fluidic
channels using a blood compatible pressure sensitive adhesive
(9795, 3M, St Paul, Minn.).
[0266] Device Packaging: The device was mechanically mated to a
plastic manifold with external fluidic reservoirs to deliver blood
and buffer to the device and extract the generated fractions.
[0267] Device Operation: An external pressure source was used to
apply a pressure of 2.0 PSI to the buffer and blood reservoirs to
modulate fluidic delivery and extraction from the packaged
device.
[0268] Experimental conditions: Human fetal cord blood was drawn
into phosphate buffered saline containing Acid Citrate Dextrose
anticoagulants. 1 mL of blood was processed at 3 mL/hr using the
device described above at room temperature and within 48 hrs of
draw. Nucleated cells from the blood were separated from enucleated
cells (red blood cells and platelets), and plasma delivered into a
buffer stream of calcium and magnesium-free Dulbecco's Phosphate
Buffered Saline (14190-144, Invitrogen, Carlsbad, Calif.)
containing 1% Bovine Serum Albumin (BSA) (A8412-100ML,
Sigma-Aldrich, St Louis, Mo.) and 2 mM EDTA (15575-020, Invitrogen,
Carlsbad, Calif.).
[0269] Measurement techniques: Cell smears of the product and waste
fractions (FIG. 46A-46B) were prepared and stained with modified
Wright-Giemsa (WG16, Sigma Aldrich, St. Louis, Mo.).
[0270] Performance: Fetal nucleated red blood cells were observed
in the product fraction (FIG. 46A) and absent from the waste
fraction (FIG. 46B).
Example 4
Isolation of Fetal Cells from Maternal Blood
[0271] The device and process described in detail in Example 1 were
used in combination with immunomagnetic affinity enrichment
techniques to demonstrate the feasibility of isolating fetal cells
from maternal blood.
[0272] Experimental conditions: blood from consenting maternal
donors carrying male fetuses was collected into K.sub.2EDTA
vacutainers (366643, Becton Dickinson, Franklin Lakes, N.J.)
immediately following elective termination of pregnancy. The
undiluted blood was processed using the device described in Example
1 at room temperature and within 9 hrs of draw. Nucleated cells
from the blood were separated from enucleated cells (red blood
cells and platelets), and plasma delivered into a buffer stream of
calcium and magnesium-free Dulbecco's Phosphate Buffered Saline
(14190-144, Invitrogen, Carlsbad, Calif.) containing 1% Bovine
Serum Albumin (BSA) (A8412-100ML, Sigma-Aldrich, St Louis, Mo.).
Subsequently, the nucleated cell fraction was labeled with
anti-CD71 microbeads (130-046-201, Miltenyi Biotech Inc., Auburn,
Calif.) and enriched using the MiniMACS.TM. MS column (130-042-201,
Miltenyi Biotech Inc., Auburn, Calif.) according to the
manufacturer's specifications. Finally, the CD71-positive fraction
was spotted onto glass slides.
[0273] Measurement techniques: Spotted slides were stained using
fluorescence in situ hybridization (FISH) techniques according to
the manufacturer's specifications using Vysis probes (Abbott
Laboratories, Downer's Grove, Ill.). Samples were stained from the
presence of X and Y chromosomes. In one case, a sample prepared
from a known trisomy 21 pregnancy was also stained for chromosome
21.
[0274] Performance: Isolation of fetal cells was confirmed by the
reliable presence of male cells in the CD71-positive population
prepared from the nucleated cell fractions (FIG. 47). In the single
abnormal case tested, the trisomy 21 pathology was also identified
(FIG. 48).
[0275] The following examples show specific embodiments of devices.
The description for each device provides the number of stages in
series, the gap size for each stage, .epsilon. (Flow Angle), and
the number of channels per device (Arrays/Chip). Each device was
fabricated out of silicon using DRIE, and each device had a thermal
oxide layer.
Example 5
[0276] This device includes five stages in a single array. [0277]
Array Design: 5 stage, asymmetric array [0278] Gap Sizes: Stage 1:
8 .mu.m [0279] Stage 2: 10 .mu.m [0280] Stage 3: 12 .mu.m [0281]
Stage 4: 14 .mu.m [0282] Stage 5: 16 .mu.m [0283] FlowAngle: 1/10
[0284] Arrays/Chip: 1
Example 6
[0285] This device includes the stages, where each stage is a
duplex having a bypass channel. The height of the device was 125
.mu.m. [0286] Array Design: symmetric 3 stage array with central
collection channel [0287] Gap Sizes: Stage 1: 8 .mu.m [0288] Stage
2: 12 .mu.m [0289] Stage 3: 18 .mu.m [0290] Stage 4: [0291] Stage
5: [0292] Flow Angle: 1/10 [0293] Arrays/Chip: 1 [0294] Other:
central collection channel
[0295] FIG. 49A shows the mask employed to fabricate the device.
FIGS. B1B-B1D are enlargements of the portions of the mask that
define the inlet, array, and outlet. FIGS. 50A-50G show SEMs of the
actual device.
Example 7
[0296] This device includes the stages, where each stage is a
duplex having a bypass channel. "Fins" were designed to flank the
bypass channel to keep fluid from the bypass channel from
re-entering the array. The chip also included on-chip flow
resistors, i.e., the inlets and outlets possessed greater fluidic
resistance than the array. The height of the device was 117 .mu.m.
[0297] Array Design: 3 stage symmetric array [0298] Gap Sizes:
Stage 1: 8 .mu.m [0299] Stage 2: 12 .mu.m [0300] Stage 3: 18 .mu.m
[0301] Stage 4: [0302] Stage 5: [0303] Flow Angle: 1/10 [0304]
Arrays/Chip: 10 Other: large fin central collection channel on-chip
flow resistors
[0305] FIG. 51 A shows the mask employed to fabricate the device.
FIGS. 51B-51D are enlargements of the portions of the mask that
define the inlet, array, and outlet. FIGS. 52A-52F show SEMs of the
actual device.
Example 8
[0306] This device includes the stages, where each stage is a
duplex having a bypass channel. "Fins" were designed to flank the
bypass channel to keep fluid from the bypass channel from
re-entering the array. The edge of the fin closest to the array was
designed to mimic the shape of the array. The chip also included
on-chip flow resistors, i.e., the inlets and outlets possessed
greater fluidic resistance than the array. The height of the device
was 138 .mu.m. TABLE-US-00002 Array Design: 3 stage symmetric array
Gap Sizes: Stage 1: 8 .mu.m Stage 2: 12 .mu.m Stage 3: 18 .mu.m
Stage 4: Stage 5: Flow Angle: 1/10 Arrays/Chip: 10 Other: alternate
large fin central collection channel on-chip flow resistors
[0307] FIG. 45A shows the mask employed to fabricate the device.
FIGS. 45B-45D are enlargements of the portions of the mask that
define the inlet, array, and outlet. FIGS. 532A-532F show SEMs of
the actual device.
Example 9
[0308] This device includes the stages, where each stage is a
duplex having a bypass channel. "Fins" were optimized using Femlab
to flank the bypass channel to keep fluid from the bypass channel
from re-entering the array. The edge of the fin closest to the
array was designed to mimic the shape of the array. The chip also
included on-chip flow resistors, i.e., the inlets and outlets
possessed greater fluidic resistance than the array. The height of
the device was 139 or 142 .mu.m. [0309] Array Design: 3 stage
symmetric array [0310] Gap Sizes: Stage 1: 8 .mu.m [0311] Stage 2:
12 .mu.m [0312] Stage 3: 18 .mu.m [0313] Stage 4: [0314] Stage 5:
[0315] Flow Angle: 1/10 [0316] Arrays/Chip: 10 [0317] Other: Femlab
optimized central collection channel (Femiab I) on-chip flow
resistors
[0318] FIG. 54A shows the mask employed to fabricate the device.
FIGS. 54B-E1D are enlargements of the portions of the mask that
define the inlet, array, and outlet. FIGS. 55A-55S show SEMs of the
actual device.
Example 10
[0319] This device includes a single stage, duplex device having a
bypass channel disposed to receive output from the ends of both
arrays. The obstacles in this device are elliptical. The array
boundary was modeled in Femlab to. The chip also included on-chip
flow resistors, i.e., the inlets and outlets possessed greater
fluidic resistance than the array. The height of the device was 152
.mu.m. [0320] Array Design: single stage symmetric array [0321] Gap
Sizes: Stage 1: 24 .mu.m [0322] Stage 2: [0323] Stage 3: [0324]
Stage 4: [0325] Stage 5: [0326] Flow Angle: 1/60 [0327]
Arrays/Chip: 14 [0328] Other: central barrier [0329] ellipsoid
posts [0330] on-chip resistors [0331] Femlab modeled array
boundary
[0332] FIG. 44A shows the mask employed to fabricate the device.
FIGS. 44B-44D are enlargements of the portions of the mask that
define the inlet, array, and outlet. FIGS. 56A-56C show SEMs of the
actual device.
Example 11
[0333] Deterministic devices incorporated into devices of the
invention were designed by computer-aided design (CAD) and
microfabricated by photolithography. A two-step process was
developed in which a blood sample is first debulked to remove the
large population of small cells and then the rare target epithelial
cells target cells are recovered by immunoaffinity capture. The
devices were defined by photolithography and etched into a silicon
substrate based on a CAD-generated design. The cell enrichment
module, which is approximately the size of a standard microscope
slide, contains 14 parallel sample processing sections and
associated sample handling channels that connect to common sample
and buffer inlets and product and waste outlets. Each section
contains an array of microfabricated obstacles that is optimized to
separate the target cell type by size via displacement of the
larger cells into the product stream. In this example, the
microchip was designed to separate red blood cells (RBCs) and
platelets from the larger leukocytes and circulating tumor cells.
Enriched populations of target cells were recovered from whole
blood passed through the device. Performance of the cell enrichment
microchip was evaluated by separating RBCs and platelets from white
blood cells (WBCs) in normal whole blood (FIG. 67). In cancer
patients, circulating tumor cells are found in the larger WBC
fraction. Blood was minimally diluted (30%), and a 6 ml sample was
processed at a flow rate of up to 6 ml/hr. The product and waste
stream were evaluated in a Coulter Model "A.sup.C-T diff" clinical
blood analyzer, which automatically distinguishes, sizes and counts
different blood cell populations. The enrichment chip achieved
separation of RBCs from WBCs, in which the WBC fraction had >99%
retention of nucleated cells, >99% depletion of RBCs and >97%
depletion of platelets. Representative histograms of these cell
fractions are shown in FIG. 68. Routine cytology confirmed the high
degree of enrichment of the WBC RBC fractions (FIG. 69).
[0334] Next, epithelial cells were recovered by affinity capture in
a microfluidic module that is functionalized with immobilized
antibody. A capture module with a single chamber containing a
regular array of antibody-coated microfabricated obstacles was
designed. These obstacles are disposed to maximize cell capture by
increasing the capture area approximately four-fold, and by slowing
the flow of cells under laminar flow adjacent to the obstacles to
increase the contact time between the cells and the immobilized
antibody. The capture modules can be operated under conditions of
relatively high flow rate but low shear to protect cells against
damage. The surface of the capture module was functionalized by
sequential treatment with 10% silane, 0.5% gluteraldehyde and
avidin, followed by biotinylated anti-EpCAM. Active sites were
blocked with 3% bovine serum albumin in PBS, quenched with dilute
Tris HCl and stabilized with dilute L-histidine. Modules were
washed in PBS after each stage and finally dried and stored at room
temperature. Capture performance was measured with the human
advanced lung cancer cell line NCI-H1650 (ATCC Number CRL-5883).
This cell line has a heterozygous 15 bp in-frame deletion in exon
19 of EGFR that renders it susceptible to gefitinib. Cells from
confluent cultures were harvested with trypsin, stained with the
vital dye Cell Tracker Orange (CMRA reagent, Molecular Probes,
Eugene, Oreg.), resuspended in fresh whole blood and fractionated
in the microfluidic chip at various flow rates. In these initial
feasibility experiments, cell suspensions were processed directly
in the capture modules without prior fractionation in the cell
enrichment module to debulk the red blood cells; hence, the sample
stream contained normal blood red cells and leukocytes as well as
tumor cells. After the cells were processed in the capture module,
the device was washed with buffer at a higher flow rate (3 ml/hr)
to remove the nonspecifically bound cells. The adhesive top was
removed and the adherent cells were fixed on the chip with
paraformaldehyde and observed by fluorescence microscopy. Cell
recovery was calculated from hemacytometer counts; representative
capture results are shown in Table 2. Initial yields in
reconstitution studies with unfractionated blood were greater than
60% with less than 5% of non-specific binding. TABLE-US-00003 TABLE
2 Run Avg. flow Length of No. cells No. cells number rate run
processed captured Yield 1 3.0 1 hr 150,000 38,012 25% 2 1.5 2 hr
150,000 30,000/ml 60% 3 1.08 2 hr 108,000 68,661 64% 4 1.21 2 hr
121,000 75,491 62%
[0335] Next, NCI-H1650 cells that were spiked into whole blood and
recovered by size fractionation and affinity capture as described
above were successfully analyzed in situ. In a trial run to
distinguish epithelial cells from leukocytes, 0.5 ml of a stock
solution of fluorescein-labeled CD45 pan-leukocyte monoclonal
antibody was passed into the capture module and incubated at room
temperature for 30 minutes. The module was washed with buffer to
remove unbound antibody and the cells were fixed on the chip with
1% paraformaldehyde and observed by fluorescence microscopy. As
shown in FIG. 70, the epithelial cells were bound to the obstacles
and floor of the capture module. Background staining of the flow
passages with CD45 pan-leukocyte antibody is visible, as are
several stained leukocytes, apparently due to a low level of
non-specific capture.
Example 12
Device Embodiments
[0336] A design for preferred deterministic device is shown in FIG.
73A, and parameters corresponding to three preferred device
embodiments associated with this design are shown in FIG. 73B.
These embodiments are particularly useful for separating epithelial
cells from blood.
Example 13
PCR Assay for EGFR Mutations
[0337] A blood sample from a cancer patient is processed and
analyzed using the devices and methods of Example 11, resulting in
an enriched sample of epithelial cells containing CTCs. This sample
is then analyzed to identify potential EGFR mutations.
[0338] To perform this analysis, genomic DNA is isolated from the
target cells present in the enriched sample and amplified for use
in allele-specific Real Time PCR assays. Since all EGFR mutations
in NSC lung cancer reported to date that are known to confer
sensitivity or resistance to gefitinib lie within the coding
regions of exons 18 to 21, each of these four exons is
PCR-amplified with a unique set of exon-specific primers. Next,
multiplexed allele-specific quantitative PCR reactions are
performed using the TaqMan 5' nuclease assay PCR system (Applied
Biosystems) and a model 7300 Applied Biosystems Real Time PCR
machine. This allows the rapid identification of any of the known
clinically relevant mutations.
[0339] A two-step PCR protocol is required for this method. First,
exons 18 through 21 are amplified in standard PCR reactions. The
resultant PCR products are split into separate aliquots for use in
allele-specific multiplexed Real Time PCR assays. The initial PCR
reactions are stopped during the log phase in order to minimize
possible loss of allele-specific information during amplification.
Next, a second round of PCR amplifies subregions of the initial PCR
product specific to each mutation of interest. Given the very high
sensitivity of Real Time PCR, it is possible to obtain complete
information on the mutation status of the EGFR gene even if as few
as 10 CTCs are isolated. Real Time PCR provides quantification of
allelic sequences over 8 logs of input DNA concentrations; thus,
even heterozygous mutations in impure populations are easily
detected using this method.
[0340] Oligonucleotides are designed using the primer optimization
software program Primer Express (Applied Biosystems), and
hybridization conditions are optimized to distinguish the wild type
EGFR DNA sequence from mutant alleles. EGFR genomic DNA amplified
from lung cancer cell lines that are known to carry EGFR mutations,
such as H358 (wild type), H1650 (15-bp deletion, .DELTA.2235-2249),
and H1975 (two point mutations, 2369 C.fwdarw.T, 2573 T.fwdarw.G),
is used to optimize the allele-specific Real Time PCR reactions.
Using the TaqMan 5' nuclease assay, allele-specific labeled probes
specific for wild type sequence or for known EGFR mutations are
developed. The oligonucleotides are designed to have melting
temperatures that easily distinguish a match from a mismatch, and
the Real Time PCR conditions are optimized to distinguish wild type
and mutant alleles. All Real Time PCR reactions are carried out in
triplicate.
[0341] Initially, labeled probes containing wild type sequence are
multiplexed in the same reaction with a single mutant probe.
Expressing the results as a ratio of one mutant allele sequence
versus wild type sequence can identify samples containing or
lacking a given mutation. After conditions are optimized for a
given probe set, it is then possible to multiplex probes for all of
the mutant alleles within a given exon within the same Real Time
PCR assay, increasing the ease of use of this analytical tool in
clinical settings.
[0342] The purity of the input sample of CTCs may vary, and the
mutation status of the isolated CTCs may be heterogeneous.
Nevertheless, the extremely high sensitivity of Real Time PCR
enables the identification any and all mutant sequences
present.
Example 14
Determining Counts for Non-Epithelial Cell Types
[0343] Using the methods of the invention, one may make a diagnosis
based on counting cell types other than epithelial cells. A
diagnosis of the absence, presence, or progression of cancer may be
based on the number of cells in a cellular sample that are larger
than a particular cutoff size. For example, cells with a
hydrodynamic cell diameter of 14 microns or larger may be selected.
This cutoff size would eliminate most leukocytes. The nature of
these cells may then be determined by downstream molecular or
cytological analysis.
[0344] Cell types other than epithelial cells that would be useful
to analyze include endothelial cells, endothelial progenitor cells,
endometrial cells, or trophoblasts indicative of a disease state.
Furthermore, determining separate counts for epithelial cells and
other cell types, followed by a determination of the ratios between
the number of epithelial cells and the number of other cell types,
may provide useful diagnostic information.
[0345] A deterministic device may be configured to isolate targeted
subpopulations of cells such as those described above, as shown in
FIG. 71A-D. A size cutoff may be selected such that most native
blood cells, including red blood cells, white blood cells, and
platelets, flow to waste, while non-native cells, which could
include endothelial cells, endothelial progenitor cells,
endometrial cells, or trophoblasts, are collected in an enriched
sample. This enriched sample may be further analyzed.
[0346] Using a deterministic device, therefore, it is possible to
isolate a subpopulation of cells from blood or other bodily fluids
based on size, which conveniently allows for the elimination of a
large proportion of native blood cells when large cell types are
targeted. As shown schematically in FIG. 72, a deterministic device
may include counting means to determine the number of cells in the
enriched sample, and further analysis of the cells in the enriched
sample may provide additional information that is useful for
diagnostic or other purposes.
Example 15
Enrichment of Fetal Nucleated Red Blood Cells from Maternal
Blood
[0347] For this example, the device includes a deterministic
separation component, as described herein, capable of separated
fetal nucleated red blood cells and maternal white blood cells from
maternal enucleated red blood cells. The deterministic component is
connected to a reservoir containing sodium nitrite. A maternal
blood sample, e.g., that has been diluted, is introduced into the
device to produce a fraction enriched in fetal red blood cells and
depleted of maternal red blood cells. This sample is directed into
the reservoir where the sodium nitrite oxidizes the fetal heme
iron, thereby increasing the magnetic responsiveness of the fetal
red blood cells. A magnetic field is then applied, e.g., via a MACS
column, and the altered fetal red blood cells bind to the magnet,
while maternal white blood cells are not bound by the magnet.
Removing the white blood cells, e.g., by a rinse, and then
eliminating the magnetic field allows recovery of the fetal red
blood cells, e.g., for analysis, storage, or further
manipulation.
[0348] Other Embodiments
[0349] All publications, patents, and patent applications mentioned
in the above specification are hereby incorporated by reference.
Various modifications and variations of the described method and
system of the invention will be apparent to those skilled in the
art without departing from the scope and spirit of the invention.
Although the invention has been described in connection with
specific embodiments, it should be understood that the invention as
claimed should not be unduly limited to such specific embodiments.
Indeed, various modifications of the described modes for carrying
out the invention that are obvious to those skilled in the art are
intended to be within the scope of the invention.
[0350] Other embodiments are in the claims.
* * * * *