U.S. patent application number 15/720628 was filed with the patent office on 2018-04-12 for chip-based flow cytometer type systems for analyzing fluorescently tagged particles.
This patent application is currently assigned to LUMINEX CORPORATION. The applicant listed for this patent is LUMINEX CORPORATION. Invention is credited to John C. CARRANO, William R. DEICHER, Jesse C. PHILLIPS, Adam Richard SCHILFFARTH.
Application Number | 20180100872 15/720628 |
Document ID | / |
Family ID | 38663109 |
Filed Date | 2018-04-12 |
United States Patent
Application |
20180100872 |
Kind Code |
A1 |
SCHILFFARTH; Adam Richard ;
et al. |
April 12, 2018 |
CHIP-BASED FLOW CYTOMETER TYPE SYSTEMS FOR ANALYZING FLUORESCENTLY
TAGGED PARTICLES
Abstract
Portable systems for processing and analyzing biological or
environmental samples as well as different configurations of
chip-based flow cytometers are provided. The portable systems
include an automated assay preparation module configured to process
a sample into a fluid assay with fluorescently tagged particles and
a microfluidic analysis module coupled to the fluid assay module,
wherein the microfluidic analysis module includes a chip-based flow
cytometer.
Inventors: |
SCHILFFARTH; Adam Richard;
(Cedar Park, TX) ; DEICHER; William R.; (Austin,
TX) ; CARRANO; John C.; (Austin, TX) ;
PHILLIPS; Jesse C.; (Elgin, TX) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
LUMINEX CORPORATION |
Austin |
TX |
US |
|
|
Assignee: |
LUMINEX CORPORATION
Austin
TX
|
Family ID: |
38663109 |
Appl. No.: |
15/720628 |
Filed: |
September 29, 2017 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
11750000 |
May 17, 2007 |
9810707 |
|
|
15720628 |
|
|
|
|
60747483 |
May 17, 2006 |
|
|
|
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
G01N 35/0098 20130101;
G01N 15/1459 20130101; G01N 2021/6439 20130101; G01N 15/1484
20130101; G01N 35/1095 20130101 |
International
Class: |
G01N 35/10 20060101
G01N035/10; G01N 15/14 20060101 G01N015/14; G01N 35/00 20060101
G01N035/00 |
Claims
1-28. (canceled)
29. A chip-based flow cytometer comprising: (a) a substrate having
fixedly arranged therein: (i) a first input conduit for receiving a
sample fluid containing fluorescent particles; (ii) a second input
conduit for receiving a sheath fluid; (iii) a fluid flow chamber
coupled to the first and second input conduits, wherein the fluid
flow chamber is configured to generate a fluid stream with the
sample fluid confined within the sheath fluid; (iv) a channel
coupled to the fluid flow chamber for routing the fluid stream
through an optical interrogation region; and (v) an outlet coupled
to the channel configured for the sample fluid and the sheath fluid
to exit the substrate after passing through the optical
interrogation region; (b) an illumination system configured to
direct light at a plurality of different spots within the optical
interrogation region of the channel; and (c) a collection system
comprising a plurality of detectors configured to gather
fluorescent light emitted from the fluorescent particles in the
optical interrogation region, wherein the fluorescent light emitted
from the fluorescent particles at each of the different spots is
collected by a different detector of the collection system.
30. The chip-based flow cytometer of claim 29, wherein the
illumination system comprises a light source and a beam
splitter.
31. The chip-based flow cytometer of claim 29, wherein the light
source is a light emitting diode.
32. The chip-based flow cytometer of claim 29, wherein the
illumination system comprises a different light source for each of
the different spots within the optical interrogation region.
33. The chip-based flow cytometer of claim 31, wherein at least one
of the light sources emits light within a different wavelength
range than another of the light sources.
34. The chip-based flow cytometer of claim 29, wherein the
plurality of detectors comprises a silicon avalanche
photodiode.
35. The chip-based flow cytometer of claim 29, wherein the
fluorescent particles are beads.
36. The chip-based flow cytometer of claim 29, wherein the
fluorescent particles are cells.
Description
[0001] This application is a continuation of U.S. patent
application Ser. No. 11/750,000, filed May 17, 2007, which is now
U.S. Pat. No. 9,810,707, which claims priority to U.S. Provisional
Patent Application, Ser. No. 60/747,483, filed May 17, 2006, the
entire contents of which are incorporated herein by reference.
BACKGROUND OF THE INVENTION
1. Field of the Invention
[0002] The present invention generally relates to systems for
processing and analyzing fluid samples. Certain embodiments relate
to chip based flow cytometer type systems configured to perform
measurements of samples including fluorescently tagged
particles.
2. Description of the Related Art
[0003] The following description and examples are not admitted to
be prior art by virtue of their inclusion in this section.
[0004] Generally, flow cytometers are devices configured to use
optical techniques to measure one or more characteristics of
particles or cells in a fluid flowing through the devices. This
particle or cell interrogation can be exploited for a number of
purposes such as assaying for various chemical and biological
molecules. Although flow cytometers offer a number of advantages,
the devices have a number of disadvantages. For example, flow
cytometers generally utilize optical components that are sensitive
to their environment. Furthermore, flow cytometers are typically
time consuming to manufacture, complicated to operate, and
expensive. These characteristics often restrict the use of flow
cytometers to highly trained technicians. Moreover, some samples
need to be processed before being run through a flow cytometer and,
therefore, significant laboratory resources and other equipment are
often needed for the analysis of assays.
[0005] It would, therefore, be advantageous to develop systems that
measure characteristics of particles or cells in a fluid and are
relatively simple to operate. In addition, it would be beneficial
for such systems to be capable of performing the measurements
without requiring significant laboratory resources for
pre-processing of the sample fluids. Furthermore, it would be
advantageous for the systems to include components which are
substantially insensitive to their environments. Moreover, it would
be beneficial for such systems to be relatively inexpensive and not
time consuming to manufacture.
SUMMARY OF THE INVENTION
[0006] The following description of various embodiments of systems
and chip-based flow cytometers are not to be construed in any way
as limiting the subject matter of the appended claims.
[0007] An embodiment of a system for processing and analyzing
biological or environmental samples includes an automated assay
preparation module configured to process a sample into a fluid
assay with fluorescently tagged particles and a microfluidic
analysis module coupled to the
automated assay preparation module, wherein the microfluidic
analysis module includes a chip-based flow cytometer.
[0008] An embodiment of a system for analyzing a fluid sample
includes a channel for routing a fluid sample with magnetic
particles through the system and a means for inducing a magnetic
field along at least a portion of the channel such that the
magnetic particles flow within a predetermined region of the fluid
sample.
[0009] Another embodiment of a system for analyzing a fluid sample
includes a channel for routing a fluid sample having fluorescently
tagged particles through the system and an illumination subsystem
including a light source system and an optical system collectively
configured to direct light toward an interrogation region of the
channel. The system further includes a measurement subsystem with
an aspherical mirror configured to gather fluorescence emitted from
the magnetic particles and an examination system for analyzing the
collected fluorescence.
[0010] An embodiment of a chip-based flow cytometer includes a
first input conduit for receiving a fluid sample with fluorescently
tagged particles, a second distinct conduit for receiving a sheath
fluid, and a fluid flow chamber coupled to the first and second
input conduits. The fluid flow chamber is configured to generate a
fluid stream with the sample fluid confined within the sheath fluid
and having a first dimension of up to approximately 80 microns in a
vertical direction perpendicular to the flow of the fluid stream
and a second dimension of up to approximately 25 microns in a
horizontal direction perpendicular to the flow of the fluid
stream.
[0011] Another embodiment of a chip-based flow cytometer includes a
channel for routing a fluid sample having fluorescently tagged
particles through the flow cytometer. In addition, the chip-based
flow cytometer includes an illumination subsystem with a light
source system and an optical system collectively configured such
that individual light sources within the light source system direct
light toward different spots within the interrogation region.
Moreover, the chip-based flow cytometer includes a measurement
subsystem having a collection system configured such that the
fluorescent light emitted from the magnetic particles at each of
the different spots is collected by a different detector of the
collection system and an examination system for analyzing the
collected fluorescence.
BRIEF DESCRIPTION OF THE DRAWINGS
[0012] Further advantages of the present invention may become
apparent to those skilled in the art with the benefit of the
following detailed description of the preferred embodiments and
upon reference to the accompanying drawings in which:
[0013] FIG. 1 is a schematic diagram of a portable system
configured to process and measure fluidic samples;
[0014] FIG. 2 is an isometric view of an exemplary embodiment of a
microfluidic analysis module that may be included in the portable
system referenced in FIG. 1;
[0015] FIG. 3 is an isometric view of an exemplary embodiment of a
fluid focusing subsystem that may be included in the microfluidic
analysis module referenced in FIG. 2;
[0016] FIG. 4 is a side view of an exemplary collection of light
sources, collection optics and detectors included in the
microfluidic analysis module referenced in FIG. 2;
[0017] FIG. 5 illustrates a cross-sectional view of an exemplary
system configured for preparing a fluid assay;
[0018] FIG. 6 illustrates a schematic drawing of a different
exemplary system configured for preparing a fluid assay;
[0019] FIG. 7 illustrates a prospective view of an exemplary system
which follows the schematic layout of FIG. 6;
[0020] FIG. 8 illustrates a magnified prospective view of the
reaction vessel included in the system depicted in FIG. 7;
[0021] FIG. 9 illustrates cross-sectional view of the reaction
volume of the reaction vessel depicted in FIG. 8 during a series of
process steps for preparing a fluid assay;
[0022] FIG. 10 illustrates a magnified prospective view of the
reagent pack receiver of the system depicted in FIG. 7 as well as a
reagent pack;
[0023] FIG. 11A-C illustrates cross-sectional view of the reagent
pack receiver depicted in FIG. 10 with a reagent pack arranged
therein and in a variety of positions to portray oscillation of the
reagent pack;
[0024] FIG. 12 illustrates a flowchart of an exemplary method for
preparing a fluid assay;
[0025] FIG. 13 illustrates a flowchart of an exemplary method for
processing a fluid sample into a form that is compatible with a
predetermined assay;
[0026] FIG. 14 illustrates a flowchart of an exemplary method for
preparing a nucleic acid assay;
[0027] FIG. 15 illustrates a flowchart of an exemplary method for
preparing an immunoassay.
[0028] FIG. 16 is an isometric top view of an exemplary embodiment
of a reaction cartridge that may be included in the system
embodiments described herein;
[0029] FIG. 17 illustrates different isometric views of another
exemplary embodiment of a reaction cartridge, at various times
during operation of the reaction cartridge, that may be included in
the system embodiments described herein; and
[0030] FIG. 18 is an isometric side view and a top view of a
reagent storage module that may be included in the portable systems
described herein.
[0031] While the invention is susceptible to various modifications
and alternative forms, specific embodiments thereof are shown by
way of example in the drawings and may herein be described in
detail. The drawings may not be to scale. It should be understood,
however, that the drawings and detailed description thereto are not
intended to limit the invention to the particular form disclosed,
but on the contrary, the intention is to cover all modifications,
equivalents and alternatives falling within the spirit and scope of
the present invention as defined by the appended claims.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0032] Turning now to the drawings, systems for processing and
analyzing fluid samples are provided. In general, the systems
described herein may be used to process and/or analyze samples
including, but not limited to, bodily fluids, environmental
samples, and/or biological tissues and substances. Furthermore, as
described in more detail below, the systems described herein are
configured for processing samples with fluorescently tagged
particles infused therein. In some embodiments, the particles may
be magnetic. It is noted that the figures are not necessarily drawn
to scale. In particular, the scale of some elements in some of the
figures may be greatly exaggerated to emphasize characteristics of
the elements. In addition, it is further noted that the figures are
not drawn to the same scale. Elements shown in more than one figure
that may be similarly configured have been indicated using the same
reference numerals.
[0033] FIG. 1 illustrates an exemplary portable system for
processing and analyzing fluidic samples. In general, the portable
systems described herein may include a processing module, an
analysis module, and support modules including, but not limited to,
fluidics, fluid storage, power supply, computer hardware (and
software), display, and a human interface. FIG. 1 illustrates
portable system 12 opened showing an exemplary assortment and
placement of modules within a base portion and lid of the system.
It is noted, however, the portable systems described herein are not
necessarily so limited. In particular, other portable systems
having fewer or more modules than the ones described in reference
to FIG. 1 may be considered. In addition or alternatively, one or
more of the modules described in reference to portable system 12
may be arranged in a different position relative to the other
modules. For instance, in some cases, portable system 12 may
include different modules or no modules in the lid of the system.
In other cases, portable system 12 may not include a lid. In any
case, the "portability" of the systems described herein may refer
to systems being able to be transported by a user.
[0034] As shown in FIG. 1, portable system 12 may include computer
1, display 2, battery 3, and human interface 9, all of which may
include any suitable component known in the art for the
corresponding device. In some cases, computer 1 may be used to
convert measurements taken by microfluidic analysis module 5 (e.g.,
fluorescence measurements, light scatter measurements, etc.) into
values which reflect the amount of analyte present in a sample. In
addition or alternatively, computer 1 may be used to control the
operations of other components within portable system 12, such as
but not limited to the components within processing module 6 and
microfluidic analysis module 5. In any case, display 2 may be used
to present measurement values and/or converted values to a user. In
addition or alternative to the inclusion of battery 3, portable
system 12 may be equipped with an AC/DC converter. Human interface
9 may be configured such as to control the initiation of processing
or analyzing a fluid and/or manipulate the measurements acquired
during analysis. As further shown in FIG. 1, portable system 12 may
include reagent cartridge storage 4, processing module 6,
microfluidic analysis module 5, sheath fluid module 7, and pump
module 8, each of which may be configured as described further
herein. In some embodiments, the systems described herein may
include one or more interchangeable modules that can be replaced
such that the systems can be used for different applications.
Possible applications of the embodiments described herein include,
but are not limited to, a medical diagnostic device or
environmental biological sampler. The modular nature of the
embodiments allows for easy and inexpensive reconfigurations from
one application to another.
[0035] In some embodiments, microfluidic analysis module 5 may
include a highly integrated chip-based flow cytometer. More
specifically, microfluidic analysis module 5 may include a fixed
configuration of some or all of the following components fabricated
as semiconductor devices: microfluidic channels, photo multiplier
tubes, avalanche photodiodes, pin photo diodes, magnetic
transducers, optical filters, lenses, mirrors, resonators, optical
gain mediums, and excitation sources such as light emitting diodes,
resonant cavity light emitting diodes, diode lasers, vertical
cavity surface emitting lasers, phosphorescent materials,
radioactive materials, plasmas, and acoustic sources. An exemplary
configuration of components for microfluidic analysis module 5 is
illustrated in FIG. 2. In particular, FIG. 2 illustrates an
embodiment of microfluidic analysis module 5 in which fluidic
channels, fluidic focusing components, and collection optics are
fixedly arranged within semiconductor substrate 10. In some
embodiments, microfluidic analysis module 5 may also include light
sources (e.g., light sources 14 and 16 in FIG. 2) and optical
components (e.g., beam splitter 18 in FIG. 2) fixedly arranged
relative to each other and semiconductor substrate 10. In
alternative cases, light sources 14 and 16 and/or beam splitter 18
may be integrated within semiconductor substrate 10.
[0036] In general, the chip-based flow cytometer of microfluidic
analysis module 5 may be configured to measure one or more
characteristics of fluorescently tagged particles which are infused
within a fluid flowing through the flow cytometer. More
specifically, the chip-based flow cytometer may be configured to
measure fluorescence emitted by particles within a sample and use
the measurements to determine the presence of a reagent associated
with the particles. Based on the presence or absence of the
reagent, the system can determine the presence or absence of one or
more analytes in the samples and may also determine other
characteristics of the one or more analytes such as concentration
within the sample. In some cases, light scattering characteristics
of the particles may be additionally measured by the chip-based
flow cytometer to determine the presence/absence of analyte within
a sample and/or classifications of the particles.
[0037] In general, the term "particle" as used herein may refer to
any substrate used for the analysis of chemistry, biological, and
environmental assays and may specifically refer to articles used to
provide and/or support molecular reactions for the qualification
and/or quantification of an analyte of interest including but not
limited to kinase activity. In addition, the term "particle" may
reference articles of a broad range of sizes, such as but not
limited to articles having dimensions between approximately 1 nm
approximately 300 .mu.m. Hence, the term "particle" may refer to a
number of different materials and configurations, including but not
limited to particles, beads, polystyrene beads, microparticles,
gold nanoparticles, quantum dots, nanodots, nanoparticles,
composite particles (e.g., metal-polymeric particles or
magnetite-polymeric particles), nanoshells, nanorods, nanotubes,
microbeads, latex particles, latex beads, fluorescent beads,
fluorescent particles, colored particles, colored beads, tissue,
cells, micro-organisms, spores, organic matter, any non-organic
matter, or any combination thereof. Accordingly, any of such terms
may be interchangeable with the term "particle" used herein.
[0038] Recent innovations have allowed simultaneous analysis of
multiple assays through the use of distinguishable carrier
particles. One example of such an assay system is the xMAP.RTM.
technology that is commercially available from Luminex Corporation
of Austin, Tex. The xMAP technology uses a family of dyed particles
onto which one or more assay-specific reagents may be applied
(e.g., by coupling to one or more functional groups on the surface
of the particles). The particle platform employs different sets of
particles distinguishable by fluorescence. For example, the sets of
particles may be distinguishable by wavelength of fluorescence,
intensity of fluorescence, ratio of intensities of fluorescence at
different wavelengths, etc. In general, the variation of
fluorescence may be integrated by different dyes and/or
fluorophores incorporated into the particles and/or are coupled to
a surface of the particles. In some embodiments, the sets of
particles may be additionally distinguishable by size and/or shape.
In any case, a particle platform having distinguishable carrier
particles is generally advantageous because it uses fluid based
kinetics to bind several different analytes to the assay-specific
reagents. In particular, the particles can be used to test for more
than 100 different analytes in a sample.
[0039] In general, each of the different sets of particles may have
a different reagent coupled to the particles. The different
reagents may selectively react with different analytes in the fluid
sample. In other words, each of the different reagents may react
with one analyte in a sample, but may not substantially react with
any other analytes in the sample. In some cases, one or more
additional detectable reagents may be allowed to react with one or
more of the analytes. The one or more additional reagents may be
detectable (and possibly distinguishable) by fluorescence (e.g.,
wavelength of fluorescence, intensity of fluorescence, etc.). In
addition to the enhanced reaction kinetics, the use of a
multiplexed particle platform advantageously allows a user to
simply add or remove one or more subsets of particles, to or from
the population to which the sample is exposed, to change the tests
being performed in a panel.
[0040] Turning back to FIG. 2, the operation of the flow cytometer
may include introducing the sample on which an assay is being
performed into input conduit 22. Prior to being illuminated, the
sample may, in some embodiments, be combined with a sheath fluid in
fluid flow chamber 24 as shown in FIG. 2. The sheath fluid may be
pumped by pump module 8 from sheath fluid module 7, enter the
analysis module through input conduit 26, and may flow through
sheath fluid channel 28 to fluid flow chamber 24. Therefore, the
sample and sheath fluids are injected into the flow cytometer
through separate input ports. The two fluids meet in fluid flow
chamber 24 and the chamber is configured such that a fluid stream
is generated which includes the sheath fluid encompassing the
sample fluid. An exemplary configuration of fluid flow chamber 24
is illustrated in FIG. 3. It is noted, however, that other fluid
combining techniques may be used for the systems described herein
including, but not limited to, hydrodynamic focusing,
electrokinetic focusing, acoustic wave focusing, and magnetic
focusing. Consequently, the systems described herein are not
necessarily limited to the depictions of FIGS. 2 and 3. For
example, a fluid combining device that may be additionally or
alternatively used with the flow cytometer of microfluidic analysis
module 5 may be a hydrodynamic focusing cuvette arranged at a
joined interface of channels 20 and 28. The cuvette may perform
highly uniform focusing and confinement of the sample stream in all
directions that lie perpendicular to the axis of the cuvette.
[0041] As shown in FIG. 3, fluid flow chamber 24 may be configured
to confine the sample fluid within the sheath fluid in both the
vertical and horizontal directions. In this manner, the sheath
fluid may surround the sample fluid from all sides. This physical
confinement technique confines the sample fluid to approximately
the center of the stream generated from the fluid flow chamber 24
and, in some cases, narrows the sample fluid to a fraction of its
previous diameter. By reducing the diameter of the sample fluid,
particles in the flow are pulled farther apart along the fluid
channel allowing for easier interrogation. It has been found,
however, that the incorporation of fixed chip-based components
within a flow cytometer offers notable measurement precision even
with relatively wide fluid streams. Thus, fluid flow chamber 24 may
be configured to narrow a sample fluid diameter to a lesser degree
than in conventional systems. For instance, fluid flow chamber 24
may be configured to reduce the diameter of the sample fluid within
channel 25 to less than 10 times its diameter within channel 20 or,
more specifically, about 5 times its diameter within channel 20.
Narrowing the sample fluid to a lesser degree may advantageously
reduce the amount of sheath fluid needed, reducing costs and
waste.
[0042] Another manner to describe the confinement adaptations of
fluid flow chamber 24 is to specify exemplary dimensions of the
sample stream within the fluid stream it is configured to generate.
For example, fluid flow chamber 24 may be configured such that the
sample fluid has a first dimension of up to approximately 80
microns in a vertical direction perpendicular to the flow of the
fluid stream (i.e., a first dimension of up to approximately 80
microns in the z-direction when flow of the fluid is in the
x-direction). In addition, fluid flow chamber 24 may be configured
such that the sample fluid has a second dimension of up to
approximately 25 microns in a horizontal direction perpendicular to
the flow of the fluid stream (i.e., a second dimension of up to
approximately 25 microns in the y-direction when flow of the fluid
is in the x-direction). Larger or smaller dimensions for the sample
fluid, however, may be considered as well, depending on the design
specifications of the flow cytometer.
[0043] In any case, the fluid stream generated from fluid flow
chamber 24 may flow through channel 25 as shown in FIGS. 2 and 3.
More specifically, the fluid stream generated from fluid flow
chamber 24 may flow to an optical interrogation region of the flow
cytometer, denoted as collection optics 30 along channel 25 In FIG.
2. After passing through the optical interrogation region, the
combined sample and sheath fluids may exit the analysis module
through outlet 32. In some embodiments, fluid channel 25 may be
configured to be non-removable. In other words, portable system
[[25]]12 may include a fluid channel that is not disposable. In
contrast, the fluid channels in existing chip scale technologies
are designed to be formed in a removable substrate so that the
fluid channels may be disposable. Therefore, a distinguishing
feature of the embodiments described herein is that the fluid
channel may be neither removable nor disposable. In some
embodiments, it may be advantageous to arrange the sample fluid of
the generated fluid stream in a predetermined location of fluid
channel 25. More specifically, it may be advantageous to have the
particles within the sample fluid arranged in a relatively
predictable location in channel 25 (e.g., approximately the center
of the fluid channel) such that the angles at which light may be
directed toward the particles and emissions collected from the
particles for optimum operation of the flow cytometer may be
anticipated.
[0044] In order to accommodate the arrangement of particles within
a predetermined location of channel 25, the systems described
herein may, in some embodiments, include means 27 for inducing a
magnetic field along at least a portion of channel 25 as shown in
FIG. 2. For example, the flow cytometer of microfluidic analysis
module 5 may include a solenoid coil wrapped around fluid channel
25. It is noted that the systems described herein are not
necessarily limited to such a magnetic field inducing mechanism. In
particular, other means for inducing a magnetic field along at
least a portion of channel 25 may be additionally or alternatively
used. In any case, means 27 may, in some embodiments, extend along
the entirety of fluid channel 25 (i.e., between fluid flow chamber
24 and output 32). In yet other embodiments, means 27 may extend
along a limited section of fluid channel 25. For example, means 27
may, in some embodiments, be restricted to a portion of fluid
channel 25 extending between fluid flow chamber 24 and through the
interrogation region denoted by collection optics 30. In yet other
embodiments, means 27 may, in some embodiments, may be restricted
to a shorter portion of fluid channel 25 such as in close proximity
to and including the interrogation region. In any case, means 27
may be configured to generate a magnetic field around fluid channel
25 in some embodiments. Alternatively, means 27 may be configured
to generate a magnetic field along less than the circumferential
periphery of fluid channel 25.
[0045] As noted above, the sample fluid surrounded by the sheath
fluid flows from fluid flow chamber 24 to the optical interrogation
region of fluid channel 25. In the optical interrogation region,
light sources 14 and 16 illuminate the sample fluid. Fluorescence
emitted by the particles within the sample fluid is collected by
collection optics 30 and directed to one or more detectors of the
flow cytometer, which may be fixedly arranged relative to substrate
10 at an angle anticipated for the emissions. Therefore, the
optical interrogation region of fluid channel 25 is defined by the
locations along the fluid channel that are illuminated by the light
beams and the locations along the fluid channel at which the
collection optics collect light (e.g., fluorescent light, scattered
light, or some combination thereof). As shown in FIG. 2, the light
from light sources 14 and 16 may be directed to different locations
along fluid channel 25 that are spaced apart from each other. Such
locations may be referred to herein as interrogation spots. The
interrogation spots may include any suitable spacing, depending on
the design specifications of the flow cytometer.
[0046] To facilitate multiple interrogation spots, the flow
cytometer may, in some embodiments, include a beam splitter between
one or more of light sources 14 and 16 and fluid channel 25, such
as shown with the inclusion of beam splitter 18 in FIG. 2. In
general, beam splitter 18 may include any suitable optical
element/s that is configured to split light into two or more
different beams of light. Thus, beam splitter 18 is not restricted
to the depiction of splitting light into three beams as illustrated
in FIG. 2. Furthermore, the cytometer shown in FIG. 2 is not
restricted to using beam splitter 18 with respect to light source
14. In particular, the flow cytometer may additionally or
alternatively include a beam splitter positioned to split light
directed from light source 16. In some embodiments, it may be
advantageous to include multiple light sources within the flow
cytometer, particularly one for each interrogation spot. As such,
in some cases, the flow cytometer may not include beam splitters.
In particular, due to the miniaturization of device components
within the chip-based flow cytometer, the detectors of the flow
cytometer may need to collect full emissions from an interrogation
spot in order to adequately measure the fluorescence of a
particular channel. Consequently, in addition to including a
different light source for each interrogation spot, the flow
cytometer may include a different detector for each interrogation
spot. Furthermore, the flow cytometer may include a different set
of optical components, including but not limited to mirrors, lens,
and/or filters, for each interrogation spot. An exemplary
arrangement of light sources, optical elements, and detectors used
for the flow cytometers described herein is shown in FIG. 4 and
described in more detail below.
[0047] In any case, although FIG. 2 shows the inclusion two light
sources with the flow cytometer depicted therein, it is to be
understood that the flow cytometer may include any number of light
sources within its illumination subsystem. Any suitable light
sources may be employed within the flow cytometer, such as but not
limited to light emitting diodes (LEDs), lasers, arc lamps, fiber
illuminators, light bulbs, incandescent lamps, or any other
suitable light sources known in the art. In addition, the one or
more light sources may be configured to emit monochromatic light,
polychromatic light, broadband light, or some combination thereof.
Furthermore, light from the one or more light sources may be
directed to fluid channel 25 in any suitable direction (e.g., by
suitable positioning of the light sources and/or by using suitable
light directing optical elements). As such, although FIG. 2
illustrates light sources 14 and 16 directing light toward fluid
channel 25 at substantially opposite directions, the systems
described herein are not necessarily so limited.
[0048] As noted above, FIG. 4 illustrates an exemplary arrangement
of light sources, optical elements, and detectors used for the flow
cytometers described herein. The exemplary arrangement includes
four light sources 38, which are substantially perpendicularly
aligned with four distinct collection optics 42 and four distinct
detectors 44. In other words, collection optics 42 are arranged to
collect light emitted from the particles within the sample fluid
along a direction that is substantially perpendicular to a
direction at which light from light sources 38 is directed.
Collection optics 42 may include one or more refractive optical
elements, each of which is configured to collect light fluoresced
and/or scattered from a corresponding location along the fluid
channel. Detectors 44 may include any suitable detectors such as
but not limited to silicon avalanche photodiodes. In some cases,
each of light sources 38 may be configured to emit light having
substantially the same wavelength. In other embodiments, however,
one or more of light sources 38 may be configured to emit light at
a different wavelength than the light emitted by other of light
sources 38.
[0049] In some embodiments, the systems described herein may
include filters 48 positioned in between collection optics 42 and
detectors 44. Filters 48 may include any suitable optical elements
known in the art such as but not limited to spectral filters that
are configured to limit the wavelength(s) of the light detected by
detectors 44. As further shown in FIG. 4 the exemplary arrangement
may include illumination optics 50. Illumination optics 50 may
include a number of refractive optical elements, which may include
any suitable refractive optical elements known in the art. Each of
the refractive optical elements of illumination optics 50 may be
configured to collimate one of light beams 52 generated by light
sources 38 of semiconductor light emitters. In this manner, the
light beams may be directed to channel 25 along directions that are
substantially parallel to each other. Although FIG. 4 is shown to
include four sets of components, it is to be understood that the
systems described herein may include any suitable number of
component sets.
[0050] FIG. 5 illustrates a different exemplary arrangement of
light sources, optical elements, and detectors used for the flow
cytometers described herein which employs a configuration referred
to herein as 90 degree off-axis illumination. In such
configurations, the system may include an optical element
configured to direct light to fluid channel 25 at an angle that is
about 90 degrees from the angle at which light sources 38 are
configured to direct light to the fluid channel. Alternatively,
light sources 38 may be arranged to direct light at a 90 degree
angle to fluid channel 25. More specifically, a mirror or other
suitable optical element may be arranged such that light directed
from light sources 38 strikes fluid channel 25 at a direction that
is substantially perpendicular to both the fluid channel and the
optical stack that includes collection optics 42 and detectors 44
such that the 90.degree. side scatter component of the light is
collected and detected for the optical interrogation method. To
illustrate such a configuration, FIG. 5 depicts the exemplary
arrangement of components along an x-z plane, wherein fluid flow in
channel 25 is in the x-direction and the position of the optical
elements and detectors are in the z-direction relative to channel
25. In such embodiments, the light source/s is arranged in the
y-direction relative to channel 25 and, therefore, is not depicted
in FIG. 5. Rather, light beam 54 directed from the light source/s
is shown coming out of the page denoting the 90 degree off-axis
illumination. Although FIG. 5 illustrates a single set of
components, it is to be understood that the systems described
herein may include any suitable number of distinct sets of
components as similarly described for the configuration depicted in
FIG. 4.
[0051] In some embodiments, the flow cytometers described herein
may include an aspherical mirror for gathering the fluoresced
and/or scattered light. In particular, an aspherical mirror may
advantageously distort the collected light to a level within a
range of light which the detectors may be capable of detecting.
More specifically, the detection range of the detectors cannot
generally be scaled down in the same manner as the other devices in
the chip-based flow cytometer and, thus, it may be beneficial to
incorporate an aspherical mirror to alter collected light into a
range which is within the ability of the detectors. In some
embodiments, the aspherical mirror may be coated with an
anti-reflective coating (ARC) to aid in rejection of unwanted
wavelengths, increasing the signal-to-noise ratio of the collected
light. In some embodiments, an ARC that is configured to reflect
fluorescent emissions rather than scattered light may be employed.
In other embodiments, an ARC that is configured to reflect
scattered light in addition to fluorescent emissions may be
employed. Such configurations may be facilitated by the wavelength
range the ARC is configured to reflect. As shown in FIG. 5,
aspherical mirror 56 may be arranged on the side of fluid channel
25 opposing collection optics 42, filter 48, and detector 44. In
this manner, aspherical mirror 56 may increase the amount of light
collected by the flow cytometer. It is noted that the configuration
of components described in reference to FIG. 4 may also include an
aspherical mirror.
[0052] In response to the excitation, particles in the sample flow
may fluoresce thereby signaling the presence of at least one of the
following materials with the sample fluid including, but not
limited to, particle identification dye, enzymes, proteins, amino
acids, DNA, RNA, antibodies, and antigens. In addition to direct
fluorescence being used as an indicator, the presence of a magnetic
field may be used to further modulate the excitation of the
particle or emission from the particle. One advantageous feature of
the analysis module is the ability to measure or "read" and
classify fluorescent particles in real time using output generated
by multiple channels of the analysis module. In some embodiments,
the system may be configured to perform the measurements by gating
a response of particles to illumination as the sample flows through
the interrogation region in fluid channel 25. For example, as the
sample flows through the optical interrogation region of the
analysis module, gating the response of the particles to
illumination may be performed by collecting and detecting the
fluorescence and/or scattered light with the collection optics and
the one or more detectors and comparing the output of the one or
more detectors to a predetermined threshold. If the output is above
the predetermined threshold, the system may determine that a
microsphere caused the fluorescence and/or scattered light and
therefore that the microsphere is passing through the interrogation
region. As such, the fluorescence and/or scattered light
corresponding to the microsphere may be recorded or otherwise
processed by the system (e.g., processed for real-time
classification).
[0053] In another embodiment, the system may be configured to
perform the measurements by distinguishing between single particles
flowing through the interrogation region of fluid channel 25 and
multiple particles flowing through the interrogation region at
substantially the same time. For example, scattered light detected
by one or more detectors of the analysis module may generally be
proportional to the volume of the particles that are illuminated by
the one or more light sources. Therefore, output of the one or more
detectors may be used to determine a diameter and/or volume of the
particles that are in the optical interrogation region. In
addition, the output of the one or more detectors and the known
size or volume of the particles may be used to identify more than
one microsphere that are stuck together or that are passing through
the optical interrogation region at approximately the same time.
Therefore, such particles may be distinguished from other sample
particles and calibration particles. Furthermore, the output of the
one or more detectors may be used to distinguish between sample
particles and calibration particles if the sample particles and
calibration particles have different sizes.
[0054] As noted above, portable system 12 may, in some embodiments,
include processing module 6. Such a module may generally be
configured to process samples before the samples are introduced
into microfluidic analysis module 5. The processing may include any
one or more of particle size filtering, centrifuging, analyte
isolation, analyte amplification, washing of the sample, cell
lysing, clotting factor neutralization, pH regulation, temperature
cycling, reagent mixing, and assay reaction. Other processing steps
may be considered as well. Exemplary configurations of systems
which may be used for processing module 6 are illustrated in FIGS.
6-9 and described in more detail below. Exemplary components which
may be used to support such systems are illustrated in FIGS.
10-11A-C and 16-18. In addition, methods for operating such process
modules are outlined in flowcharts of FIGS. 12-15. In yet other
embodiments, portable system 12 may not include processing module
6. In such cases, portable system 12 may be configured to analyze
raw samples (i.e., samples which have not be pre-processed) or
samples which have been pre-processed independent of portable
system 12.
[0055] FIG. 6 illustrates a schematic drawing of fluid assay
preparation system 51 and FIG. 7 illustrates a perspective view of
an exemplary configuration for fluid assay preparation system 51.
As shown in FIGS. 6 and 7, fluid assay preparation system 51 may
include sample inlet 53 for introducing a fluid sample into system
51. In some embodiments, fluid assay preparation system 51 may
include sample preprocessing system 54 for processing the sample
prior to being introduced into inlet 53. The preprocessing system
may be configured to perform any of the steps described below in
reference to FIG. 13 or any state transformation steps. For
example, a wetted wall cyclone may be considered for condensing a
gas sample into a liquid. Fluid assay preparation system 51 further
includes reagent pack 56 including a plurality of vessels each
filled with different reagents. Reagent pack 56 may also include
one or more vessels for receiving waste streams from the fluid
assay preparation performed by system 51. It is noted that the
reagents noted in FIG. 6 are exemplary and fluid assay preparation
system 51 is not necessarily so limited. For processing a sample,
reagent pack 56 may be arranged within reagent pack receiver 64
(shown in FIG. 7) and coupled to multi-port valve 58, which in turn
may be coupled to reaction vessel 60 by fluidic lines. In addition,
input 53 may be coupled to multi-port valve 58. In an alternative
embodiment, fluid assay preparation system 51 may include one or
more individual valves respectively coupled to the vessels of
reagent pack 56 and/or input 53. In any case, reagent pack 56 may
be stored within reagent storage module 4 of portable system 12
prior to being used by processing module 6.
[0056] As shown in FIGS. 6 and 7, fluid assay preparation system 51
may further include control electronics 66 and pump 62 coupled to
multi-port valve 58. Alternatively, fluid assay preparation system
51 may use pump module 8 of portable system 12. In either case,
control electronics 66, pump 62 or pump module 8, and multi-port
valve 58 may be collectively configured such that the sample
introduced within input 53 and the reagents within reagent pack 56
may be introduced into reaction vessel as well as drawn therefrom,
preferably at separate stages within the fluid assay preparation
process. A more detailed description of exemplary routings of the
reagents to and from reaction vessel 60 is provided in reference to
FIGS. 12-15 below.
[0057] As shown in FIG. 7, fluid assay preparation system 51 may
further include storage medium 68 coupled to control electronics
66. In general, storage medium 68 may include program instructions
which are executable by a processor for automating the preparation
of a fluid assay, such as but not limited to the steps described in
below in reference to the flowcharts depicted in FIGS. 12-15. The
storage medium may include but is not limited to a read-only
memory, a random access memory, a magnetic or optical disk, or a
magnetic tape. The program instructions may be implemented in any
of various ways, including procedure-based techniques,
component-based techniques, and/or object-oriented techniques,
among others. For example, the program instructions may be
implemented using ActiveX controls, C++ objects, JavaBeans,
Microsoft Foundation Classes ("MFC"), or other technologies or
methodologies, as desired. In some embodiments, storage medium 246
may include a processor for executing the program instructions. In
other embodiments, however, storage medium 246 may be configured to
be coupled to a processor (e.g., by a transmission medium). In
either case, the processor may take various forms, including a
personal computer system, mainframe computer system, workstation,
network appliance, Internet appliance, personal digital assistant
(PDA), a digital signal processor (DSP), field programmable gate
array (FPGA), or other device. In general, the term "computer
system" may be broadly defined to encompass any device having one
or more processors, which executes instructions from a memory
medium. It is noted that storage medium 68 is shown coupled to
control electronics 66 by dotted lines in FIG. 7 to indicate that
the connection may be either fixed or detachable.
[0058] In some embodiments, fluid assay preparation system 51 may
be configured for multiple use operation and, therefore, may be
reusable. In particular, fluid assay preparation system 51 may be
configured to prepare multiple fluid assays, including those of the
same or different makeup. In other embodiments, fluid assay
preparation system 51 may be configured for single use operations
and, therefore, may be configured to be disposable. In either case,
reagent pack 56 may be configured for single or multiple use
operations. As such, reagent pack 56 may be configured to be
disposable (i.e., thrown away after a single fluid assay has been
prepared) or may be reusable (i.e., includes reagent amounts
sufficient to prepare multiple assays). In the latter case, the
vessels of reagent pack 56 may be configured to be disposed after
one or more of the reagents are consumed or may be configured to be
refilled. In either embodiment, reagent pack 56 allows for easy
replacement and may be generally inexpensive to maintain and
produce.
[0059] An exemplary configuration for reaction vessel 60 is shown
in FIG. 8. As shown in FIG. 8, reaction vessel 60 may include an
injection/aspiration needle which may be used to receive and
dispatch solutions to and from reaction vessel 60, such as from/to
reagent pack 56 and input 53 of fluid assay preparation module 50.
Reaction vessel 60 further includes an analysis module aspiration
needle, which may be used to dispatch solutions to microfludic
analysis module 5. Reaction vessel 60 may further include a vent
port, magnet actuator, and magnet 70 as shown in FIG. 8. In some
embodiments reaction vessel 60 may further include a sonication
system or, more generally, fluid assay preparation system 51 may
include a sonication system in proximity to reaction vessel 60. An
exemplary manner in which to utilize the magnet actuator and magnet
for preparing fluid assay is shown in FIG. 9. In particular, FIG. 9
includes snapshot I in which the reaction vessel volume is empty
and, therefore, no fluid sample or reagent has been introduced
therein. FIG. 9 further illustrates snapshot II in which the
reaction vessel volume is filled with a fluid sample, magnetic
particles and, in some cases, one or more reagents. Snapshot III of
FIG. 9 illustrates magnet 70 actuated in proximity to the reaction
vessel volume to immobilize the magnetic particles and snapshot IV
of FIG. 9 illustrates the reaction vessel volume having the fluid
removed when the magnetic particles are immobilized. A more
detailed description of possible stagings of such an operation
during a fluid assay preparation procedure is provided below in
reference to FIGS. 12-15.
[0060] FIG. 10 illustrates an exemplary configuration for reagent
pack receiver 64. In particular, FIG. 10 illustrates reagent pack
receiver 64 including a slot to receive reagent pack 56. As shown
in FIG. 10, the slot may include septum piercing needles to
puncture vessels of reagent pack 56 and allow the reagents to be
routed to a multi-port valve 58 and/or any valve respectively
coupled thereto. The slot and piercing needles allow for easy
removal and installation while not requiring the operator to make
the fluidic connections. In some embodiments, it may be
advantageous to configure reagent pack receiver 64 to tilt back and
forth. In particular, it may be advantageous, in some embodiments,
to agitate one or more reagents within reagent pack 56. For
example, it may be advantageous to agitate particles in solution to
reduce clumping in a reagent pack vessel. Such agitation may be
incorporated within reagent pack receiver 64 by tilting mechanism
72, various positions of which are illustrated in cross-sectional
views of reagent pack receiver 64 in FIGS. 11A-C. In some
embodiments, reagent pack 56 may include a small air bubble within
one or more of the reagent vessels to main suspension of components
within the respective reagents during oscillation of tilting
mechanism 72. The presence of an air bubble may be particularly
advantageous for reagents comprising particles to maintain their
suspension within the accompanying slurry. In general, the
operation of titling mechanism 72 may be continuous, periodic, or
sporadic.
[0061] Turning to FIGS. 12-15, flowcharts of exemplary methods for
preparing fluid assays are shown. As noted above, the storage
mediums of the systems described herein may include program
instructions which are executable by a processor for automating the
preparation of a fluid assay, such as but not limited to the steps
described in below in reference to the flowcharts depicted in FIGS.
12-15. Therefore, the methods described in reference to FIGS. 12-15
may be referred to as "computer-implemented methods". It is noted
that the terms "method" and "computer-implements method" may be
used interchangeably herein. It is also noted that the
computer-implemented methods and program instructions of the
systems described herein may, in some cases, be configured to
perform processes other than those associated with fluid assay
preparation and, therefore, the computer-implemented methods and
program instructions of systems described herein are not
necessarily limited to the depiction of FIGS. 12-15.
[0062] As shown in FIG. 12, a method for preparing a fluid assay
may include block 80 in which a fluid sample is mixed with a first
set of magnetic particles. In reference to system 51 of FIG. 12,
the process of block 80 may include infusing a fluid sample into
input 53 and routing the fluid through multi-port valve 58 to
reaction vessel 60. Subsequent or concurrent thereto, a first set
of magnetic particles from reagent pack 56 may be routed to through
multi-port valve 58 to reaction vessel 60 to mix with the fluid
sample. The fluid sample may, in some embodiments, be preprocessed
(i.e. processed prior to being introduced into the systems) such as
by the processing steps described below in reference to FIG. 13. In
addition or alternatively, the state of the sample may be
transformed prior to being introduced into the systems. For
example, a solid sample, such as biological tissue, may be
suspended within a buffer or an air sample may be condensed into a
liquid. In other embodiments, the fluid sample may not be processed
prior to being introduced into the systems. In such cases, system
51 may, in some embodiments, be configured to conduct some of the
steps described below in reference to FIG. 13. For example, input
53 may, in some cases, include a filter. In addition or
alternatively, reagent pack 56 may include a lysing agent for
lysing cells within the fluid sample. In such cases, it may be
particularly advantageous for system 51 to include a sonication
system to insure the cells are lysed after a certain incubation
time.
[0063] It is noted that other reagents which are known for
processing a fluid sample may be additionally or alternatively
included within reagent pack 56 for mixing with the magnetic
particles and the fluid sample during block 80, such as but not
limited to those specific to processing tissue or fluid samples.
Consequently, the methods and the systems described herein are not
necessarily restricted to the aforementioned processes. In any
case, incorporating the aforementioned process steps into system 51
can expand the functionality of process module 6 to perform two
processes: the automation of sample processing and the automation
of assay preparation. Sample processing is the conversion of a raw
sample into a form that is compatible with the desired assay. Assay
preparation takes the converted sample and forms a particle based
assay.
[0064] In general, the first set of magnetic particles referenced
for mixing with the fluid sample in block 80 may be configured to
react with the fluid sample to capture a desired agent upon the
magnetic particles. For example, in some cases, the first set of
magnetic particles may be configured to capture nucleic acid from a
fluid sample. Such a process is illustrated in the nucleic acid
assay flowchart depicted in FIG. 14 and is described in more detail
below. Alternatively, the first set of magnetic particles may be
configured to capture antigens located in a biological sample (such
as tissue or bodily fluid). Such a process is illustrated in the
immunoassay flowchart depicted in FIG. 15 and is described in more
detail below. It is noted that magnetic particles are referenced
herein as reagents and, therefore, may constitute a reagent for
which reagent pack 56 may be configured to store for the
preparation of a fluid assay. More specifically, the term "reagent"
as used herein may generally be referred to herein as a substance
used to prepare a product because of its chemical or biological
activity.
[0065] Subsequent to a predetermined incubation time (which may be
assay-specific) for process described in block 80, the method may
continue to block 81 in which the first set of magnetic particles
are immobilized with a magnetic field. Such a process may include
moving an actuator to which one or more magnets of system 51 is
coupled in proximity to reaction vessel 60. Subsequent thereto, the
method may continue to block 82 in which the fluid is separated
from the first set of magnetic particles. In particular, system 51
may be operated to remove unreacted fluid sample from reaction
vessel 60. In some embodiments, the method may continue mixing
different fluid reagents with the first set of magnetic particles
subsequent to the separation of the magnetic particles from the
fluid sample as shown in block 84. In such cases, after mixing with
the magnetic particles, the method may reiterate the steps of
immobilizing the magnetic particles to separate the different fluid
reagents therefrom. For example, in some cases, a washing solution
may be mixed with the first set of magnetic particles to remove any
unreacted components of the fluid sample previously mixed with the
magnetic particles. In addition or alternatively, other reagents
may be mixed with the first set of magnetic particles to remove
components desirable for analysis, such as for example nucleic acid
for nucleic acid assays. In other embodiments, reagents may be
mixed with the first set of magnetic particles to add components to
the magnetic particles for subsequent analysis, such as
immunoassays, for example.
[0066] In either case, the first set of magnetic particles may, in
some embodiments, be analyzed as shown by the path between blocks
82 and 89. In such cases, the process of block 89 may include
moving the first set of magnetic particles to microfluidic analysis
module 5. In other embodiments, the method may alternatively mix
the solution separated from the first set of magnetic particles
(discussed in reference to block 82) with a second distinct set of
magnetic particles as shown in block 86 of the flowchart depicted
in FIG. 12. For example, in some embodiments, nucleic acid
separated from the first set of magnetic particles in a nucleic
assay (as described in reference to block 82) may be mixed with a
PCR reagent to start a PCR process, which is described in more
detail below in reference to FIG. 14. In such a case, the method
may continue to block 87 in which the fluid is separated from the
second set of magnetic particles, which may include the
immobilization of the second set of magnetic particles and the
removal of the residual fluid. In some cases, the immobilization of
the second set of magnetic particles may be by the same magnet used
to immobilize the first set of magnetic particles. In other
embodiments, however, the second set of magnetic particles may be
immobilized by a different magnet within system 51. Subsequent
thereto, the second set of magnetic particles may be analyzed as
shown by the path between blocks 52 and 89. Procedures for
analyzing the second set of magnetic particles may be generally
within the scope described for analyzing the first set of magnetic
particles.
[0067] As noted above, FIG. 13 illustrates a flowchart of exemplary
steps that may be used to process a fluid sample, either prior to
or subsequent to being introduced into system 51. In particular,
FIG. 13 outlines some determination which may be considered as to
how a fluid sample is processed. For example, the flow chart
includes block 90 in which a determination of whether the collected
sample needs to be concentrated. Examples of embodiments in which a
sample may need to be concentrated is when the sample volume needs
to be reduced and/or the concentration of analyte within the sample
is expected to be too low. FIG. 13 further includes block 92 in
which a determination of whether the collected sample needs to be
filtered. A filtering process may be advantageous for removing
particles which are not of interest or may interfere with the
analysis of the sample. In addition to such processes, FIG. 13
includes block 94 in which a determination of whether the assay to
be prepared needs the cells of the collected sample to be lysed
such that material within a cell can be accessed for analysis. As
described above in reference to FIG. 12, the lysing process may be
performed prior or subsequent to mixing a fluid sample with a set
of magnetic particles. Following the determinations of blocks 90,
92, and 94, the flow chart includes block 96 in which a
determination of what type of assay is to be performed. The
flowchart depicted in FIG. 13 outlines that a nucleic acid assay or
an immunoassay (protein based) may be prepared. Flowcharts
outlining exemplary methods for both types of assays are depicted
in FIGS. 14 and 15, respectively, and are described in more detail
below. It is noted that the methods described in reference to FIGS.
14 and 15 may be performed by any of the system configurations
described herein.
[0068] As shown in block 100 in FIG. 14, preparation of a nucleic
assay may include capturing nucleic acid on to a carrier, such as a
magnetic particle, which is or can be immobilized. Thereafter, the
nucleic acid carrier may be immobilized and the remaining sample
discarded as shown in block 102. In some cases, the nucleic acid
carriers may be washed after discarding the sample. Although such a
process is not depicted in FIG. 14, it is not necessarily omitted
therefrom. In blocks 104 and 106, a determination of whether the
nucleic acid needs to be separated from the carrier is made and, if
applicable, the nucleic acid is separated therefrom. In such cases,
the solution may also be heated to remove the nucleic acid from the
particles and, consequently, system 51 may, in some embodiments,
include auxiliary heaters. The processes for blocks 100, 102, 104,
and 106 may generally be performed by system 51 as described above
in reference to processing in reaction vessel 60. After blocks 104
and 106, the method continues to blocks 108 and 110 in which a
determination of whether a reverse transaction to convert RNA to
DNA needs to be conducted and, if applicable, is performed in block
110.
[0069] Thereafter, a determination of whether real time monitoring
(analysis) is to be performed with DNA amplification as outlined in
block 112. If the determination is to go forward with real time
monitoring, a PCR process is performed with a PCR solution which
may be provided by Luminex Corporation of Austin, Tex. The PCR
process is outlined in block 114 and is formed concurrently with
plurality of steps 116 for amplifying DNA, introducing reporter
tags (e.g., PE) onto the particles, and analyzing the particles. If
a determination is made to forego real time monitoring, the PCR
process is not performed, but plurality of steps 116 are performed
and when the particles are ready for analysis, they are analyzed by
microfluidic analysis module 5. In either case, analysis results
may be displayed on display 2 as shown in block 119. In general,
the aforementioned RNA to DNA reverse transaction process, the PCR
process, and plurality of steps 116 may be performed by system 51
as described above in reference to processing in reaction vessel
60. In the case that system 51 is configured for multiple use
operations, the method may continue to block 118 to reset the fluid
assay preparation system/module (APM) for a new sample.
[0070] FIG. 15 illustrates a flowchart of an exemplary process for
preparing an immunoassay. As shown in FIG. 15, the method may
include block 120 in which a fluid sample is mixed with magnetic
particles having antibodies attached thereto. After an
assay-specific incubation period, the magnetic particles are
immobilized and washed as noted in block 122 and subsequently
additional antibodies are added to the magnetic particles as noted
in block 124. Subsequent thereto, the method continues to block 126
in which the magnetic particles are immobilized and washed again. A
determination as to whether the antibodies need to be tagged is
shown in block 128 followed by the appropriate steps if applicable.
Thereafter, the particles are sent to microfluidic analysis module
5 as shown in block 130. In general, each of the process steps
leading up to block 130 (i.e., blocks 120, 122, 124, 126, and 128)
may be performed by system 51 as described above in reference to
processing in reaction vessel 60. In the case that system 51 is
configured for multiple use operations, the method may include
resetting the fluid assay preparation system/module (APM) for a new
sample after block 130.
[0071] In addition to being used with processing module 6, the
reagent cartridges described in reference to FIGS. 6-10 can also be
used for acquiring a sample. For example, FIG. 16 illustrates a
variant of the reaction cartridge that allows for direct sampling
with the cartridge. The cartridge shown in FIG. 16 is configured to
acquire a sample across blood collection volume 96 by pressing
microneedle array 98 against a patient's skin. Sheath fluid may be
introduced to the reaction vessel through sheath inlet 100, and the
sample may be removed from the reaction vessel through sample
outlet 102. Sheath inlet 100 and sample outlet 102 may have any
suitable configuration known in the art. The reaction cartridge may
also include a removable seal 104, which may be configured as
described herein. The sample flows from the microneedle array into
a holding chamber for extraction by the reagent cartridge receiver,
one embodiment of which is shown in FIG. 17. In particular, FIG. 17
shows the operation of a reaction cartridge with microneedles. In
particular, the microneedle cartridge may be initially sealed as
shown by microcartridge 106. Top seal 108 of the microcartridge is
removed to expose microneedles 110. The microneedle region of the
cartridge is then pressed against the patient's skin. The
microneedle cartridge is resealed after a sample is acquired, as
shown by microcartridge 112. Then, the microneedle cartridge is
placed in receiver module 114 for analysis. Placing the cartridge
into the receiver actuates two needles 116 and 118 that pierce the
cartridge's seals. One needle injects sheath fluid into the
cartridge while the other needle receives the sample and sheath
fluid combined flow. The cartridge shown in FIG. 16 could simply be
a sample taking component that passes the sample onto a reaction
cartridge like those mentioned above or could contain reagents to
process the sample internally.
[0072] It is often the case that reagents used in biological
detection must be refrigerated or frozen when stored. The
embodiments described herein, if used with such reagents, may
include a refrigeration unit onboard portable system 12 for reagent
storage module 4. One embodiment of a reagent storage module is
shown in FIG. 18, which can store and refrigerate reagents and
provide an interlock and indicator system so that used reagents are
not accidentally used more than once. For example, as shown in FIG.
18, the reagent storage module may include detector reagent storage
120, which may have any suitable configuration known in the art. In
FIG. 18, the reagent storage module is shown with cartridges 122
removed (on left) and with cartridges 122 inserted (on right). In
addition, the reagent storage module may include indicator panel
124 that includes one or more indicators for each reaction
cartridge. For example, the indicator panel may include indicator
126 for each reaction cartridge. The indicator may be changed
depending on the status of the reagent cartridges in the reagent
storage module. For example, a red light may indicate a used
cartridge, an unlit indicator may indicate a missing reagent
cartridge, and a green indicator may indicate a new reagent
cartridge. Although the reagent storage module shown in FIG. 18 is
configured for storing a particular number of reaction cartridges,
it is to be understood that the reagent storage module may be
configured to store any suitable number of reaction cartridges.
[0073] The embodiments described herein provide a number of
advantages over other systems configured to perform measurements of
samples. For example, the embodiments described herein are
substantially insensitive to their environments. In addition, the
embodiments described herein are not time consuming to manufacture.
Additionally, the embodiments described herein are relatively
simple to operate and can be used by relatively untrained users.
Furthermore, the embodiments described herein are relatively
inexpensive and are capable of performing the measurements without
requiring significant laboratory resources for pre-processing of
the one or more samples. Moreover, the embodiments described herein
are relatively flexible in design such that a single system can be
used for substantially different applications.
[0074] Further modifications and alternative embodiments of various
aspects of the invention may be apparent to those skilled in the
art in view of this description. Accordingly, this description is
to be construed as illustrative only and is for the purpose of
teaching those skilled in the art the general manner of carrying
out the invention. It is to be understood that the forms of the
invention shown and described herein are to be taken as the
presently preferred embodiments. Elements and materials may be
substituted for those illustrated and described herein, parts and
processes may be reversed, and certain features of the invention
may be utilized independently, all as would be apparent to one
skilled in the art after having the benefit of this description of
the invention. Changes may be made in the elements described herein
without departing from the spirit and scope of the invention as
described in the following claims.
* * * * *