U.S. patent application number 14/793542 was filed with the patent office on 2015-11-12 for method for separating a sample into density specific fractions.
The applicant listed for this patent is MicroAire Surgical Instruments, LLC. Invention is credited to John Raymond Chapman, Philip H. Coelho, Rodney D. Sparks.
Application Number | 20150321203 14/793542 |
Document ID | / |
Family ID | 45723963 |
Filed Date | 2015-11-12 |
United States Patent
Application |
20150321203 |
Kind Code |
A1 |
Chapman; John Raymond ; et
al. |
November 12, 2015 |
Method for Separating a Sample into Density Specific Fractions
Abstract
The centrifugation vessel includes an outer wall containing an
interior space. A dam defines a barrier which divides the interior
space into at least two regions including a catch basin defining a
higher gee region and a reservoir defining a lower gee region.
These regions are joined together over the dam. The dam includes a
face which is preferably tapered to enable optimization of speed of
separation of a sample placed within the vessel. The vessel is
usable in a biological sample processing method by having the
higher gee region of the vessel configured to have an elongate form
and the volume optimized for collection of a higher density
fraction of the sample. Supply and withdrawal tubes extend into the
regions for reliable extraction and separate collection of
differing density fractions after separation by centrifugation.
Inventors: |
Chapman; John Raymond;
(Sacramento, CA) ; Sparks; Rodney D.; (Antelope,
CA) ; Coelho; Philip H.; (Sacramento, CA) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
MicroAire Surgical Instruments, LLC |
Charlottesville |
VA |
US |
|
|
Family ID: |
45723963 |
Appl. No.: |
14/793542 |
Filed: |
July 7, 2015 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
13199119 |
Aug 19, 2011 |
9101926 |
|
|
14793542 |
|
|
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|
61401877 |
Aug 21, 2010 |
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Current U.S.
Class: |
494/37 |
Current CPC
Class: |
B01D 21/262 20130101;
B01L 3/5021 20130101; G01N 33/491 20130101; B04B 1/00 20130101;
B04B 5/02 20130101; B04B 5/0414 20130101; A61M 1/3693 20130101;
B01L 2400/0409 20130101; B01L 2300/0851 20130101 |
International
Class: |
B04B 5/04 20060101
B04B005/04; B01D 21/26 20060101 B01D021/26; B04B 1/00 20060101
B04B001/00 |
Claims
1-20. (canceled)
21. A method for separation of a sample into at least two fractions
of different densities, the method including the steps of:
identifying a centrifuge vessel having: an upper end and a floor
end; an outer wall surrounding a fluid containing interior space of
the vessel, the outer wall extending from the upper end to the
floor end; a barrier inside the outer wall, the barrier partially
dividing the interior space into at least a first region and a
second region, the barrier having a lip with the first region and
the second region connected above the lip and the first region and
the second region spaced apart below the lip, wherein the barrier
in the first region extends tapering diagonally from the lip to the
inner surface of the outer wall at a position between the upper end
and the floor end; placing a sample into the interior space of the
vessel; positioning the vessel into a centrifuge; spinning the
vessel within the centrifuge to separate the sample into differing
density fractions; and stopping said spinning step while keeping
the separated differing density fractions at least partially
divided by the barrier into the first region and the second region
within the centrifuge vessel.
22. The method of claim 21, wherein said identifying a centrifuge
vessel step includes locating the lip of the barrier between a
higher gee side and a lower gee side of the vessel at a particular
fixed position at least partially correlated with expected
prevalence of the at least two fractions of the sample.
23. The method of claim 21, wherein said identifying a centrifuge
vessel step includes the region adjacent a higher gee side of the
vessel having a volume below the lip of the barrier greater than an
amount of a higher density one of the at least two fractions of the
sample, such that the higher density fraction is collected within
the higher gee region after centrifugation.
24. The method of claim 21, wherein said positioning step includes
a cradle having an upper end which is open and into which the
centrifuge vessel is adapted to be removably placed along a cradle
center line, the center line of the cradle oriented substantially
parallel with the spin axis.
25. The method of claim 24, wherein said identifying a centrifuge
vessel step includes the barrier extending down from the lip on a
side of the barrier closest to the spin axis after said positioning
step, having a face extending at an angle tapering toward the spin
axis as the face extends away from the lip.
26. The method of claim 25, wherein said identifying a centrifuge
vessel step includes the face tapering in a curving manner away
from the lip and partially toward the spin axis as the face extends
away from the lip.
27. The method of claim 21, wherein said positioning step includes
a cradle having an open upper end into which the centrifuge vessel
is adapted to be placed along a center line of the cradle, the
center line of the cradle angled non-parallel to the spin axis with
the open upper end of the cradle located closer to the spin axis
than other portions of the cradle.
28. The method of claim 27, wherein said identifying a centrifuge
vessel step includes the barrier having a face extending down from
the lip on a side of the barrier closest to the spin axis, the face
angled to be closer to the spin axis where the face is spaced from
the lip than a distance from the face to the spin axis where the
face is adjacent the lip.
29. The method of claim 28, wherein said identifying a centrifuge
vessel step includes a side of the barrier opposite the face
oriented substantially parallel with portions of the outer wall
most distant from the spin axis for at least a portion of the
barrier after said positioning step.
30. The method of claim 29, wherein said identifying a centrifuge
vessel step includes portions of a side of the barrier opposite the
face tapering at an angle relative to portions of the outer wall of
the vessel most distant from the spin axis after said positioning
step, the angle causing tapering portions of the wall of the
barrier opposite the face to be most distant from the spin axis at
a location most distant from the lip of the barrier.
31. A method for processing a biological sample having at least two
fractions of different densities, the method including the steps
of: identifying a centrifuge with a spin axis and at least one
sample vessel support spaced from the spin axis and adapted to spin
about the spin axis; identifying a vessel for the biological
sample, the vessel sized and shaped to be supported at least
partially by the sample vessel support of the centrifuge; wherein
said identifying a vessel step includes the vessel having: an upper
end and a floor end; an outer wall adapted to contain fluids
therein, the outer wall extending from the upper end to the floor
end; a barrier inside the outer wall, the barrier dividing an
interior of the container into at least a first region and a second
region, a lip defining an upper end of the barrier where the first
region and second region join together, and a pair of surfaces on
the barrier extending down from the lip, wherein one of the
surfaces extends tapering diagonally from the lip to the inner
surface of the outer wall at a position between the upper end and
the floor end; placing a sample into the vessel; locating the
vessel into the vessel support of the centrifuge; spinning the
vessel to separate the sample into fractions; and stopping said
spinning step while keeping the separated fractions at least
partially divided by the barrier into the separate regions within
the centrifuge vessel.
32. The method of claim 31, wherein said positioning step includes
configuring the sample vessel support of the centrifuge as a cradle
sized and shaped to have a portion of the sample vessel placed
therein, and placing the vessel into the cradle.
33. The method of claim 31, wherein said identifying a vessel step
includes providing the barrier in a fixed position with a face
extending down from the lip on a side of the barrier closest to the
spin axis after said locating step, the face tapering toward said
spin axis at least partially as the face extends away from the
lip.
34. The method of claim 33, wherein said identifying a vessel step
includes the face of the barrier being substantially flat.
35. The method of claim 33, wherein said identifying a vessel step
includes the face having a concave contour.
36. The method of claim 33, wherein said identifying a vessel step
includes the barrier having a wall on a side of the barrier
opposite the face which is oriented substantially parallel with a
high gee side of the vessel for at least portions of the wall of
the barrier opposite the face.
37. The method of claim 36, wherein said identifying a vessel step
includes portions of the wall on the side of the barrier opposite
the face which are spaced from the lip exhibiting a taper away from
the outer wall defining the high gee side of the vessel, the taper
at an angle causing portions of the wall having the taper to angle
away from the high gee side of the outer wall and away from the
spin axis of the centrifuge as the taper extends from the lip.
38. The method of claim 31, wherein said identifying a vessel step
includes the barrier dividing the vessel into a reservoir on a
lower gee side of the barrier and a catch basin on a higher gee
side of the vessel after said locating step, a withdrawal tube
extending down into the catch basin; and withdrawing high density
fractions of the biological sample through the withdrawal tube
after said stopping step.
39. The method of claim 38, wherein said identifying a vessel step
includes the withdrawal tube extending to a location within the
catch basin most distant from the lip, the catch basin sized to
have a volume such that a majority of contents of the catch basin
are a higher density fraction of the sample, with the higher
density fractions of the sample collecting within a lower half of
the catch basin.
40. The method of claim 39, wherein said biological sample includes
fractions of at least three different densities with a volume of
the catch basin sized large enough to contain the two higher
density fractions; and first removing a highest density fraction
from the catch basin through the withdrawal tube, and finally
collecting a medium density fraction from the catch basin by
withdrawal from the withdrawal tube.
41. The method of claim 31, wherein the barrier in the second
region extends from the lip to the floor end of the vessel.
42. The method of claim 31, wherein said first region and second
region have different widths.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application claims benefit under Title 35, United
States Code .sctn.119(e) of U.S. Provisional Application No.
61/401,877 filed on Aug. 21, 2010.
FIELD OF THE INVENTION
[0002] The following invention relates to centrifuges and vessels
therefore which are used in processes for separating a sample into
fractions of different densities. More particularly, this invention
relates to centrifuges and centrifuge operation methods which
utilize sample containing vessel geometry to speed the sample
separation process and maintain separation after
centrifugation.
BACKGROUND OF THE INVENTION
[0003] Essentially a centrifuge is an apparatus that separates
particles that are in a fluid. Centrifugation provides a means for
achieving two goals through one approach: particles can be both
concentrated and purified under centrifugal forces. Centrifugation
of particles in a suspending medium causes the particles to
sediment rapidly in the direction outward from the center of
rotation. The centrifugal force generated by centrifugation is
proportional to the speed of rotation and the radius of the rotor.
At a fixed centrifugal force and medium viscosity, the
sedimentation rate of the particle is proportional to the molecular
weight of the particle and the difference between its density and
the density of the medium. There are two types of centrifugation
procedures: one is "preparative" which is used to isolate specific
particles; the other is called "analytical" which is used to
measure the physical properties of sedimenting particles. When a
suspension is rotated at a certain speed or revolutions per minute
(RPM), centrifugal force causes the particles to move radially away
from the axis of rotation.
[0004] Centrifuges are among a select group of laboratory
instruments that are as scalable as they are configurable.
Individuals who have used bench top centrifuges that handle
sub-milliliter volumes may be surprised to learn that centrifuges,
some as large as rooms, are used in industrial processing. The use
of centrifuges has been summarized in the following books, the
entire contents are incorporated herein: Centrifugal Separations in
Biotechnology by Wallace Woon-Fong Leung Academic Press; 1 edition
(Aug. 30, 2007) (by reference and for industrial applications
reviewed in Perry's Chemical Engineers' Handbook 8/E Section
18:Liquid-Solid Operations and Equipment McGraw-Hill Professional
(Aug. 1, 2007); Industrial Centrifugation Technology by Wallace
Woon-Fong Leung (Feb. 1, 1998); Biological Centrifugation (The
Basics) by J. M. Graham (Oct. 15, 2001); Refining iron-contaminated
zinc by filtration and centrifugation by John A. Ruppert (Jan. 1,
1967); Processing by Centrifugation by Liya L. Regel and William R.
Wilcox (Sep. 1, 2001); Centrifugation in Density Gradients by C. A.
Price (October 1982); Decanter Centrifuge Handbook by A. Records
and K Sutherland (Mar. 16, 2001); Bioseparations Science and
Engineering (Topics in Chemical Engineering (Oxford University
Press) by Roger G. Harrison, Paul W. Todd, Scott R. Rudge, and
Demetri Petrides (Oct. 31, 2002).
[0005] Centrifuge designs are simple, consisting of an enclosed
compartment inside which a rotor spins rapidly. Rotors, which can
usually be interchanged, contain equally spaced openings into which
sample tubes are inserted. Samples will either spin at a fixed
angle relative to the rotating axis or "swing out" to perpendicular
under centripetal force as the rotor speed increases. Forces
generated as the rotor spins cause components in the sample to
migrate toward the bottom of the sample tube, according to weight
or density.
[0006] Entry-level mini-centrifuges easily fit on a bench top,
operate at a single, relatively low speed, generate low
gravitational (g) forces, and cost only a few hundred dollars.
"Minis" are used for samples whose components are easily separated
by density. Most medical and veterinary office centrifuges are of
this type. The next level up, compact bench top centrifuges, spin
tubes of up to about 2 mL and create tens of thousands of gs.
Researchers use them to separate DNA, proteins, and cellular
components.
[0007] There are many ways to differentiate centrifuges by type,
speed, and features. Beckman-Coulter (Fullerton, Calif.), for
example, divides its product line into three basic platforms: bench
top devices operating at up to about 10,000 rpm, "washing machine"
centrifuges that provide up to about 100,000 g, and
ultracentrifuges that deliver in excess of one million g. In fact,
one could argue that all centrifuges exist along a continuum of
features that may be mixed and matched, which include g-force
generated, sample tube size, refrigeration capabilities, rotation
angle, computerization, and others. The ultracentrifuge is a
centrifuge optimized for spinning a rotor at very high speeds,
capable of generating acceleration as high as 1,000,000 g (9,800
km/s.sup.2). There are two kinds of ultracentrifuges, the
preparative and the analytical ultracentrifuge. Both classes of
instruments find important uses in molecular biology, biochemistry
and polymer science.
[0008] Common Centrifugation Vocabulary and Formulas. [0009]
Pellet: hard-packed concentration of particles in a tube or rotor
after centrifugation. [0010] Supernatant: The clarified liquid
above the pellet. [0011] Adapter: A device used to fit smaller
tubes or centrifugal devices in the rotor cavities. [0012] RPM:
Revolutions Per Minute (Speed). [0013] R.sub.max: Maximum radius
from the axis of rotation in centimeters. [0014] R.sub.min: Minimum
radius from the axis of rotation in centimeters. [0015] 99999:
Relative centrifugal Force. RCF=11.17.times.Rmax (RPM/1000).sup.2
[0016] K-factor: Pelleting efficiency of a rotor. Smaller the
K-factor, better the pelleting efficiency.
[0016] K = 2.53 .times. 10 11 Ln ( R max / R min ) ( RPM ) 2
##EQU00001## [0017] S-value: the sedimentation coefficient is a
number that gives information about the molecular weight and shape
of the particle. S-value is expressed in Svedberg units. The larger
the S-value, the faster the particle separates.
[0018] The force on the particles (compared to gravity) is called
Relative Centrifugal Force (RCF). For example, an RCF of
500.times.g indicates that the centrifugal force applied is 500
times greater than Earth's gravitational force. Modern day
ultracentrifuges can generate forces in excess of 300,000 times
that of gravity, forces sufficient to overcome the very cohesion of
most molecules (including the metal of the rotor). The force is
usually given as some value times that of gravity (g) and is called
RCF. The centrifugal force is dependent upon the radius of the
rotation of the rotor, the speed at which it rotates, and the
design of the rotor itself (fixed angle, vs swinging bucket). Rotor
speed and design can be held constant, but the radius will vary
from the top of a centrifuge tube to the bottom. If a measurement
for the radius is taken as the mid-point, or as an average radius,
and all forces are mathematically related to gravity, then one
obtains a relative centrifugal force, labeled as .times.g.
Centrifugation procedures are given as .times.g measures, since RPM
and other parameters will vary with the particular instrument and
rotor used. Relative Centrifugal Force is a constant that is
independent of the apparatus used.
[0019] Protocols for centrifugation typically specify the amount of
acceleration to be applied to the sample, rather than specifying a
rotational speed such as revolutions per minute. This distinction
is important because two rotors with different diameters running at
the same rotational speed will subject samples to different
accelerations. During circular motion the acceleration is the
product of the radius and the square of the angular velocity and it
is traditionally named "relative centrifugal force" (RCF). The
acceleration is measured in multiples of "g" (or .times."g"), the
standard acceleration due to gravity at the Earth's surface, and it
is given by
RCF = r ( 2 .pi. N ) 2 g ##EQU00002## [0020] where [0021] g is
earth's gravitational acceleration, [0022] r is the rotational
radius, [0023] N is the rotational speed, measured in revolutions
per unit of time. [0024] This relationship may be written as
[0024] RCF=1.118.times.10.sup.--5r.sub.cmN.sub.RPM.sup.2
where
[0025] r.sub.cm is the rotational radius measured in centimeters
(cm),
[0026] N.sub.RPM is rotational speed measured in revolutions per
minute (RPM).
[0027] In 1851, George Gabriel Stokes derived an expression, now
known as Stokes' law, for the frictional force, also called drag
force, exerted on spherical objects with very small Reynolds
numbers (e.g., very small particles) in a continuous viscous fluid.
Stokes' law is derived by solving the Stokes flow limit for small
Reynolds numbers of the generally unsolvable Navier-Stokes
equations:
F.sub.d=6.pi..mu.RV
where: [0028] F.sub.d is the frictional force acting on the
interface between the fluid and the particle (in N), [0029] .mu. is
the fluid's viscosity (in [kg m.sup.-1 s.sup.-1]), [0030] R is the
radius of the spherical object (in m), and [0031] V is the
particle's velocity (in m/s).
[0032] If the particles are falling in the viscous fluid by their
own weight due to gravity, then a terminal velocity, also known as
the settling velocity, is reached when this frictional force
combined with the buoyant force exactly balance the gravitational
force. The resulting settling velocity (or terminal velocity) is
given by:
V s = 2 9 ( .rho. p - .rho. f ) .mu. gR 2 ##EQU00003##
where: [0033] V.sub.s is the particles' settling velocity (m/s)
(vertically downwards if .sub.p>.sub.f, upwards if
.sub.p<.sub.f), [0034] g is the gravitational acceleration
(m/s.sup.2), [0035] .sub.p is the mass density of the particles
(kg/m.sup.3), and [0036] .sub.f is the mass density of the fluid
(kg/m.sup.3).
[0037] From application of Stoke Law, the following principles are
derived: The sedimentation rate of particles is proportional to
their size; the sedimentation rate is proportional to the density
of the particle and to the medium; the sedimentation rate is null
when both densities are the same; the sedimentation rate diminishes
by increasing the viscosity of the medium, and the sedimentation
rate increases by increasing the force field.
[0038] Separation methods. Centrifugal separations can be separated
into two basic types: differential pelleting and zonal separations.
Differential pelleting is most useful for crude separations of raw
material where purity and yield are not critical. The method
involves sedimenting particles out of solution, and either
retaining the pellet or supernatant depending on where the material
of interest is located. As predicted by the equations above, larger
particles will sediment prior to smaller ones, and more dense
particles prior to less dense ones. In addition, asymmetrical
particles will sediment more slowly than spherical ones of the same
mass and density. The separations are not clean, however, since the
centrifugal force required to pellet large particles from the top
of a sample will also pellet small particles from the bottom. The
greater the difference in sedimentation rate between the particles
being separated, the cleaner the preparation will be.
[0039] Differential centrifugation. In this method, the centrifuge
tube is filled with an uniform fluid mixture. After centrifugation
are obtained two fractions: a pellet that contains the sedimented
material and a supernatant with the material not sedimented. The
method is nonspecific, and it is difficult to assure if the desired
particle will remain in the supernatant, in the pellet or
distributed between both; but is a very useful technique. An
example of the application is the the elimination of prokaryotic
cells in culture broths. Centrifugation of cultures to
10.000.times.g for 20 minutes is enough to create the required
centrifugal force necessary to sediment bacteria cells.
[0040] Protein precipitation with ammonium sulfate. The saline
precipitation is a technique used in the initial steps of enzyme
purification and in some immunoassays. Proteins are surface
polyelectrolytes, when a salt is added to the medium, their ions
neutralize the protein charges, arriving at a situation in which
there aren't net charge, then, proteins flocculate. This technique
requires differential centrifugation: centrifuge to 10,000.times.g
for 60 minutes so that the proteins that are flocculating are
precipitated.
[0041] Thermal treatment. Some proteins are more thermostable than
others which can be used as a method for isolating and
concentrating. The denatured proteins tend to become aggregated and
by using differential centrifugation can be eliminated by their
sedimentation.
[0042] Zonal Separations. There are two types of zonal separations,
both of which rely on density gradients: rate zonal and isopycnic.
Rate-zonal centrifugation separates particles based on differences
in their sedimentation coefficients (s), which is a function of
both particle size and density. In practice, differences in size
dominate the differences in sedimentation velocity (s) among most
biological particles, since the range of densities is not large and
s varies as the square of particle diameter. Isopycnic separations
discriminate among particles based solely on differences in buoyant
density. In both techniques, centrifugation is carried out in a
density gradient, which, among other functions, prevents mixing of
the sample thereby ensuring that separated particles remain
separated.
[0043] For rate zonal separations, a sample is introduced to the
top of a density gradient. When subjected to centrifugal force, the
sample components migrate through the gradient according to their
s. Particles migrate at different speeds, resulting in greater
distance between particles having different s over time. Because
the particles do not come to rest at equilibrium in the gradient,
care must be taken so that the particles of interest do not pellet.
For effective separations, the initial sample volume should be
small (the sample layer should be only a few millimeters thick),
because the sample zone continues to widen over time as a result of
diffusion. Therefore, while rate zonal gradients eliminate problems
associated with pelleting during the purification, a suitable
concentration step that does not result in pelleting or aggregation
must be employed prior to using this technique. Many different
types of density gradient media may be employed for rate zonal
separations. Choosing the appropriate medium requires matching the
properties of the medium to one's specific application. In general,
it is beneficial to employ media preparations of high viscosity for
rate zonal separations because viscous forces will magnify
differences in settling velocity between similar particles.
[0044] In isopycnic (or equilibrium buoyant density) separations,
particles migrate through the density gradient until they reach the
point at which their density is equal to that of the surrounding
medium. Media used for this type of separation must therefore be
able to form a solution that is at least as dense as the particle
that are to be purified. Samples may be top-loaded or bottom-loaded
in preformed density gradients, or homogeneously mixed with a
self-forming gradient medium before centrifugation. As particles
approach their equilibrium position in a gradient, the difference
in density between the particle and the medium decreases and,
consequently, so does the migration rate of the particle. Particles
become increasingly focused over time until the focusing force is
balanced by diffusion. Achieving equilibrium, at which point the
particles are most focused, can require long centrifugation runs
under high g-forces. This method eliminates pelleting and
aggregation concentrated and purified target particle preparations
at the same time. Isopycnic separations also provide a means for
directly determining buoyant density, a commonly reported
physico-chemical property of materials.
[0045] Because the two zonal techniques described above separate
based on partially independent properties (size versus density),
they can be used sequentially to separate particles that may not be
separable by either method alone. Two-dimensional separations have
been particularly valuable for biological particulate purification,
since most biological particulates have a combination of
sedimentation coefficient and buoyant density that distinguishes
them from other fluid constituents.
[0046] Density gradient centrifugation. Density gradient
centrifugation is a popular method for fractionation of nucleic
acids, virus particles and proteins. This is done by centrifugation
of a mixture of particles or components in a density gradient
column. Particles or components with different densities will be
separated at different positions in the density gradient column.
Basically, there are two types of density gradient centrifugation,
termed rate zonal and isopycnic. Preparation of density gradients.
In either zonal or isopycnic density gradient centrifugation, a
density gradient has to be prepared prior to centrifugation by
either a hand-layering process or by employing a density gradient
former. A number of materials such as sucrose, Ficoll, or salts
such as NaCl, NaBr, or CsCl, can be used for preparation of the
density gradient. A sucrose density gradient can be prepared by
pipetting into a centrifuge tube layers of progressively lower
concentrations of sucrose on top of higher concentrations. Density
gradient columns can also be prepared by the use of a syringe with
a piece of tubing attached to the syringe needle (20-22 gauge). To
prepare a 5-20% sucrose density gradient in a 15 ml tube, start by
placing 3 ml of 5% sucrose in the tube and then carefully inject
the 3 ml of 10% sucrose into the tube by keeping the tip of the
syringe tubing at the bottom of the centrifuge tube. Repeat the
process with 3 ml of 15% and 3 ml of 20% sucrose. When the
preparation is completed, remove the syringe tubing carefully by
holding the tip of tubing against the wall of the centrifuge tube.
Ficoll and cesium chloride density gradients can be prepared in a
similar manner. Density gradients thus prepared can either be used
immediately as a step gradient or made into a linear gradient by
allowing it to diffuse in a refrigerator overnight.
[0047] Rate Zonal Density Gradient Centrifugation. In rate zonal
density gradient centrifugation, a sample solution containing
particles to be fractionated is layered on top of the density
gradient column. Under centrifugation the particles will start to
sediment through the density gradient into separate zones. Each
zone consists of particles with the same sedimentation rate. In the
rate zonal centrifugation, centrifugation must be terminated before
any of the separated zones reach the bottom of the tube, since the
density of some zones may be higher than the highest density area
in the density gradient.
[0048] Isopycnic (="same density") density gradient centrifugation.
In isopycnic density gradient centrifugation, the density gradient
column encompasses the whole range of densities of sample
particles. Each particle will sediment only to the position in the
gradient where the density in the gradient column equals its own
density, and the particle will remain at this position. In the
isopycnic method, it is not always convenient to form a gradient
artificially and layer the sample on top of the gradient column. It
is sometimes necessary to start with a uniformly-mixed solution of
gradient material and sample. During centrifugation, gradient
material redistributes in the tube and forms a linear density
gradient. At the same time, sample particles which are initially
distributed throughout the tube either sediment or float to their
isopycnic positions. This type of procedure is termed the
self-generating gradient technique.
[0049] Historically, self-generating isopycnic density gradient
centrifugation have generally required long hours of
centrifugation. For example, isopycnic "banding" of DNA can take
36-48 hours in a self-generating cesium chloride density gradient
using standard swinging-bucket or fixed-angle ultracentrifuge
rotors. The running time cannot be shortened by increasing the
rotor speed, since this only results in changing the positions of
zones in the tube due to the redistribution of gradient material
further down the tube. Run times can be decreased by shortening the
distance over which the gradient forms, however. A recent
innovation to decrease running times for DNA preparation (down to
3-4 hours) has been the use of "vertical" or "near-vertical"
rotors, in which the gradient forms across the diameter, rather
than the length of the tube.
[0050] Separated zones ("bands") from both rate zonal and isopycnic
density gradient centrifugation can be removed by: (i) puncturing a
hole on the bottom of the tube and collecting the fractions or
drops either manually or using a fraction collector, (ii) removing
successive zones from the top of the unpunctured tube, or (iii)
puncturing the tube through the side to recover a band as a single
fraction.
[0051] Application of Density Gradient Centrifugation. Density
gradient centrifugation has been used extensively in separation and
purification of a wide variety of biological materials. It is
particularly well suited for the study of viruses and nucleic
acids. Cells and sub-cellular components such as bacteria,
nucleoids, ribosomes, membranes, etc. have been isolated and
purified with this technique.
[0052] Numerous investigators have identified the criteria for
choosing density gradient media for biological separations (Cline
and Ryel 1971; Hinton et al. 1974). In summary, the criteria are as
follows: The media should be inert or at least nontoxic to the
specimen (minimal osmotic effect, ionic strength, and neutral pH);
the media should form a solution covering the density range for the
particular application, and be stable in solution; the physical and
chemical properties of the media should be known, and it be
possible to use one or more properties to determine the precise
concentration of the media; the solution should not interfere with
monitoring of zones of fractionated material within the gradient;
it should be easy to separate the sample from gradient material
without loss of the sample or its activity; and the gradient media
should be available as a pure compound; and be relatively
inexpensive.
[0053] Ionic media. Alkali metal salts, such as cesium chloride,
are most widely used for making isopycnic gradients with any
standard technique including preformed or self-forming gradients.
Metal salts can provide some of the densest preparations available,
have a low viscosity, and their concentration in solution is easily
measured by refractive index. The major drawbacks of alkali metals
lie in their effects on biological activity; salt solutions have
high ionic strengths, which disrupt protein-protein and nucleic
acid-protein bonds, and have high osmolarities, affecting particle
hydration.
[0054] Small hydrophilic organic molecules (sucrose, glycerol,
sorbitol, etc.) that non-ionic media. Sucrose meets most of the
criteria of an ideal medium for rate zonal separations, being
biologically inert, stable, and relatively cheap. Due to its
popularity as such, sucrose is very well characterized with respect
to concentration, viscosity, density, and refractive index, making
it easy to develop and adapt methods for uncharacterized
particulates. While sucrose has little effect on intermolecular
bonding and is non-ionic, high osmotic pressure may cause shrinkage
in enveloped viruses and thereby affect infectivity in sensitive
viruses. The high viscosity of sucrose at concentrations useful for
virus separations may aid in separation between similarly sized
particles under rate zonal conditions, but the high viscosity and
relatively low density limits the application of sucrose and other
small organic molecules in isopycnic separations of viruses. Other
sugars, notably glycerol and sorbitol, have also been used
effectively as rate zonal media. These gradients need to be
preformed as solutions of small organic molecules do not generally
form gradients when centrifuged.
[0055] High molecular-weight organics (Ficoll, dextran, glycogen,
etc.). High molecular-weight polysaccharides do not penetrate
intact biological membranes and have a lower osmolarity than
solutions of monosaccharides. Therefore, these media may be
especially useful when employed with biological particles.
Unfortunately, due to the size of these polysaccharides, they
cannot be removed from the sample by dialysis or ultrafiltration,
so dilution and high-speed centrifugation are generally required,
which are contraindicated with sensitive specimens as discussed
above. Since polysaccharide media such as Ficoll (GE Healthcare)
and dextran diffuse slowly, it is necessary to preform linear
gradients using gradient mixers. This characteristic also ensures
that gradients are quite stable once formed. The high viscosity of
these media necessitates longer spin times than those of sucrose
gradients.
[0056] Colloidal Silica (Percoll, Ludox, etc.). Colloidal silica
suspensions such as Percoll (GE Healthcare) and Ludox (DuPont) are
truly non-ionic media that can be used to rapidly generate
self-forming gradients. These media are well characterized,
permitting the use of refractive index for examining density
profiles of gradients since absorption prohibits monitoring by UV
light. Percoll density marker bead kits, available from a number of
vendors (e.g., Sigma-Aldrich, product DMB-10), are useful for
visually monitoring gradient profiles. Whereas colloidal media
cannot be effectively filter sterilized, they may be autoclaved
before being adjusted for osmolarity and can be used over a wide pH
range (5.5-10 for Percoll). Percoll is commonly used for cell
separations, because the suspension of colloidal silica can be
prepared in almost any buffer required to maintain cell viability.
Another limitation is that the silica particles may begin to pellet
before smaller viruses have time to form discrete, purified bands.
To remove Percoll from virus purifications requires dilution and
high-speed differential centrifugation (i.e., 100,000 g for 2 h in
a swinging bucket or 1.5 h in an angled rotor), which may lead to
aggregation and deactivation of viruses, as previously
discussed.
[0057] Iodinated organic compounds (Nycodenz, OptiPrep, and
metrizamide). Iodinated compounds provide an excellent combination
of biological inertness, a wide density range, and low viscosity,
which allows for reduced spin times. These compounds, including
Nycodenz (Axis-Shield), iodixanol (sold asOptiPrep by Axis-Shield),
and metrizamide, are heat stable, autoclavable, and of minimal
ionic strength.
[0058] In U.S. Pat. No. 5,605,529 entitled "HIGH EFFICIENCY
CENTRIFUGE ROTOR" issued on Feb. 25, 1997 to Petithory, the entire
contents are incorporated herein by reference, disclosed about the
uses of fixed angular rotors in centrifuges. The field of the
Petithory invention was relating generally to centrifuge rotors,
and more particularly to fixed angle centrifuge rotors.
[0059] Most blood chemistry tests require preparation of serum or
plasma prior to analysis. To this end, red blood cells and other
cellular material are separated from the patient's blood following
collection. Typically, blood is collected in evacuated tubes and
centrifuged at 2000-3000 rpm for 10-20 15 minutes.
[0060] One type of centrifuge rotor which houses tubes for
centrifugation is a fixed angle rotor, in which the tubes are
retained in cavities angled relative to the axis of rotation. The
dynamics of fixed angle rotors and their ability to enhance the
speed of centrifugation are known in the art. The clearing
efficiency (K-factor) of fixed angle rotors, which corresponds to
the time required to sediment a specific particle in a known medium
at a given speed of rotation, can be calculated using the following
formula:
K - factor = 2.53 .times. 10 11 .times. Ln ( r 1 r 2 ) N 2
##EQU00004##
where r.sub.1=radius, in cm, from the outermost point of liquid in
the tube to the central axis of rotation, r.sub.2 radius, in cm,
from the center of the top of liquid within the tube to the central
axis of rotation and N=rpm.
[0061] It is apparent from the above formula that a rotor having
tube cavities inclined at a steep angle (approaching 0.degree. in
reference to the axis of rotation) can provide the lowest K-factor,
and the greatest separation efficiency. However, there are
drawbacks associated with using a rotor having steeply angled tube
cavities including the fact that the steeper the angle, the greater
the tendency of particles to adhere to the outermost wall of the
tube, which could lead to contamination of the supernatant.
[0062] Another drawback is that the sedimentation boundary formed
in a fixed angle rotor centrifuge device is significantly larger
than the sedimentation boundary formed in centrifuges using a
swing-out style rotor.
[0063] Another disadvantage of a steeply angled rotor occurs when
gel barrier tubes are used. The position of the gel band along the
top side-wall of the processed tube makes it difficult to pipette
the supernatant plasma or serum without coming into contact with
the gel material. This is especially important in analyzers which
employ primary tube sampling capability. Since the thickness of the
gel band decreases with the relative steepness of the tube angle,
the band can collapse upon deceleration and cause contamination of
the supernatant with the particles in the gel.
[0064] Still another disadvantage is that there exists a "mixing
effect" during reorientation of the tubes from the horizontal
position to the vertical position during deceleration, which also
increases with the steepness of the tubes within the rotor. During
sedimentation, particles travel outward from the axis of rotation
until they hit the wall of the tube, then slide downward along the
tube wall. This descending layer of increased particle
concentration combined with a corresponding ascending layer of
reduced concentration fluid creates a fluid flow within the tube
which increases the time required to sediment particles,
particularly those of low density or irregular shape.
[0065] A final disadvantage of using steeply angled tube cavity
rotors is that as the steepness of the tube increases, the capacity
of the tube decreases. Since the closure of these tubes can trap
particles, there is a limit to the tube angle that can be used
during centrifugation.
[0066] Advances in the speed of test instrumentation have created a
demand for faster blood separation methods, and particularly for
high speed separation of the blood or serum within the original
blood collection tube while maintaining a minimal distortion of the
separation boundary within the sample containers.
[0067] Centrifuges are suited and used for the separation of
components including cells, organelles or macromolecules contained
in biologic fluids including bone marrow, peripheral blood, urine,
phlegm, synovial semen, milk, saliva, mucus, sputum, exudates,
cerebrospinal fluid, amniotic fluid, cord blood, intestinal fluid,
cell suspensions, tissue digests, tumor cell containing cell
suspensions, microbe containing cell suspensions, radiolabelled
cell suspensions and cell culture fluid for therapeutic or
diagnostic purposes. Centrifuges are well suited for the washing of
cell suspensions and other particulate matter. Centrifuges also are
used for separation of components present in aqueous solutions,
lake water, ocean water, river water, waste water, and sewage for
the purpose of preparative analytical testing or purification.
Centrifuges are also suited for the separation of a component of an
inorganic or organic chemical reaction that has resulted in the
formation of a precipitate or flocculent. Centrifuges have
occasionally been used for separation of particulates added to an
aqueous solution for the purpose of inducing a chemical reaction
and then terminating said chemical reaction by centrifugation of
the heterogeneous fluid using the apparatus of the invention.
Centrifuges have been used to in combination with density particles
to perform immunoaffinity cell separation steps. This expansive
list is still not inclusive for all the varied functions for which
centrifuges are routinely employed and known in the prior art.
Below are detailed examples of some of these applications.
[0068] Charlton et al. were awarded U.S. Pat. No. 4,106,907 on Aug.
15, 1978 entitled "Centrifuge Tube and Method for Performing Assay
with Same", for which the entire contents are incorporated herein
by reference for the purpose of handling radioactive material.
[0069] Kimura was awarded U.S. Pat. No. 4,861,477 on Aug. 29, 1989
entitled "Tubular Container for Centrifugal Separation" for which
the entire contents are incorporated herein by reference. A tubular
container for centrifugal separation suited for easy separation of
a relatively small amount of the phase having an intermediate
specific gravity from the heaviest and lightest phases. The
container has a first section defining a bottom chamber of a
certain volume for containing therein the heaviest phase, a second
section contiguous to the first section and defining an
intermediate chamber for containing therein the phase having the
intermediate specific gravity, and a third section contiguous to
the second section and defining an upper chamber for containing
therein the lightest phase. The diameter of said second section is
smaller than the diameters of the first and third sections.
[0070] Saunders et al. was awarded U.S. Pat. No. 5,422,018 on Jun.
6, 1995 entitled "Centrifuge Tube and Adaptor" for which the entire
contents are incorporated herein by reference. Saunder's discloses
a centrifuge tube and adaptor apparatus is provided which
facilitates separation of biological materials and permits easy
extraction of a fraction after centrifugation. The tube is a
deformable tube with a wide upper chamber and a narrowed lower
portion. The tube is supported within the centrifuge rotor or
within another container within the centrifuge by a liquid support
medium, which surrounds and supports the narrow portion of the
tube, and thus prevents the tube from collapsing during high speed
centrifugations.
[0071] Muller was awarded U.S. Pat. No. 5,260,032 on Nov. 9, 1993
entitled "Integral Centrifuge Tube and Specimen Slide" for which
the entire contents are incorporated herein by reference. Muller's
device was made for use in a centrifuge to automatically prepare
microscope slide specimens from samples of body fluids. A
centrifuge tube and specimen slide are formed integrally in a
unitary device. A lens clearance section is provided as a planar
surface to avoid interference between the device and the rotatable
lenses of a turret microscope while the device is in viewing
position on the microscope stage. The device is constructed to
minimize packing of sediment and other constituent elements of the
sample at the entrance to the slide member and is so configured as
to admit of a step during the centrifuge process which flexes the
slide member to enhance the distribution of cells deposited
therein.
[0072] Levine et al. were awarded U.S. Pat. No. 5,342,790 on Aug.
30, 1994 entitled "Apparatus for Indirect Fluorescent Assay of
Blood Samples" for which the entire contents are incorporated
herein by reference. Levine discloses that a patient's health is
diagnosed by centrifuging blood samples in a transparent tube,
which tube contains one or more groups of particles such as
lyposomes or plastic beads of different densities for each group.
Each group of density-defined particles carries antigens or
antibodies which are specific to a complement antigen or antibody
which may be in the blood sample being tested, and which are
indicative of the patient's health. A label tagged antibody which
is specific to all bound antibody/antigen couples is added to the
blood sample so as to form labeled antibody+antigen-antibody
complexes (AAAC) in the blood sample. Upon centrifugation, the
complexed particles will settle out in different areas in the tube
according to the respective density of the particles, and the
degree of label emission of the particle layers can enable
qualitative or quantitative analyses of the blood sample to be
made. Unbound labeled antibodies will be washed away from the
complexed layers by the washing action of the descending blood
cells during the centrifugation step. Unbound labeled antibodies
will thus not interfere with the analysis.
[0073] Gerken was awarded U.S. Pat. No. 4,713,219 on Dec. 15, 1987
entitled "Plastic Reaction Vessel" for which the entire contents
are incorporated herein by reference. Gerken describes a plastic
reaction vessel for holding a small quantity of liquid comprises a
vessel body which has a body flange (4) surrounding an opening
formed in the body, a cover, and a connecting strip (5) which is
integral with the vessel body and the cover. Opposite to the
connecting strip (5), the body flange (4) has a downwardly facing
abutment surface (25), which is engageable by a hooklike extension
(23), which is formed on the cover (6) and extends downwardly when
the cover is closed. The connecting strip (5) comprises a hinge
portion (12) between its opposite end portions. The cover comprise
a cylindrical skirt, which is adapted to be inserted into the
vessel body through the opening therein. A sealing lip (8) is
provided on the outside of said skirt at that end thereof which is
adapted to be inserted into the opening of the vessel body. The
cover (6) has an outwardly protruding rim (16), from which a
depending flange extends, which contacts the body flange so that a
parallel guidance of the cover (6) is effected in conjunction with
the hinge portion of the connecting strip. An alignment of the
cover (6) is effected by the sealing lip (8), which is formed on
the cylindrical skirt and in sealing contact with the inside
surface of the vessel body.
[0074] According to Kaiser (U.S. Published Patent Application No.
2004/0038316 A1) the improved methods of separating cells have had
a great utility in the many medical and biological fields that
require purified populations. Many biological techniques such as
are employed in biotechnology, microbiology, clinical diagnostics
and treatment, in vitro fertilization, hematology and pathology,
require such processes as identification, separation, culturing, or
manipulation of a target cell or particle, e.g. cell subsets,
platelets, bacteria, virus particles, etc. Cell separation is a
rapidly growing area of biomedical and clinical development.
Improved methods of separating a desired cell subset from a complex
population permit the study and use of cells that have relatively
uniform and denned characteristics. Cell separation is widely used
in research, e.g. to determine the effect of a drug or treatment on
a targeted cell population; investigation of biological pathways;
isolation of transformed or otherwise modified cell populations;
etc. Present clinical uses include the isolation of hematopoietic
stem cells for reconstitution of blood cells, particularly in
combination with ablative chemo and radiation therapy.
[0075] The disclosure of an invention in U.S. Published Patent
Application No. 2004/0182795, by Randel Dorian and Richard Storrs,
the entire contents of which are hereby incorporated herein by
reference incorporated herein by reference., teaches an apparatus
and methods for separation and concentration of plasma and plasma
platelet mixtures from plasma erythrocyte mixtures such as whole
blood and is particularly applicable to the preparation and use of
autologous plasma concentrates.
[0076] Rapid fractionation of blood into erythrocyte, plasma or
plasma-platelet fractions is desirable for the preparation of
autologous concentrates from blood obtained from a patient during
surgery. Each fraction can be modified or returned to the blood
donor. Useful plasma fractions, with our without platelets, have
value as sealants when concentrated without precipitation of
fibrinogen, that is, when concentrated by removal of water
therefrom in accordance with this invention. This invention has
particular value for rapidly preparing autologous concentrated
plasma fractions to help or speed healing, or as a hemostatic agent
or tissue sealant.
[0077] Background of the Invention of U.S. Published Patent
Application No. 2004/0182795, by Randel Dorian and Richard Storrs,
the entire contents of which are hereby incorporated herein by
reference: Blood may be fractionated and the different fractions of
the blood used for different medical needs. For instance, anemia
(low erythrocyte levels) may be treated with infusions of
erythrocytes. Thrombocytopenia (low thrombocyte (platelet) levels)
may be treated with infusions of platelet concentrate.
[0078] Under the influence of gravity or centrifugal force, blood
spontaneously sediments into layers. At equilibrium the top,
low-density layer is a straw-colored clear fluid called plasma.
Plasma is a water solution of salts, metabolites, peptides, and
many proteins ranging from small (insulin) to very large
(complement components). Plasma per se has limited use in medicine
but may be further fractionated to yield proteins used, for
instance, to treat hemophilia (factor VIII) or as a hemostatic
agent (fibrinogen).
[0079] Following sedimentation, the bottom, high-density layer is a
deep red viscous fluid comprising anuclear red blood cells
(erythrocytes) specialized for oxygen transport. The red color is
imparted by a high concentration of chelated iron or heme that is
responsible for the erythrocytes high specific gravity. Packed
erythrocytes, matched for blood type, are useful for treatment of
anemia caused by, e.g., bleeding. The relative volume of whole
blood that consists of erythrocytes is called the hematocrit, and
in normal human beings can range from about 38% to about 54%.
[0080] Depending upon the time and speed of the centrifugation, an
intermediate layer can be formed which is the smallest, appearing
as a thin white band on top the erythrocyte layer and below the
plasma; it is called the buffy coat. The buffy coat itself
generally has two major components, nucleated leukocytes (white
blood cells) and anuclear smaller bodies called platelets
(thrombocytes).
[0081] Leukocytes confer immunity and contribute to debris
scavenging. Platelets seal ruptures in the blood vessels to stop
bleeding and deliver growth and wound healing factors to the wound
site. If the centrifugation is of short duration, the platelets can
remain suspended in the plasma layer.
[0082] The sedimentation of the various blood cells and plasma is
based on the different specific gravity of the cells and the
viscosity of the medium. This may be accelerated by centrifugation
according approximately to the Svedberg equation:
V((2/9).omega..sup.2R(d.sub.cells-d.sub.plasma)r.sup.2)/.eta..sub.t
where [0083] V=sedimentation velocity, [00111]m=angular velocity of
rotation, [0084] R=radial distance of the blood cells to the center
of the rotor, [0085] d=specific gravity, [0086] r=radius of the
blood cells, and [0087] .eta.t=viscosity of the medium at a
temperature of t.degree. C.
[0088] When sedimented to equilibrium, the component with the
highest specific gravity (density) eventually sediments to the
bottom, and the lightest rises to the top. The rate at which the
components sediment is governed roughly by the Svedberg equation;
the sedimentation rate is proportional to the square of the size of
the component. In other words, at first larger components such as
white cells sediment much faster than smaller components such as
platelets; but eventually the layering of components is dominated
by density.
[0089] Soft Spin Centrifugation
[0090] When whole blood is centrifuged at a low speed (up to 1,000
g) for a short time (two to four minutes), white cells sediment
faster than red cells; and both sediment much faster than platelets
(according to the Svedberg equation shown above). At higher speeds
the same distribution is obtained in a shorter time. This produces
layers of blood components that are not cleanly separated and
consist of (1) plasma containing the majority of the suspended
platelets and a minor amount of white cells and red cells, and (2)
below that a thick layer of red cells mixed with the majority of
the white cells and some platelets. The method of harvesting
platelet-rich plasma (PRP) from whole blood is based on this
principle. The term "platelet-rich" is used for this component
because most of the platelets in the whole blood are in the plasma
following slow centrifugation so the relative concentration of
platelets in the plasma has increased.
[0091] Centrifugal sedimentation that takes the fractionation only
as far as separation into packed erythrocytes and PRP is called a
"soft spin." "Soft spin" is used herein to describe centrifugation
conditions under which erythrocytes are sedimented but platelets
remain in suspension. "Hard spin" is used herein to describe
centrifugation conditions under which platelets sediment in a layer
immediately above the layer of erythrocytes.
[0092] Two Spin Platelet Separation
[0093] Following a soft spin, the PRP can removed to a separate
container from the erythrocyte layer, and in a second
centrifugation step, the PRP may be fractioned into platelet-poor
plasma (PPP) and platelet concentrate (PC). In the second spin the
platelets are usually centrifuged to a pellet to be re-suspended
later in a small amount of plasma or other additive solution
[0094] In the most common method for PRP preparation, the
centrifugation of whole blood for 2 to 4 min at 1,000 g to 2,500 g
results in PRP containing the majority of the platelets. After the
centrifugation of a unit (450 ml) of whole blood in a 3-bag system
the PRP is transferred to an empty satellite bag and next given a
hard spin to sediment the platelets and yield substantially
cell-free plasma. This is termed "two-spin" platelet
separation.
[0095] To recover the platelets following two-spin separation, most
of the platelet poor plasma (PPP) is removed except for about 50 ml
and the pellet of platelets is loosened and mixed with this
supernatant. Optionally one can remove about all plasma and
reconstitute with additive solution. To allow aggregated platelets
to recover the mixture is given a rest of one to two hours before
platelets are again resuspended and then stored on an agitator.
[0096] It is believed that two-spin centrifugation can damage the
platelets by sedimenting the platelets against a solid,
non-physiological surface. The packing onto such a surface induces
partial activation and may cause physiological damage, producing
"distressed" platelets which partially disintegrate upon
resuspension.
[0097] Hard Spin Centrifugation
[0098] If the centrifugation is continued at a low speed the white
cells will sediment on top of the red cells whereas the platelets
will remain suspended in the plasma. Only after extended low speed
centrifugation will the platelets also sediment on top of the red
cells.
[0099] Experiments with a blood processor have shown that
centrifugation at a high speed (2,000 g-3,000 g) produces a similar
pattern of cell separation in a shorter time. Initially the cells
separate according to size, i.e., white cells sediment faster than
red cells and platelets remain in the plasma. Soon the red cells
get `packed` on each other squeezing out plasma and white cells.
Because of their lower density, white cells and platelets are
pushed upwards to the interface of red cells and plasma whereas the
platelets in the upper plasma layer will sediment on top of this
interface, provided the centrifugal force is sufficiently high and
sedimentation time is sufficiently long. Plasma, platelets, white
cells and red cells will finally be layered according to their
density. Platelets sedimented atop a layer of red cells are less
activated than those isolated by the "two spin" technique.
[0100] Leukoreduction
[0101] The PC's resulting from both two spin processing and
apheresis methods contain donor leukocytes. In apheresis,
centrifugal blood processing is a growing field, per-processing
bowl and to pick up various centrifugally permitting the continuous
removal of blood from a patient, separated components of the
material during centrifugation then administration of the depleted
blood back to the patient (U.S. Pat. No. 4,389,206, the entire
contents of which are hereby incorporated herein by reference). The
white cells negatively affect platelet storage and may induce
adverse effects after transfusion due to cytokine formation.
Removal of leukocytes (leukoreduction) from PRP and PC is important
because non-self leukocytes (allogeneic leukocytes) and the
cytokines they produce can cause a violent reaction by the
recipient's leukocytes. In 1999 the FDA Blood Product Advisory
Committee recommended routine leukoreduction of all non-leukocytes
components in the US (Holme 2000). Therefore, much of the prior art
focuses on leukoreduction of platelet concentrates because
non-autologous leukocytes excite deleterious immune reactions.
Since the process of this invention provides a convenient way to
quickly harvest autologous platelets from the patient's blood,
immune reactions are not a risk, and the presence of leukocytes is
of little or no concern.
[0102] Plasma concentrates and their utility in hemostasis and
wound healing have been described in U.S. Pat. No. 5,585,007.
Plasma concentrates can be made in a two-step method, first
separating of plasma from the majority of erythrocytes and then
concentrating the plasma by removing water. The plasma can be
separated from the erythrocytes by centrifugation. The water can be
removed from the plasma using a semipermeable membrane or by
contact with a desiccated hydrogel bead. The membrane and hydrogel
bead pores allow passage of water, salts and other low molecular
weight components while blocking passage of cells, platelets
(thrombocytes), cell fragments and larger molecules such as
fibrinogen. The passage of water and low molecular weight
components through the membrane or into the bead concentrates the
plasma, the cells and high molecular weight components contained
therein. The dry hydrogel beads can be dextranomer or
polyacrylamide.
[0103] Recent publications report that platelet preparations
enhance the healing rate of hard and soft tissue defects. Activated
cytokine proteins, released from activated platelets, signal the
migration, proliferation and activation of monocyte cells. Monocyte
cells sense a gradient of cytokines and migrate towards the
source.
[0104] Fibers of polymerized fibrin form pathways by which monocyte
cells translocate into the wound. Translocation is enhanced by
tension on these fibers imparted by the action of platelet
microtubules during clot retraction. Therefore, in situ
polymerization of platelet-containing fibrinogen solutions provides
an enhanced setting for wound healing. Platelet-plasma concentrates
provide enhanced signals and pathways for wound healing cell
migration.
[0105] Platelets have a limited half-time in vivo, and platelet
activity declines rapidly ex vivo. An optimal wound healing
compound therefore would contain freshly isolated platelets. To
minimize risk of disease transmission and maximize beneficial
patient response to platelet activity the platelet/plasma
concentrate would preferably be prepared from the patient's own
blood, i.e. autologously. The amount of blood withdrawn from the
patient should be as small as possible to minimize morbidity caused
by blood loss.
[0106] The invention of U.S. Patent Application Publication No.
2004/0182795 by Randel Dorian and Richard Storrs provides methods
and apparatus for rapidly separating patient plasma from whole
blood, contacting said plasma with dry hydrogel beads,
concentrating said plasma, and separating the resulting plasma
concentrate from the beads for application to patient wounds.
[0107] Dorian's invention relates to a device for preparing plasma
concentrate from plasma containing cells (plasma cell mixture)
comprising a centrifugal separation chamber having a plasma-cell
mixture inlet port and a centrifugal separation chamber outlet
port. The concentrating chamber has an inlet port and a concentrate
outlet, the inlet port communicating with the centrifugal
separation chamber outlet port, the concentrating chamber
containing hydrogel beads and at least one inert agitator. The
device also includes a concentrate chamber having an inlet
communicating with the concentrate outlet through a filter, the
concentrate chamber having a plasma concentrate outlet port. A
plunger can be positioned in the concentrating chamber. The
concentrating chamber has an inner concentrating chamber wall, the
plunger having an outer edge surface conforming to a surface of the
inner concentrating chamber wall; and the hydrogel beads and
agitator can be positioned in the concentrating chamber between the
plunger and the filter. The outer edge surface of the piston can
form a sealing engagement with the surface of the inner
concentrating chamber wall.
[0108] In one embodiment, the centrifugal separation chamber has an
erythrocyte-plasma interface level, and the centrifugal chamber
outlet port is positioned above the erythrocyte-plasma interface
level. The concentrating chamber can have an unconcentrated
plasma-air interface level, the centrifugal separation chamber
outlet port and the concentrating chamber inlet port form an open
passageway for flow of plasma, and the concentrating chamber inlet
port is positioned at a level above said plasma-air interface
level. Alternatively, the centrifugal separation chamber can have a
one-way valve permitting flow of plasma from the centrifugal
separation chamber into the concentrating chamber. In these
embodiments, the agitator can be a dense object such as a smooth
ball which can be a stainless steel. The filter can be a porous
frit.
[0109] The term "plasma concentrate" is defined to include both
plasma concentrate with platelets and plasma concentrate without
platelets.
[0110] A method of Dorian's invention for producing plasma
concentrate from plasma containing erythrocytes and platelets can
comprise the steps of (a) centrifugally separating a plasma-cell
mixture to form an erythrocyte-rich layer and a plasma layer; (b)
moving the plasma from the plasma layer into a concentrating
chamber containing hydrogel beads and an agitator to form a
hydrogel bead-plasma mixture; (c) causing the agitator to stir the
hydrogel bead-plasma mixture, minimizing gel polarization and
facilitating absorption of water by the beads from the plasma,
until a hydrogel bead-plasma concentrate is formed; and (d)
separating plasma concentrate from the hydrogel beads from the
hydrogel bead-plasma concentrate by passing the plasma concentrate
through a filter. The hydrogel beads can have the effective
absorption capacity to remove at least 10 percent of the water from
the plasma, at least 25 percent of the water from the plasma, or at
least 50 percent of the water from the plasma. The plasma
containing erythrocytes and platelets can be whole blood.
[0111] Dorian's invention can be a method for producing plasma
concentrate with a plasma concentrating device comprising a
centrifugal separation chamber having a plasma-cell mixture inlet
port and an centrifugal separation chamber outlet port; a
concentrating chamber having a inlet port and a concentrate outlet,
the inlet port communicating with the centrifugal separation
chamber outlet port, the concentrating chamber containing hydrogel
beads and at least one inert agitator; and a concentrate chamber
having an inlet communicating with the concentrating outlet through
a filter, the concentrate chamber having a plasma concentrate
outlet port. With this device, the method can comprise (a)
centrifuging a plasma-cell mixture in the centrifugal separation
chamber to form an erythrocyte-rich layer and a plasma layer; (b)
moving the plasma from the plasma layer through the separation
chamber outlet port through the inlet port of the concentrating
chamber to form a hydrogel bead-plasma mixture; (c) causing the
agitator to stir the hydrogel bead-plasma mixture, minimizing gel
polarization and facilitating absorption of water by the beads from
the plasma, until a hydrogel bead-plasma concentrate is formed; and
(d) separating plasma concentrate from the hydrogel beads from the
hydrogel bead-plasma concentrate by passing the plasma concentrate
through the filter and the concentrating chamber outlet port.
[0112] In Dorian's method, a plunger can be positioned in the
concentrating chamber, the hydrogel beads and agitator are
positioned in the concentrating chamber between the plunger and the
filter, and the concentrating chamber has an inner concentrating
chamber wall, the plunger having an outer edge surface conforming
to a surface of the inner concentrating chamber wall. With this
variation of the device, the method can comprise (a) centrifuging a
plasma cell mixture in the centrifugal separation chamber to form
an erythrocyte-rich layer and a plasma layer; (b) moving plasma
from the plasma layer through the inlet/outlet port and the filter
by axial movement of the plunger in the proximal direction away
from the filter; (c) moving the plasma concentrating device in
alternative distal and proximal directions along the central axis
of the concentrating chamber to stir the hydrogel bead-plasma
mixture, minimizing gel polarization and facilitating absorption of
water by the beads from the plasma, until a hydrogel bead-plasma
concentrate is formed; and (d) separating plasma concentrate from
hydrogel beads by moving the plasma concentrate through the filter.
In step (d) the plasma concentrate can be moved through the filter
and into the concentrate outlet by moving the plunger in the distal
direction toward the filter. Other means of moving the plasma
concentrate through the filter are within the intended scope of
this invention, such as movement by centrifugal force or suction,
for example.
[0113] In U.S. Pat. No. 7,553,413, dated Jun. 30, 2009 entitled
"PLASMA CONCENTRATOR DEVICE," the inventors Randel Dorian, Michael
D. Leach and Richard Wood Storrs, the entire contents of which are
hereby incorporated herein by reference, disclose a plasma
concentrator of this invention having a concentrator chamber,
concentrator gel beads, a filter, and an agitator. The agitator has
agitator blades extending outwardly from the lower end. The
agitator end is positioned in the concentrator chamber and
supported for rotation about its central axis and for reciprocal
movement along its central axis. The concentrator has a top with an
upper opening through which the upper end of the actuator stem
extends, and a lower opening in which the filter is positioned. The
concentrator chamber can have a cylindrical inner wall, and the
agitator blades can have an outer edge in close proximity to the
inner wall with the space between the outer edge and the inner wall
being less than the diameter of the gel beads. The filter is
selected to block effective flow of plasma therethrough under
ambient gravity conditions and permit plasma and plasma concentrate
flow therethrough under centrifugal forces of the separation
gravity. The method concentrates plasma by removing water without
significantly denaturing the fibrinogen in the plasma. The plasma
is introduced into a concentration chamber containing a plurality
of dehydrated concentrator gel beads and an agitator. Then water is
removed from the plasma while stirring the beads to reduce plasma
polarization and breaking up clumps of beads that form during the
agitation. Then centrifugal force can be applied to the
concentrated plasma in an amount sufficient to separate a
substantial portion of the plasma concentrate from the beads.
[0114] A major improvement in making plasma concentrate from whole
blood for use in wound healing and as a tissue sealant is described
in U.S. Pat. No. 5,585,007; this patent is hereby incorporated
herein by reference in its entirety. This device, designed for
placement in a medical laboratory or surgical amphitheater, used a
disposable cartridge for preparing tissue sealant. The device was
particularly applicable for stat preparations of autologous tissue
sealants. Preparation in the operating room of 5 ml of sealant from
50 ml of patient blood required less than 15 minutes and only one
simple operator step. There was no risk of tracking error because
processing can be done in the operating room. Chemicals added could
be limited to anticoagulant (e.g., citrate) and calcium chloride.
The disposable cartridge could fit in the palm of the hand and was
hermetically sealed to eliminate possible exposure to patient blood
and ensure sterility. Adhesive and tensile strengths of the product
were comparable or superior to pooled blood fibrin sealants made
with precipitation methods. Use of antifibrinolytic agents (such as
aprotinin) was not necessary because the tissue sealant contained
high concentrations of natural inhibitors of fibrinolysis from the
patient's blood. This new tissue sealant also optionally contained
patient platelets and additional factors that promote wound
healing, healing factors that are not present in commercially
available fibrin sealants.
[0115] This device used a new sterile disposable cartridge with the
separation chambers for each run. Since the device was designed to
be used in a normal medical setting with ample power, the permanent
components, designed for long-term durability, safety and
reliability, were relatively heavy, using conventional centrifuge
motors and accessories.
[0116] Small, self-contained centrifugal devices for obtaining
platelet concentrates from blood are described in application Ser.
No. 10/394,828 filed Mar. 21, 2003, the entire contents of which
are hereby incorporated herein by reference. This device separates
blood into erythrocyte, plasma and platelet layers and selectively
removes the platelet layer as a platelet concentrate, that is,
platelets suspended in plasma. The plasma fraction, being in an
unconcentrated form, is not effective as a hemostat or tissue.
[0117] In a patent application entitled "Buoy Suspension
Fractionation System" with the application Ser. No. 12/101,586
(Publication No. 2009/0014391 A1), filed on Apr. 11, 2008, the
entire contents of which are hereby incorporated herein by
reference, Leach discloses a separator that uses centrifugation to
fractionate a suspension such as blood comprises a separation
container and a buoy. The buoy is carried in the separation
container and has a tuned density that is configured to reach an
equilibrium position in a suspension. The guide surface is carried
on the buoy upper surface and is inclined to an accumulation
position near a buoy perimeter. The buoy suspension fractionation
system can be used in a method of isolating a fraction from a
suspension, and in a method for re-suspending particulates for
withdrawal.
[0118] In patent application entitled "Apparatus and method for
separating and isolating components of a biological fluid" having
application Ser. No. 12/315,722 (Publication No. 2010/0140182 A1)
and a filing date of Dec. 4, 2008, the entire contents of which are
hereby incorporated herein by reference, Chapman et al. discloses
that it is known to separate biological fluids, such as aspirated
bone marrow or peripheral blood, into their component parts,
fractions, phases, or constituent layers by centrifugation. It is
also known to provide mechanical devices comprised of a tube which
houses a solid separator which, when actuated by centrifugal force,
allows biological fluid to flow through or around the piston based
on differing relative densities thereby separating the biological
fluid into a one or more component parts above and one or more
component parts below the solid separator. For example, when the
biological fluid within the tube is blood, the centrifugation
process results in a high density layer of red blood cells below
the solid separator, a low density layer of plasma above the solid
separator, and a buffy coat layer which defines an intermediate
density layer or third fraction above the solid separator and below
the low density layer of plasma.
[0119] One of the earliest solid separators was disclosed in U.S.
Pat. No. 3,508,653, issued Apr. 28, 1970 to Coleman, the entire
contents of which are hereby incorporated herein by reference. That
device was a rubber or other elastomeric cylinder. A major problem
with that device was the inability to maintain a seal because it is
costly to maintain the precise inner diameter of the test tube when
mass produced. A subsequent solid separator development is
disclosed in U.S. Pat. No. 3,814,248, issued Jun. 4, 1974 to
Lawhead, the entire contents of which are hereby incorporated
herein by reference. Next, U.S. Pat. No. 3,779,383, issued Dec. 18,
1973 to Ayres, the entire contents of which are hereby incorporated
herein by reference, disclosed a device in which the blood
introduction end of the tube is opposite to the movable separator
end of the tube, and abutting an impenetrable rubber closure.
Following Ayres, U.S. Pat. No. 3,931,018, issued Jan. 6, 1976 to
North, Jr., the entire contents of which are hereby incorporated
herein by reference, disclosed a solid separator for use in
separation of blood serum and blood plasma using centrifugal force
that must be inserted into the blood collection tube after blood
collection.
[0120] In a patent to Levine, et al. (U.S. Pat. No. 4,159,896,
issued Jul. 3, 1979), the entire contents of which are hereby
incorporated herein by reference, a centrifugally motivated solid
separator device is disclosed in which a cylindrical float is
disposed inside of a tube, which float has an accurately controlled
outside diameter so as to fit snugly in the tube bore under static
conditions. When used in harvesting blood cells the float is formed
with an axial through bore which receives and expands the white
cell and platelet layers in the blood sample after centrifugation
thereof. The disclosed float was made from a plastic material
having a specific gravity that causes it to float in the packed red
cells after centrifugation of the blood sample in the tube.
[0121] In another patent to Levine, et al, (U.S. Pat. No.
5,393,674, issued Feb. 28, 1995), the entire contents of which are
hereby incorporated herein by reference, a clear plastic tube large
enough to process 1 ml of blood and equipped with a cylindrical
float and filled with an inert gas at low pressure is disclosed.
The float contains a through bore, and prior to centrifugation, is
held fixably at an initial location by tight contact between the
exterior of the float and the interior wall of the tube. Unlike the
inventions of Coleman, which contain pistons (or buoys) with no
through bore, the Levine float relocates, under centrifugation, to
a new position determined by its density relative to the density of
the blood fractions as a result of the shrinkage of its diameter
due to the longitudinal elongation (and subsequent lateral
narrowing) of the float body that results from the substantial
gravity gradient that occurs from the top to the bottom of the
float. This substantial G force gradient (several thousand Gs)
causes the float to elongate and narrow just as a rubber tube
elongates and narrows when pulled from both ends. This space
between the exterior of the float and the interior of the tube that
develops during centrifugation provides the freedom of movement of
the float consequent with the motion of the blood components to
their new location determined by their density relative to the
float. Levine does not posit, but it is assumed that some of the
redistributing blood components also travel through the bore during
centrifugation but since the top and bottom of the through bore are
not closed, any cells and platelets that wind up there following
centrifugation are easily infiltrated by the red cells and plasma
during normal post centrifugation handling. Designed predominately
as a diagnostic tool that proceeds through the visual examination
of the cells that at least temporarily occupy the through bore
right after centrifugation, Levine also discloses the possibility
of extracting these cells with a syringe needle for additional
diagnostic examination. This method of extraction necessarily is
inefficient as a means of cell recovery as the intruding needle
necessarily relocates the target cells above and below the through
bore as it is inserted.
[0122] Hence, these known mechanical devices are generally capable
of separating biological fluids into component parts or fractions;
however, these devices are not very precise thereby resulting in
inefficient separation of the biological fluid into component parts
or fractions because of the substantial commingling of the
separated fractions. Additionally, these known mechanical devices
fail to provide a simple or efficient method to extract a fraction
other than the top fraction of the sample leading to low
recoveries, especially of the clinically important buffy coat
fraction.
[0123] It is also known to provide more complicated mechanical
devices in an attempt to alleviate the above known problems. For
example, the patent to Leach, et al. (U.S. Pat. No. 7,374,678,
issued May 20, 2008), the entire contents of which are hereby
incorporated herein by reference, in a first embodiment, discloses
a device for separating a sample, such as blood, into a plurality
of fractions. The device is comprised of a plunger (or second
piston) which, prior to centrifugation, is retained proximate a top
end of a closed ended distortable tube during centrifugation and a
first piston (or buoy) which is tightly fitted near the bottom of
the closed ended distortable tube such that under centrifugation
with a sample of blood, the tube wall longitudinally compresses and
bows outward thereby allowing the buoy to move in a direction of
the top of the tube lifted by a layer of red blood cells of higher
density than the piston that has flowed downward between the buoy
and the interior of the tube wall. After centrifugation, the tube
wall returns to its original dimension and traps this first piston
at a new location coinciding with the interface position of a top
plasma fraction and a bottom red blood fraction of the separated
sample. On or near a collection face of this first piston (or buoy)
is a third fraction which includes "a small, yet concentrated,
amount of red blood cells, white blood cells, platelets, and a
substantial portion of a buffy coat of the blood sample." The
device then employs a plunger (or second piston) which is manually
pushed down into the tube from a location proximate the top end of
the tube. The plunger (or second piston) includes a valve which
allows the plasma to pass through the plunger to while the plunger
is lowered to a predetermined depth above the first piston set by a
depth gauge which locates the plunger a distance away from the
collection face of the piston thereby defining a third fraction
between a bottom face of the plunger (or second piston) and the
collection face of the first piston. The extraction of the third
fraction is accomplished via a vacuum created on a tube extending
between a collection valve disposed in the top of the tube and a
bore extending from the top of the plunger and the bottom of the
plunger.
[0124] Accordingly, this device relies on the imprecise
longitudinal compression and decompression of the tube wall in
order to control the flow path between fractions and fails to
contain the separated fractions until after centrifugation stops
and the tube wall returns to its original dimensions. Furthermore,
the extraction of the third fraction requires infiltration of the
top plasma fraction. Hence, this recently patented device still
fails to alleviate the problem of inefficient separation of the
biological fluid into component parts or fractions and the
commingling of the separated fractions.
[0125] In another embodiment, Leach, et al. discloses that the
plunger (or second piston) is rigidly or slideably fitted with the
first piston or buoy such that the pair is tightly fitted within
the closed ended distortable tube wherein under centrifugation with
a sample such of blood, the tube wall bows outward thereby allowing
the pair to move in a direction of the top of the tube while lifted
by a high density layer of red blood cells flowing downward between
the pair and the interior of the tube wall. After centrifugation,
the tube wall returns to its original dimension which grips the
periphery of the first piston at an interface position of a plasma
fraction and a red blood fraction of the separated sample. On or
near a collection face of this first piston is "a small, yet
concentrated, amount of red blood cells, white blood cells,
platelets, and a substantial portion of a buffy coat of the blood
sample." The extraction of the intermediate (buffy coat) or third
fraction is accomplished "by interconnecting a cannula or bored
tube with the connection portion of the buoy cylinder" and
connecting an extraction syringe to the cannula for creating a
vacuum to draw the intermediate or third fraction from the space
between the first and second pistons. This embodiment describes
only one centrifugation spin, and fails to alleviate the problem of
inefficient separation of the biological fluid into component parts
or fractions and the commingling of the separated fractions.
Furthermore, the extraction of a fraction other than the top
fraction still requires the infiltration of at least one other
fraction than the desired fraction to be extracted. Moreover, the
device relies on the imprecise longitudinal compression and
decompression of the tube wall in order to control the flow path
between fractions and fails to contain the separated fractions
until centrifugation stops and decompression of the tube wall is
concluded.
[0126] Another problem associated with both embodiments of Leach,
et al. is that the collection face, trough, or sump of the buoy
must be shallow to be at a desired density level of the target
buffy coat fraction and to preclude even further accumulation of
reds cells with the target white cells and platelets to be
extracted. Thus, this shallow trough results in having the target
white blood cells and platelets, come to rest on the entire large
surface area of the first piston on which the white blood cells and
platelets tend to stick, which reduces the efficiency of the final
collection step. A further problem associated with both embodiments
of Leach, et al. is the time consuming and laborious process of
fitting and interconnecting multiple parts to the device in order
to perform the extraction process.
[0127] In general, current processes for separating and extracting
fractions out of biological fluids require multiple steps that are
both laborious and time consuming and that result in poor
recoveries of the target white cells and platelets. Hence, it would
be desirable to provide a simplified and more effective process so
less time, labor, and training is required to do the procedure and
fewer white cells and platelets are lost thereby providing a
positive economic impact. A simplified process would also allow it
to be performed in an intra-operative setting by an operating room
nurse, rather than a remote laboratory setting by a technician so
that a patient can be more rapidly treated and the possibility of
mixing up samples can be essentially eliminated. Process
simplification also has a direct correlation to process
reproducibility that is also a problem with the known prior
art.
[0128] Hence, the known prior art is problematic in a number of
areas which include a deficiency in the recovery efficiency of
cells of interest (target cells), in the selectivity of separation
for reducing contamination or non-target cells from the target cell
population, and in the multiple step, laborious, and time consuming
extraction process. A summary of the invention of Chapman disclosed
in application Ser. No. 12/315,722 is a device for separating and
isolating components of a biological fluid comprising a container
for containing the fluid to be processed, a tube cap assembly for
closing the container while providing filling and extraction
communication therewith, a float assembly disposed within the
container for funneling and controlling biological fluid flow into
an inverted domed shaped isolation chamber within the float and
controlling the biological fluid flow out of the isolation chamber
for effecting an encapsulation or a sealed isolation of at least
one component or fraction of the biological fluid flow within the
isolation chamber during a centrifugation process. The device
further comprising a flexible tube for connecting an extraction
passageway disposed within the float assembly and an extraction
valve of the tube cap assembly for allowing extraction of at least
the one component or fraction encapsulated or isolated within the
chamber.
[0129] The Goddard et. al in U.S. Patent Application Publication
No. 2007/0259330 A1 published on Nov. 8, 2007, the entire contents
are incorporated herein by reference, describe an invention that
relates to the field of cell separation, and more specifically to a
method of separating mononuclear cells from blood. The Goddard
invention also encompasses a separation media which is used in the
present method, a container filled with such media and a kit useful
in cell separation.
[0130] U.S. Pat. No. 5,474,687 (Activated Cell Therapy), the entire
contents are incorporated herein by reference, relates to the
enrichment of CD34+ cells. More specifically, a method is
disclosed, which comprises layering a cell mixture containing CD34+
cells into a centrifuge tube, said density gradient solution having
an osmolality of 280.+-.10 mOsm/kg H2O and a specific density
within 0.0005 g/ml of the specific density of said CD34+ cells;
centrifuging said tube at a gravitational force sufficient to
pellet cells having specific densities greater than the specific
density of the density gradient material in said tube; and
collecting from the upper portion of said tube an enriched
population of CD34+ cells.The tube used in the method comprises an
annular member disposed in said tube and defining an opening there
through, which opening has an area less than the area of a cross
section of the tube.
[0131] In one embodiment, the method further comprises incubating
said cell mixture with a cell type-specific binding agent linked to
carrier particles prior to centrifugation, said particles having a
specific density that is at least 0.001 g/ml greater than the
specific density of said density gradient solution. This binding
agent may bind to non-CD34+ cells, and may e.g. be an antibody
directed to the CD45 antigen. The density gradient solution may
e.g. be selected from the group consisting of Percoll.TM.,
Ficoll.TM., Ficoll-Hypaque.TM., albumin, sucrose and dextran. As
appears from the above, there is still a need in this field of
novel purification protocols which allow efficient purification of
viable mononuclear cells from blood in yields useful for clinical
applications.
[0132] The invention of Vlasselaer disclosed in U.S. Pat. No.
5,474,687 dated Dec. 12, 1995, the entire contents are incorporated
herein by reference, relates to methods of enriching hematopoietic
progenitor cells from body fluids. In particular, it relates to the
use of a cell-trap centrifugation tube containing a gradient
solution adjusted to a specific density to enrich for CD34.sub.+
cells from apheresed blood. The tube allows the desired cell
population to be collected by decantation after centrifugation to
minimize cell loss and maximize efficiency. In addition, the method
can be further simplified by density-adjusted cell sorting which
uses cell type-specific binding agents such as antibodies and
lectins is linked to carrier particles to impart a different
density to undesired cell populations allowing the progenitor cells
to be separated during centrifugation in a more convenient manner.
The rapid progenitor cell enrichment method described herein has a
wide range of applications, including but not limited to, donor
cell preparation for bone marrow transplantation without the use of
invasive procedures such as bone marrow aspiration.
[0133] The invention of Inbar et al. disclosed in U.S. Pat. No.
5,314,074 dated May 24, 1994 entitled "Method and Means for Density
Gradient Centrifugation," the entire contents are incorporated
herein by reference, discloses a method and means for density
gradient centrifugation.
[0134] U.S. Pat. No. 4,824,560, the entire contents are
incorporated herein by reference, discloses method and means for
centrifugation by which a tubular vessel is used with at least two
compartments in a row communicating with one another via a narrow,
essentially capillary opening. For operation, the working fluid is
charged into the lower compartment and the liquid to be centrifuged
into the upper one with no need for any special precautions to
avoid mixing prior to centrifugation. While this method has some
significant advantage over the above-described purely manual
methods, it has the drawback that the rather narrow passage between
the compartments provides some resistance even during
centrifugation which may prolong the operation. Moreover, the
method requires specially devised centrifugation vessels which
renders it relatively costly. Furthermore, since in accordance with
that method the entire lowermost compartment must be filled with
working fluid it is not possible to vary the amount of working
fluid in a given centrifugation vessel.
[0135] In 2008, C. Nilsson,et al. published a paper entitled
"Optimal Blood Mononuclear Cell Isolation Procedures for Gamma
Interferon Enzyme-Linked Immunospot Testing of Healthy Swedish and
Tanzanian Subjects" in Clin Vaccine Immunol. 15(4): 585 -589, the
entire contents are incorporated herein by reference, in which they
compared different existing methods of density gradient separation
of peripheral blood.
[0136] It is known in the prior art to digest tissues to release
cells. Such cell suspensions can be made from surgically removed
tumors or from normal tissue such as adipose. Gimble et al
published a review manuscript in Circulation Research 100(9)
1249-60 entitled "Adipose-derived stem cells for regenerative
medicine" for which the entire contents are incorporated herein by
reference, which reviews the known art of cell isolation and
mechanical devices for adipose tissue processing. References cited
refer to article references found in the publication of Gimble.
[0137] The initial methods to isolate cells from adipose tissue
were pioneered by Rodbell and Rodbell and Jones in the 1960s. They
minced rat fat pads, washed extensively to remove contaminating
hematopoietic cells, incubated the tissue fragments with
collagenase, and centrifuged the digest, thereby separating the
floating population of mature adipocytes from the pelleted stromal
vascular fraction (SVF). The SVF consisted of a heterogeneous cell
population, including circulating blood cells, fibroblasts,
pericytes, and endothelial cells as well as "preadipocytes" or
adipocyte progenitors. The final isolation step selected for the
plastic adherent population within the SVF cells, which enriched
for the "preadipocytes."
[0138] Subsequently, this procedure has been modified for the
isolation of cells from human adipose tissue specimens. Initially,
fragments of human tissue were minced by hand; however, with the
development of liposuction surgery, this procedure has been
simplified. During tumescent liposuction, plastic surgeons infuse
the subcutaneous tissues with a saline solution containing
anesthetic and/or epinephrine via a cannula and then remove both
the liquid and tissue under suction. The procedure generates finely
minced tissue fragments, the size of which depends on the
dimensions of the cannula. Independent studies have determined that
liposuction aspiration alone does not significantly alter the
viability of isolated SVF cells. Indeed, adherent stromal cells
with characteristics of adipocyte progenitors can be found directly
within the liposuction aspiration fluid, as well as in SVF derived
from the tissue fragment digests. However, when ultrasound-assisted
liposuction is performed, the number of cells recovered from tissue
digests is reduced, as is their proliferative capacity. The
recovery of ASCs can be improved further by manipulating the
centrifugation speed. Investigators have achieved optimal cell
recovery using a centrifugation speed of 1200 g based on the
subsequent formation of a human-derived adipose tissue depot
following implantation in an immunodeficient murine model.
[0139] The cell isolation process requires the manipulation of
large volumes of lipid-laden cells, presenting potential risks to
equipment and personnel. To facilitate the process, several groups
have fabricated devices to automate the cell isolation. One
approach uses a "bag within a bag." The suctioned aspirate flows
through a central bag that automatically sieves the tissue while
draining away the aspiration fluid. Subsequently, the trapped
tissue can be washed and further manipulated. Others have developed
a closed, rotating, controlled temperature incubator capable of
collagenase digesting and separating up to one liter of tissue at a
time. These prototypes may one day lead to commercially available
manufactured devices for large scale, automated adipose tissue
manipulation and cell isolation suitable for clinical
applications.
[0140] Collas discloses a protocol for separation of the stromal
vascular fraction from adipose consists of the following steps:
[0141] Lipoaspirate Washing
[0142] It is necessary to wash the lipoaspirate extensively to
remove the majority of the erythrocytes and leukocytes. The
following procedures should be performed under aseptic conditions.
Place a maximum of 300 ml of lipoaspirate into a used sterile
medium bottle. Allow the adipose tissue to settle above the blood
fraction. Remove the blood using a sterile 25 ml pipette. Add an
equivalent volume of HBSS with antibiotics and fungizone and firmly
tighten the lid. Shake vigorously for 5-10 seconds. Place the
bottle on the bench and allow the adipose tissue to float above the
HBSS. This will take 1-5 min depending on the sample.
[0143] Carefully remove the HBSS using a 50 ml pipette. Repeat the
above washing procedure (steps 4 to 7) three times. Medium from the
final wash should be clear. If it is still red, wash again by
repeating steps 4.
[0144] Collagenase Digestion
[0145] Dispersion of adipose tissue is achieved by collagenase
digestion. Collagenase has the advantage over other tissue
digestive enzymes that it can efficiently disperse adipose tissue
while maintaining high cell viability. Make up collagenase solution
just prior to digestion. The final volume required is half that of
the washed adipose tissue volume. Add powdered collagenase to HBSS
at a final concentration of 0.2%. We dissolve the required amount
of collagenase into 40 ml of HBSS, then filter sterilize into the
remaining working volume. Add antibiotics and fungizone. Add the
washed adipose tissue to large cell culture flasks (100 ml per 162
cm2 flask). Add collagenase solution. Re-suspend the adipose tissue
by shaking the flasks vigorously for 5-10 seconds. Incubate at
37.degree. C. on a shaker for 1 to 2 h, manually shaking the flasks
vigorously for 5-10 seconds every 15 min. During the digestion,
prepare Histopaque gradients by dispensing 15 ml of Histopaque-1077
into 50 ml tubes. Two gradients are required for each 100 ml of
washed adipose tissue. The gradients must be equilibrated at room
temperature before use. Prepare 200 ml of washing medium consisting
of HBSS containing 2% FBS, antibiotics and fungizone. On completion
of the digestion period, the digested adipose tissue should have a
"soup like" consistency. Add FBS to a final concentration of 10% to
stop collagenase activity.
[0146] Separation of the Stromal-Vascular Fraction
[0147] After digestion, the ability of lipid-filled adipocytes to
float is used to separate them from the stromal vascular fraction
(SVF). Dispense the collagenase-digested tissue into 50 ml tubes.
Avoid dispensing undigested tissue. Centrifuge at room temperature
at 400.times.g for 10 min. After centrifugation, use a 50 ml
pipette to aspirate the floating adipocytes, lipids and the
digestion medium. Leave the SVF pellet in the tube.
[0148] Separation of Stromal Stem Cells from the SVF
[0149] The SVF predominantly contains erythrocytes, leukocytes,
endothelial cells and stromal stem cells. Erythrocytes are removed
first, using the red blood cell lysis buffer.
[0150] Removal of erythrocytes. Re-suspend thoroughly each SVF
pellet in 20 ml of cell lysis buffer at room temperature. Incubate
at room temperature for 10 min. Centrifuge at 300.times.g for 10
min and aspirate the cell lysis buffer.
[0151] Removal of cell clumps and remaining undigested tissue. It
is essential to obtain a cell suspension free from undigested
tissue and cell clumps, to effectively separate stromal stem cells
from other cell types using antibody-conjugated magnetic beads. The
strategies used to achieve this are separation of gross undigested
tissue using gravity, straining of cells and gradient separation.
Re-suspend SVF pellets thoroughly in 2 ml of washing medium using a
1 ml pipette. Pipet the cells up and down several times to reduce
clumping. Pool the pellets into two 50 ml tubes. Allow undigested
tissue clumps to settle by gravity for .about.1 min. Aspirate and
pass the suspended cells through 100 .mu.m cell strainers. Pass the
filtered cells through 40 .mu.m cell strainers. Add extra washing
buffer so that the final volume is equivalent to that of the
gradients (i.e., for 4 gradients, the volume of cells in washing
buffer should be 60 ml).
[0152] Ficoll Separation
[0153] Hold each tube containing Histopaque at a 45 degree angle
and carefully add the cells by running the suspension along the
inside wall of the tube at a flow rate of .about.1 ml per second.
Careful layering of cells onto the gradients is essential for
successful cell separation. Centrifuge gradients at exactly
400.times.g for 30 min. Carefully remove the medium (.about.10 ml)
above the white band of cells found at the gradient interface and
discard. Carefully remove the white band of cells (.about.5 ml) by
careful aspiration and place into a new 50 ml tube. Add an
equivalent volume of washing medium and centrifuge at 300.times.g
for 10 min using a low brake setting. Aspirate and re-suspend each
pellet in 25 ml of washing medium. Centrifuge at 300x g for 10 min
using a low brake setting.
[0154] Separation of stromal stem cells from endothelial cells and
leukocytes by magnetic cell sorting.
[0155] Stromal stem cells are separated from remaining cells using
magnetic cell sorting. Unwanted endothelial (CD31+) and leukocytes
(CD45.sub.+) are magnetically labeled and eliminated from the cell
suspension when applied to a column under a magnetic field.
Magnetically labeled cells are retained in the column, while
unlabeled stem cells with a CD45-CD31- phenotype pass through the
column and are collected. To this end, CD31+ and CD45+ cells are
labeled with FITC-conjugated anti-CD31 and anti-CD45 antibodies.
The stained cells are magnetically labeled by the addition of
anti-FITC-conjugated magnetic micro-beads. This approach presents
the advantage that cell purity after separation can be assessed by
flow cytometry or fluorescence microscopy. For the following steps,
use cold buffer and work on ice to reduce cell clumping. Re-suspend
and pool the sedimented pellets in 10 ml of column buffer (PBS
containing 2 mM EDTA and 0.5% BSA). Remove all remaining cell
clumps by passing the suspension through a 40 .mu.m cell strainer.
Perform a cell count. Transfer cells to a 15 ml tube and centrifuge
at 300.times.g for 10 min at 4.degree. C. using a low brake
setting. Re-suspend the cell pellet in column buffer and label with
anti-CD31 FITC-conjugated and anti-CD45 FITC-conjugated antibodies
according to the manufacturer's recommendations. Suspend cells in
100 .mu.l of column buffer and add 10 .mu.l of each antibody per
107 cells. Mix well and incubate for 15 min in the dark at
4.degree. C. (re-suspend the cells after 7 min of incubation). Wash
the cells to remove unbound antibody by adding 2 ml of column
buffer per 107 cells. Centrifuge at 300.times.g for 10 min at
4.degree. C. using a low brake setting. Aspirate the supernatant
completely and re-suspend the cell pellet in 90 .mu.l of column
buffer per 107 cells. Add 10 .mu.l of MACS anti-FITC magnetic
micro-beads per 107 cells. Mix well and incubate for 15 min at
4.degree. C. (re-suspend the cells after 7 min of incubation). Wash
the cells to remove unbound beads by adding 2 ml of column buffer
per 107 cells. Centrifuge at 300.times.g for 10 min at 4.degree. C.
using a low brake setting. Aspirate the supernatant completely and
re-suspend the cell pellet in 500 .mu.l of column buffer. For
magnetic cell separation, we use the MACS LD column specifically
designed for the depletion of unwanted cells. Place a MACS LD
column onto the MidiMACS separation unit or onto a compatible unit.
Prepare the column by washing with 2 ml of column buffer. Apply the
cell suspension to the column and collect the flow-through
unlabeled cells in a 15 ml tube. Wash unlabeled cells through the
column by twice adding 1 ml of column buffer. Collect the total
effluent. Check for stem cell purity If higher purity is required,
centrifuge the collected cells at 300.times.g for 10 min at
4.degree. C. using a low brake setting and repeat steps 11-17.
Perform a cell count. Centrifuge at 300.times.g for 10 min at
4.degree. C. using a low brake setting. Use the cells as required
or freeze the cells according to standard protocols.
[0156] A patent was awarded to Fraser et al. in U.S. Pat. No.
7,390,484 on Jun. 24, 2008 entitled "Self Contained Adipose Derived
Stem Cell Processing Unit" for which the entire contents are
incorporated herein by reference.
[0157] A paper was published by Conde-Green et al. entitled
"Effects of Centrifugation on Cell Composition and Viability of
Aspirated Adipose Tissue Processed for Transplantation" in the
Aesthetic Surgery Journal vol. 30 no. 2 249-255, 2010 for which the
entire contents are incorporated herein by reference. The authors
state centrifugation is one of the preferred methods of fat
processing. Although it has been promoted for nearly three decades
to separate adipose tissue components before grafting, there remain
many controversies regarding the results obtained with centrifuged
adipose tissue. In this paper, the authors demonstrate the effects
of centrifugation on the cellular components of aspirated fat.
[0158] To do the study, fat harvested from the lower abdomen of 10
female patients undergoing liposuction was divided in two equal
parts, then processed by decantation or centrifugation and sent to
the laboratory. Each processed lipoaspirate was analyzed
histologically after hematoxylin and periodic acid-Schiff staining
for the presence of intact adipocytes. It was then cultured and
analyzed by multicolor flow cytometry for identification of
adipose-derived mesenchymal stem cells.
[0159] The authors found the middle layer of the centrifuged
lipoaspirate, which is used by many surgeons, showed a great
majority of altered adipocytes and very few mesenchymal stem cells
in comparison with the decanted sample, which maintained the
integrity of the adipocytes and showed a greater number of
mesenchymal stem cells. The pellet observed as a fourth layer at
the bottom of the centrifuged lipoaspirate showed the greatest
concentration of endothelial cells and mesenchymal stem cells,
which play a crucial role in the angiogenic and adipogenic effect
of the grafted tissue. It was concluded that if centrifuged
lipoaspirate is used, the pellet (rich in adipose-derived
mesenchymal stem cells) and the middle layer should be employed to
increase fat graft survival.
[0160] Xie et al. published a paper entitled "The effect of
centrifugation on viability of fat grafts: an evaluation with the
glucose transport test" in Journal of Plastic, Reconstructive &
Aesthetic Surgery 63(3) 482-487, 2010 for which the entire contents
are incorporated herein by reference.
[0161] The authors state that an up-to-date, simple, but useful
technique to evaluate the viability of fat grafts prior to
transplant is lacking. The purpose of this study is to introduce
the glucose transport test--a new method to evaluate the viability
of fat grafts after they are subjected to different centrifugal
forces in vitro.
[0162] To conduct the their study, fat grafts were harvested from
healthy patients who underwent liposuction for body contouring. The
glucose transport test was performed to evaluate the viability of
fat grafts after centrifugation with different forces (1000-4000
rpm). An MTT assay was also performed with the same experimental
protocol for comparison. Routine histological examination was done
in all groups to examine possible structural destruction after
centrifugation.
[0163] When compared with the group not subjected to
centrifugation, the glucose transport test showed a significant
decrease in viability of fat grafts in all of the other four groups
(all p<0.001). There was a linear reduction of viability in fat
grafts with the increase in centrifugal force (all p<0.03). MTT
assay showed similar findings on the viability of fat grafts in all
five groups and correlated well with the glucose transport test
(r=0.9870). Histology showed significantly distorted and fractured
adipocytes when the centrifugal force reached 4000 rpm. The authors
conclude their study demonstrates the harmful effect on the
viability of fat grafts with an increase in centrifugal force and,
for the first time, that the glucose transport test may be an
effective and potentially useful method to evaluate the viability
of fat grafts in a clinical setting.
[0164] Anderson et al. was awarded U.S. Pat. No. 6,346,421 on Feb.
12, 2002 entitled "Methods for Concentrating and Detecting
Microorganisms Using Centrifuge Tubes," for which the entire
contents are incorporated herein by reference.
[0165] Graham et al were awarded U.S. Pat. No. 4,436,631 on Mar.
13, 1984 entitled "Multiple Particle Washing System and Method of
Use" for which the entire contents are incorporated herein by
reference. Graham discloses a particle washing system and method of
use is wherein in a preferred embodiment the fluid containing the
desired particles is placed within an inner tube having near the
bottom thereof an orifice with a diameter at least equal to that of
the diameter of the particles, and wherein the inner tube is
positioned within an outer tube having a fluid with a density at
least equal to that of the solution containing the particles to be
separated but less than that of the particles.
[0166] The application of centrifugal force to the particles
directed toward the bottom of the outer tube causes the particles
to move through the orifice and through the outer solution
contained within the outer tube so that the particles are collected
from the inner solution, washed by the outer solution, and
subsequently sedimented at the bottom of the outer tube. Graham's
invention has the stated objective to permit the rapid separation
of particles from a solution in a "one step" operation. It is
another objective that during separation of the particles from the
solution containing the particles, the particles are washed so as
to remove any nonspecific serum coating and to dilute any solute
drag. It is yet another object that the original containing
solution be separately maintained from the resulting particle
concentration to permit the removal of the original mother solution
in order to reduce contamination. It is another object to permit
the separation of particles having different densities and
dispensing at least one of such particle types to the exclusion of
the sucrose typically having a molecular weight of 5,000 or more.
The serum albumin may be selected from the group consisting of
animal serum albumin and human serum albumin. Serum albumin, to be
compatible, cannot have human gamma globulin or human
complement.
[0167] The volumes of the washing solution and mother solution are
chosen so that the interface between these solutions is contained
within the inner hollow tube. Upon the application of centrifugal
force, the particles contained within the mother solution, placed
within the cavity formed by the hollow inner cylinder, are forced
to move through the mother solution towards the bottom of the test
tube in accordance with the sedimentation coefficients or Svedberg
Units characterizing the particles. Since the hollow interior
cylinder is merely resting upon the bottom of the outer test tube,
the washing solution is capable of penetrating into and out of the
inner hollow cylinder and is consequently, partially displaced.
[0168] It is still another objective of the present invention that
these objectives be accomplished in a simple system capable of
economical production and employable within simple, inexpensive
centrifuges commonly available. It is still yet another objective
that the apparatus and methodology of the present invention be
capable of replacing expensive automated cell washers presently
available. It is a further objective of the present invention to
not only provide methodology whereby the objectives may be
accomplished but also devices capable of meeting the desired
objectives.
[0169] Rimm et al were awarded U.S. Pat. No. 6,197,523 on Mar. 6,
2001 entitled "Method for the Detection, Identification,
Enumeration, and Confirmation of Circulating Cancer and/or
Hematologic Progenitor Cells in Whole Blood" for which the entire
contents are incorporated herein by reference. Rimm's method for
analyzing blood enables one to isolate, detect, enumerate and
confirm under magnification the presence or absence of target
cancer cells and/or hematologic progenitor cells which are known to
circulate in blood. The analysis is performed in a sample of
centrifuged anti-coagulated whole blood. The analysis involves both
morphometric and epitopic examination of the blood sample while the
blood sample is disposed in a centrifuged blood sampling tube.
[0170] The epitopic analysis of the presence or absence of cancer
cells relies on the detection of epitopes which are known to
present only on cancer cells; and the epitopic analysis of the
presence or absence of hematologic progenitor cells relies on the
detection of epitopes which are known to present only on
hematologic progenitor cells. The targeted epitopes on the target
cell types are epitopes which are also known to be absent on normal
circulating blood cells; and the target cancer cell epitopes are
epitopes which are known to be absent on target hematologic
progenitor cells. Fluorophors with distinct emissions are coupled
with antibodies which are directed against the targeted
epitopes.
[0171] The morphometric analysis is performed by staining the cells
in the blood sample with an intracellular stain such as acridine
orange which highlights the intracellular cell structure. Both the
morphometric and epitopic analyses are preferably performed at or
near the platelet layer of the expanded buffy coat in the
centrifuged blood sample. The morphometric analysis and/or the
epitopic analysis may be performed under magnification both
visually and/or photometrically.
[0172] Rimm's invention relates to a method and assembly for the
detection, identification, enumeration and confirmation of
circulating cancer and/or hematologic progenitor cells in an
anti-coagulated whole blood sample which is contained in a
transparent sampling tube assembly. The detection, identification,
enumeration and confirmation steps can all be performed in situ in
the sampling tube assembly. More particularly, the method of this
invention involves the centrifugal density-based separation of the
contents of the blood sample in a manner which will ensure that any
circulating cancer and/or hematologic progenitor cells in the blood
sample are physically displaced by their density into a
predetermined axial location in the blood sample and in the
sampling tube assembly, and also into a restricted optical plane in
the sampling tube assembly which is adjacent to the wall of the
sampling tube, and finally into a very well defined zone of that
optical plane.
[0173] Babson was awarded U.S. Pat. No. 4,639,242 on Jan. 27, 1987
entitled "Vessel and Procedure for Automated Assay" for which the
entire contents are incorporated by reference. A number of
procedures in the clinical laboratory require centrifugation.
Examples include clarification of samples by removal of sediments
or cells and removal of interfering proteins by specific
precipitating reagents. In such cases the desired supernatant
solution is normally decanted from the centrifuge tube to a clean
tube for further processing. The present invention allows complete
physical separation of the precipitate and supernatant solution in
a single tube so that the supernatant solution can further be
treated or sampled as by pipetting without disturbing the
precipitate.
[0174] Hydrolytic enzymes can be measured by their action on
insoluble substrates or soluble substrates that can be precipitated
and separated from soluble products of hydrolysis. These assays can
be performed in vessels of the present invention with fewer steps
and/or reagents than is customarily used.
[0175] The reaction vessel shown in the patent may optionally be
fabricated to contain a longitudinally extending divider within the
interior of the bottom of the vessel. This divider will provide the
interior of the vessel with a left reagent chamber and a right
reagent chamber. When using this alternative form of Vessel 1, it
is possible to place a first reactant in one reagent chamber and a
second reactant in the second reagent chamber without causing
interaction between the reagents. The reaction may then be started
by tilting the vessel to allow the reagents in each chamber to mix,
or by rapidly spinning the vessel about its longitudinal axis
thereby causing the reactants to flow upward along the inside walls
of the vessel and to mix during the spinning process.
[0176] The vessel 1 contains a collection chamber portion located
near the uppermost portion of the vessel. This chamber is formed by
an increase in their interior diameter of the vessel between two
outwardly extending shoulders.
[0177] In a contemplated use by the inventors, the reaction vessel
will act as a centrifuge tube spun about it longitudinal axis. If
so spun, the contents will be forced towards the wall of the vessel
be centrifugal force. As the vessel is tapered from a smaller lower
diameter to a lower diameter to larger upper diameter the
centrifugal force can be separated into two vectors: the major
vector perpendicular to the vessel wall and a smaller vector in the
upward direction parallel to the vessel wall. If the latter force
exceeds one gravity the tube contents will be transferred entirely
to the upper cylindrical portion of the vessel where the heavier
solids contained in the fluid will be deposited on the vessel wall.
If the upward force vector is less than one gravity the vessel
contents will remain entirely in the lower portion, assuming the
vessel has not been overfilled.
[0178] The amount of centrifugal force required to exceed one
gravity in the vertical direction is related to the degree of taper
in the mid-portion of the vessel, the greater the taper the greater
the vertical force vector and the less total centrifugal force
required. The centrifugation speed required to achieve that
centrifugal force is inversely related to achieve that centrifugal
force is inversely related to the diameter of the vessel according
to the following formula: rcf=5.585d(rpm/1000).sup.2.
[0179] Pahuski et al. were awarded U.S. Pat. No. 5,700,645 on Dec.
23, 1997 entitled "Methods and kits for separation, concentration,
and analysis of cells" for which the entire contents are
incorporated by reference.
[0180] Nielsen et al. were awarded U.S. Pat. No. 4,511,349 on Apr.
16, 1985 entitled "Ultracentrifuge Tube with Multiple Chambers" for
which the entire contents are incorporated by reference.
[0181] A patent was awarded to Glover et al. entitled "Vacutainer
with Positive Separation Barrier" U.S. Pat. No. 3,879,295 in 1975,
for which the entire contents are incorporated herein by reference.
Glover teaches that an improved device for separating serum from
cells preferably embody or provide a number of desirable attributes
e.g., (1) obtaining a sample of blood and achieving separation of
the two phases under sterile conditions; (2) minimizing the risk of
loss of identity of the donor; (3) minimizing the migration of
cells once the blood has been stratified into cells and serum; (4)
utilizing, storing, or transporting the serum without interplay
between the serum and the cells; (5) economic feasibility in
manufacturing a disposable device; (6) the ability physically
separate the container at a particular location determinable by the
purpose of the test; (7) rapidity and simplicity in inserting the
physical barrier to separate the serum from the cells.
SUMMARY OF THE INVENTION
[0182] With this invention a vessel is provided for use in a
centrifuge which utilizes unique geometry to enable more rapid
separation of the sample into fractions of different densities and
to maintain such fraction separation after centrifugation. The
vessel includes an interior space contained within an outer wall. A
barrier divides this interior space of the vessel into at least two
regions. These two regions are joined together over a top of a lip
of the barrier defining an uppermost portion of the barrier, so
that the two regions come together on an upper portion of the
vessel but are spaced from each other on a lower portion of the
vessel.
[0183] The vessel has a higher gee side and a lower gee side,
respectively defined by the portion of the vessel most distant from
a spin axis of the centrifuge and closest to the spin axis of the
centrifuge, when the vessel is positioned within a cradle or other
vessel support of the centrifuge. The barrier is oriented to divide
the interior space of the vessel into the higher gee region and the
lower gee region. Thus, after centrifugation is complete, and
spinning of the centrifuge stops, higher density fractions remain
on a higher gee side of the barrier with lower density fractions
remain on the lower gee side of the barrier.
[0184] Furthermore, sample separation can be enhanced and
accelerated by providing a face of the barrier closest to the spin
axis with a taper. This taper is selected so that portions of the
face closest to the lip are most distant from the spin axis with
portions of the face most distant from the lip closest to the spin
axis. This taper can be flat or curving, such as a concave curve,
with different contours on the face adjusting the separation
rate.
[0185] The vessel benefits from being configured for the specific
sample to be separated. In particular, the lip of the barrier can
be positioned and/or the region volumes selected to match expected
percentage constituents of each fraction within the sample. This
correlation can be exact or merely general in nature. With such
vessel optimization, the barrier maintains separation of the
fractions from each other after the centrifuge stops spinning for
easier and more complete measurement, collection or other post
separation processing.
[0186] In one embodiment the centrifuge is configured so that the
vessel is oriented upright during centrifugation. In such an
embodiment the barrier could be generally vertical with the face
and side opposite the face being tapered slightly from vertical.
Preferably, the face tapers so that the barrier has a greater
horizontal width where spaced from the lip than the horizontal
width at the lip. This taper can be flat or concave, or other
shapes to optimize separation.
[0187] In a second embodiment, the centrifuge is configured to
support the vessel at an angle away from vertical at least somewhat
with upper portions of the vessel closer to the spin axis than
lower portions of the vessel. In such a centrifuge, the barrier has
a face which is tapered at an angle which causes the tip of the
barrier to be further from the spin axis than portions of the face
spaced from the tip. With such a configuration, higher density
fractions of the sample can over time migrate up the face of the
barrier, over the lip and into the catch basin. Similarly, lower
density fractions which might begin within the higher density
region of the centrifuge can migrate up over the lip of the barrier
and into the lower density region of the centrifuge, provided that
the density of the particulate fraction is less than the density of
the suspending fluid.
[0188] For certain separations where higher density fractions are
present in relatively small overall percentages of the sample, the
higher density region on the higher density side of the barrier
benefits from being configured to have a small volume similar to
but slightly more than an expected percentage for the higher
density fraction of the sample. In this way, a relatively small
higher density fraction fills a majority or at least a relatively
large minority of the higher density region of the vessel. The
higher density fractions of the specimen can then be relatively
easily distinguished from the higher density region after spinning
of the centrifuge has ceased.
[0189] The vessel can be configured with inlet and outlet tubes
which access regions on opposite sides of the barrier. These tubes
are utilized for introduction of the sample into the vessel and for
removal of higher and lower density fractions from the vessel after
centrifugation.
OBJECTS OF THE INVENTION
[0190] Accordingly, a primary object of the present invention is to
provide a vessel for use in a centrifuge which keeps differing
density fractions of a sample separate after centrifugation.
[0191] Another object of the present invention is to provide a
centrifugation vessel which facilitates more rapid separation of
differing density fractions therein.
[0192] Another object of the present invention is to provide a
centrifugation vessel which collects at least some differing
density fractions of a sample within a defined space to be more
readily measured, removed or otherwise analyzed or processed.
[0193] Another object of the present invention is to provide a
centrifugation vessel which is customized for the separation of a
particular sample into expected fractions.
[0194] Another object of the present invention is to provide a
centrifugation vessel optimized for separation of a biological
sample into at least two fractions of differing densities.
[0195] Another object of the present invention is to provide a
method for separation of a sample into differing density fractions
which also keeps the differing density fractions separate after
separation.
[0196] Another object of the present invention is to provide a
method for more rapidly separating a sample into differing density
fractions.
[0197] Another object of the present invention is to provide a
method for separating and collecting a fraction of a sample after
centrifugation.
[0198] Another object of the present invention is to provide a
centrifuge which separates and collects fractions of different
densities from a sample.
[0199] Another object of the present invention is to provide a
method and apparatus for separating particulate containing fluids
into at least two differing density fractions without the need for
any moving parts, to enhance operational reliability.
[0200] Other further objects of the present invention will become
apparent from a careful reading of the included drawing figures,
the claims and detailed description of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
[0201] FIG. 1 is a full sectional elevation view of a prior art
centrifuge and sample tube supported therein and illustrating prior
art separation of fractions of the sample.
[0202] FIG. 2 is a front elevation full sectional view of that
which is shown in FIG. 1 after rotation of the centrifuge has
stopped and illustrating how separated fractions transition to a
bottom of the tube after centrifugation.
[0203] FIG. 3 is a front elevation full sectional view of a
centrifuge and centrifuge vessel according to a first embodiment of
this invention with a barrier therein for separate collection of
differing density fractions.
[0204] FIG. 4 is a front elevation full sectional view of an
alternative embodiment of that which is shown in FIG. 3 with a
barrier exhibiting a concave face rather than a flat face.
[0205] FIGS. 5-9 are full sectional front elevation views of a
prior art tube undergoing centrifugation in a centrifuge having a
cradle which is angled to cause upper portions of the tube to be
closer to a spin axis of the centrifuge than lower portions of the
tube, and illustrating separation of differing density fractions
according to the prior art for such centrifuges.
[0206] FIG. 10 is a perspective exploded parts view of the
centrifuge vessel in the form of a tube preferred for certain forms
of biological sample separation.
[0207] FIG. 11 is a full sectional front elevation view of that
which is shown in FIG. 10.
[0208] FIG. 12 is a full sectional front elevation view of that
which is shown in FIG. 10 with supply and withdrawal tubes removed
and illustrating a variation where a higher density fraction
collection region is enlarged by featuring a beveled lower end
wall.
[0209] FIGS. 13-18 are front elevation views of a series of steps
associated with separation and collection of various fractions of a
biological sample according to a method of this invention, with
some of the figures showing the preferred tube in conjunction with
a syringe or supply of a sample or removal of fractions from the
tube, and some of the views showing the centrifuge operating on the
tube for centrifugation of the sample therein.
[0210] FIGS. 19-21 are front elevation full sectional views of the
tube of FIG. 10 and illustrating how different biological samples
can locate differing density fractions thereof in different
locations depending on the characteristics of the sample, such as
the hematocrit level of a blood sample.
DESCRIPTION OF THE PREFERRED EMBODIMENT
[0211] Referring to the drawings, wherein like reference numerals
represent like parts throughout the various drawing figures,
reference numeral 110 is directed to a preferred tube (FIGS. 10-12)
for use in a centrifuge (FIGS. 15 and 16) to separate a sample K
(FIGS. 13 and 14) into differing density constituents D, G, E
(FIGS. 16-18) for separate collection and removal. By supplying a
barrier such as a dam 120 (FIGS. 11 and 12) within a vessel, such
as in the form of the tube 110, higher density fractions D of the
sample K are caused to migrate through a spillway 140 from a
reservoir 130 to a catch basin 150 for separate collection,
facilitating later convenient and precise removal of various
different fractions of the sample.
[0212] In essence, and with particular reference to FIGS. 10-12,
basic details of the preferred tube 110 providing a preferred form
of centrifugation vessel for biological sample separation, are
described. The tube 110 is confined by an outer wall 112 and
includes a dam 120 as a preferred form of barrier dividing an
interior of the tube 110 into two separate regions. These regions
are defined in the preferred embodiment as a reservoir 130 and a
catch basin 150. A spillway 140 joins the two regions together over
a top of the dam 120. A size of the two regions can be customized
to correlate with expected prevalence of differing density
fractions within a sample. The dam 120 has a face 122 which is
particularly angled to allow migration of higher density fractions
up the face 122 and through the spillway 140 into the catch basin
150, and to accelerate such separation. The dam 120 maintains
separation even after the centrifuge ceases spinning. The
configuration of the dam 120 or other barrier within the tube 110
or other centrifuge vessel can be adjusted for differing types of
centrifuges and for use in separation of different samples and to
facilitate different rates of separation and degree of completeness
of separation.
[0213] More specifically, and with particular reference to FIGS. 1
and 2, basic details of prior art centrifuges to which this
invention is an improvement, are described. A most basic prior art
centrifuge includes a vertical spin axis A with a cradle C
configured to support a tube T in an upright fashion extending
vertically up out of the cradle C. The sample within the tube T
initially fills the tube T up to an initial fluid line B (FIG. 1).
When the centrifuge begins to spin (about the spin axis A) a
centrifugal force H (FIG. 1) acts laterally upon the sample within
the tube T.
[0214] Through the effects of higher gee forces upon the sample,
higher density fractions of the sample migrate further from the
spin axis A leaving lower density fractions of the sample closer to
the spin axis A. Such higher density fractions D are illustrated by
darker shading relative to lower density fractions E depicted by
lighter shading. A boundary F is located between the higher density
fraction D and the lower density fraction E with this boundary F
defining a transition between these two densities of fluids. A
certain amount of time is involved depending on the speed at which
the centrifuge rotor rotates and the distance that the cradle C is
located away from the spin axis A, and a differential in the
densities of the fractions being separated (and other fluid
characteristics). Depending on the purposes of the separation, it
may be sufficient to only partially separate the sample into
differing density fractions, or a greater degree of completeness of
separation may be pursued, such as by operating the centrifuge for
a longer period of time or changing the geometry of the
centrifuge.
[0215] One problem with prior art centrifugation using angular and
vertical rotors is illustrated in FIG. 2. To measure, remove or
otherwise act on fractions of the sample, the centrifuge is
typically stopped from spinning. This causes the higher density
fraction D to migrate to a bottom of the tube T with the lower
density fraction E migrating to an upper portion of the tube T.
Such migration takes place over a period of time as the centrifuge
slows to a stop. Depending on the nature of the fluid and the
difference in the densities between the fluid, and the speed and
smoothness with which the centrifuge decelerates to a standstill,
some degree of remixing of the fractions tends to occur, such that
the boundary is less clearly defined. Measuring, separation and
other action on different fractions of the sample is thus made more
complex. With such complexity, a greater amount of skill is
required for action on different fractions of the sample.
[0216] With particular reference to FIG. 3, basic details of a
basic tube 10 according to a first embodiment of this invention is
described. In this embodiment, the tube 10 acts as a form of
centrifuge vessel which resides within the cradle C of the
centrifuge vertically similar to the prior art (FIGS. 1 and 2).
Uniquely, the tube 10 includes a dam 20 which acts as a barrier
extending up from a floor 14 of the tube 10. This dam 20 is
typically fixed within the tube 10. An outer wall 12 of the tube 10
defines an interior space of the tube 10 which is divided by the
dam 20 into two regions. These regions are referred to as a
reservoir 30 and a catch basin 50. Portions of the interior space
of the tube 10 above the dam 20 are referred to as a spillway 40
where the two regions come together. A stopper 16 is typically
provided to contain the sample within the tube 10 during
centrifugation.
[0217] The dam 20 can have a variety of different configurations.
In a simplest configuration, the dam 20 could merely be a generally
vertical wall of nearly constant thickness extending up from the
floor 14. Most preferably, the dam 20 includes a face 22 which
tapers at an angle down from a lip 24 adjacent the spillway 40, the
lip 24 defining a portion of the dam 20 most distant from the floor
14. By angling the face 22, separation is enabled and a rate at
which separation occurs can be accelerated. Also, a relative volume
of the two regions is adjusted.
[0218] In this embodiment, the catch basin 50 has a constant width
away from a higher gee side of the tube 10. This width of the catch
basin 50 is configured to be small when a higher density fraction D
makes up a small portion of the overall sample, and this catch
basin 50 can be provided with a greater width and hence a greater
volume if the higher density fraction D has a greater proportion of
the overall sample. Such matching of the width of the catch basin
50 and the position of the dam 20 or other barrier within the tube
10 can be precise or merely approximate, to meet the design
objectives of the user.
[0219] Initially, the sample resides within the reservoir 30, and
optionally partially within the catch basin 50. During
centrifugation, this sample migrates against the higher gee portion
(that portion most distant from the spin axis of the centrifuge
when the tube 10 is within the spinning centrifuge 2, and the
corresponding opposite side being referred to as the "lower gee
side") of the outer wall 12 of the tube 10, such that the catch
basin 50 is filled with fluid and the reservoir 30 is only
partially filled, with fluid extending over the dam 20 and within
the spillway 40 region. The dam 20 can vary in height. In some
instances where a small initial sample is being separated, the dam
20 might extend as little as five percent of the way from the floor
of the tube 10 up to a top of the tube 10. In other embodiments,
the dam 20 might extend up to ninety-nine percent of a height of
the tube 10.
[0220] As separation occurs, a surface of the sample is defined by
line J (FIG. 3) with a boundary between fractions of differing
density is established as line I (FIG. 3). Then, when the
centrifuge ceases operation, and slows to a stop, the higher
density fluid D remains within the catch basin 50 and the lower
density fraction E falls down into the reservoir E. The separation
of the differing density fluids is thus maintained even after the
centrifuge has stopped rotating. This is in contrast to the less
precise boundary F (FIG. 2) provided by the prior art. Furthermore,
collection can be made more precise, and less complex in that
collection of higher density fluid D merely involves extraction
from the catch basin 50.
[0221] In FIG. 4, an alternative to the tube 10 of FIG. 3 is
depicted, in the form of tube 60. This alternative tube 60 includes
an outer wall 62 extending up from a floor 64 and with the
alternative tube 60 closed by a stopper 66. Such details are
similar to those of the tube 10 (FIG. 3). In this embodiment, an
alternative dam 70 is provided which uniquely exhibits a concave
face 72 which has a concave curving taper from the floor 64 up to a
lip 74, defining an uppermost portion of the alternative dam 70.
The alternative dam 70 divides a reservoir 80 from a catch basin
100 with a spillway 90 joining reservoir 80 and catch basin 100
together.
[0222] Operation of the alternative tube 60 within a centrifuge
occurs similar to the operation described above with respect to the
tube 10 (FIG. 3). However, because the alternative dam 70 has a
concave face 72, separation of the higher density fraction can
occur more rapidly. In particular, note that as the face 72
transitions towards the tip 74, a steeper angle is presented by the
face 72, so that a greater and greater force is required to cause
the higher density fraction to migrate over the tip 74 and into the
catch basin 100. However, as the higher density fraction D moves
closer to the higher gee wall of the tube 60, greater and greater
forces are acting on the higher density fluid D to drive the higher
density fluid D over the tip 74. With such a concave contour for
the face 72, these characteristics are optimized for rapid
separation.
[0223] With particular reference to FIGS. 5-9, details of a prior
art tube T' for use in a cradle C' of a centrifuge exhibiting an
angled cradle C' are described. In this prior art centrifuge, the
cradle C' is angled (FIG. 6) so that the upper end of the tube T'
is closer to the spin axis A at a lower portion of the tube T'
which resides within the cradle C'. An initial fluid line B for a
sample K remains horizontal before spinning of the centrifuge, with
such horizontal fluid line B parallel with the floor before
placement in the centrifuge and then angled relative to the floor
and non-perpendicular to outer walls of the tube T' after placement
within the cradle C' (FIGS. 5 and 6).
[0224] When the centrifuge begins to spin (about spin axis A (FIG.
7)) centrifugal forces acting along arrow H (FIG. 7) cause this
initial fluid line B to be angled to approximately vertical.
Centrifuges are allowed to continue to spin at a sufficiently high
rate to cause the higher density fraction D to migrate further from
the spin axis A, displacing a lower density fraction E toward the
spin axis A. In the representation depicted in FIG. 8, a
mid-density fraction G is also separated which migrates to a
location between the higher density fraction D and the lower
density fraction E. One such sample K is a biological sample which
includes higher density fractions D in the form of "pellet"
material and lower density fluid E in the form of plasma and
mid-density fluid G is in the form of a "buffy coat."
[0225] Once separation is complete, the centrifuge is decelerated
to a stop so that the final position of the fluids within the tube
T' are similar to that depicted in FIG. 9. Note that depending on
the characteristics of the biological sample, it can be difficult
to maintain full separation. As the various density fractions
migrate from their position during centrifugation (FIG. 8) and
after stopping of the centrifuge (FIG. 9) an opportunity is
presented for remixing of the various different fractions to some
extent. As depicted in FIG. 9, a boundary F' can tend to absorb
into the mid-density fraction G making this mid-density fraction G
difficult to identify, measure or extract.
[0226] Even if the separation remains complete, if the mid-density
fluid is a relatively small proportion of the overall sample,
extraction can be rather difficult in that an extraction tube must
be carefully placed at a depth precisely within such a mid-layer
without being too deep or too shallow. Such procedures typically
require skilled personnel and are not highly amenable to automation
and high reliability processing, unless exceptional care is taken
to ensure that the proper fraction is being extracted from the tube
T'.
[0227] With particular reference to FIGS. 10-12, details of a
preferred tube 110 for use in separating fractions from a sample K
such as a biological sample are described. This tube 110 provides
the preferred form of centrifuge vessel for certain forms of
separations. Variations on this preferred tube 110 can be made to
accommodate samples having different fraction constituent
percentages, or for separations which have fractions which have a
greater or lesser density differential from each other, or for
separations which are optimized for completeness of separation or
optimized for speed, or optimized for simplicity of the centrifuge
vessel, or optimized for other parameters defined by the user.
[0228] With this preferred tube 110, an outer wall 112 defines an
interior space of the tube 110. This outer wall 112 is preferably
cylindrical with a circular cross-section, but could have other
contours. The outer wall 112 extends up from a floor 114 to an
upper end which is enclosed by a cap 116. With this preferred tube
110, access into an interior of the tube 110 occurs through the cap
116. In particular, an in port 117 is supplied for accessing one
side of an interior of the tube 110 and an out port 118 is provided
for accessing of an opposite side of an interior of the tube 110.
An air port 119 is optionally provided to allow for removal of air
or other fluids contained within the tube 110 during introduction
of a sample to be separated. If required, a check valve or other
filter 115, such as an anti-microbial filter can be associated with
the air port 119 to prevent leakage or contamination from the air
port 119 during centrifugation. As an alternative, the tube 110
could be initially filled with a vacuum, so that no such air port
119 would be required. As another alternative, air could be removed
through one of the ports 117, 118 while a sample is introduced into
the tube 110 through the other of the ports 118, 117.
[0229] The tube 110 includes a barrier therein which separates an
interior of the tube 110 into two regions including a lower gee
region located closer to a spin axis A (FIG. 16) of the centrifuge
and a higher gee region located further from the spin axis A of the
centrifuge. This barrier is preferably in the form of a dam 120
with the two regions defined as a reservoir 130 closer to the spin
axis A (FIG. 16) and a catch basin 150 on a side of the dam 120
further from the spin axis A. A spillway 140 joins the reservoir
130 and catch basin 150 together over the dam 120.
[0230] The dam 120 could conceivably be a planar structure of
constant thickness. With such a configuration, the dam 120 would be
angled at an angle matching an angle of the cradle C' (FIGS. 15 and
16) so that this dam 120 would have approximately vertical sides
when undergoing centrifugation.
[0231] Most preferably, the dam 120 has a non-uniform width with a
narrowest portion of the dam 120 at a lip 124 adjacent the spillway
140 and most distant from the floor 114. This dam 120 has a face
122 facing the reservoir 130 which tapers non-parallel to the inner
surface of the outer wall 112 and non-perpendicular to the floor
114. The taper can be flat as depicted in FIGS. 11 and 12, or can
be concave (similar to FIG. 4) or exhibit other contours.
[0232] The angle of the face 122 is selected so that the lip 124 of
the dam 120 is further from the spin axis A than any other portions
of the face 122. This angle of the face 122 away from vertical
measures greater than zero degrees and the tube 110 has operated
successfully with the face 122 angle being five degrees. While a
range from one to ten degrees is considered optimal, face 122
angles up to about thirty degrees may be effective in some cases.
With such a configuration, higher density fractions within a sample
can migrate up along the face 122 up to the lip 124, through the
spillway 140 and into the catch basin 150. As can be seen, if the
face 122 tapered so that the lip 124 was closer to the spin axis A
than other portions of the base 122, higher density fractions would
become trapped within the reservoir 130 and full separation would
be frustrated.
[0233] A surface of the dam 120 opposite the face 122 benefits in
this embodiment from being substantially parallel with the outer
wall 112. Furthermore, the catch basin 150 is preferably rather
thin so that the catch basin 150 has a smaller volume than the
reservoir 130. Such smaller volume is particularly beneficial when
the sample being separated has a higher density fraction D (FIG. 6)
which makes up a smaller proportion of the sample K (FIG. 14) than
the lower density fraction E.
[0234] The reservoir 130 includes a supply tube 132 extending
thereinto through the cap 116. The supply tube 132 extends down to
a tip 133 from which fluids can be directed into the reservoir 130.
A plug 134 is provided for plugging the supply tube 132 outside of
the cap 116, such as to prevent discharge of fluids during
centrifugation. While the supply tube 132 is coupled to the in port
117 in the cap 116, the supply tube 132 could be used for both
introduction and removal of fluids from within the tube 110.
[0235] In one embodiment a withdrawal tube can be configured to
include a curving lower tip so that it withdraws a fraction
primarily from above a bottom end of the tip. If the tip faces
down, a false floor deflection plate can be fitted on the catch
basin so that withdrawal of constituents above such a false floor
does not capture constituents below the false floor. Such a
withdrawal tube can be particularly effective in extracting a
medium density constituent, such as a "buff coat," platelet rich
plasma or a stromal vascular fraction from adipose tissue.
[0236] The catch basin 150 includes the withdrawal tube 152
extending down from the cap 116 and in communication with the out
port 118. The withdrawal tube 152 extends down to a tip 153. This
tip 153 is preferably in a lower half of the catch basin 150 and
most preferably directly adjacent to the floor 114, with only
sufficient space to prevent blocking of the tip 153. A plug 154 can
be provided for closing off the out port 118, such as to prevent
leakage from the tube 110 during centrifugation. While the
withdrawal tube 152 and out port 118 are primarily used for removal
of fractions after centrifugation, these structures could similarly
be utilized for introduction of fluids into the tube 110.
[0237] The catch basin 150 benefits from having a constant width
and dimensions which make it significantly elongated with a height
many times greater than its width. In this manner, a relatively
small higher density fraction D (FIGS. 16 and 17) can be more
easily discerned and measured. Furthermore, the precise positioning
of a tip 153 of a withdrawal tube 152 within a fraction to be
removed can more effectively occur when the catch basin 150 has
such an elongate geometry.
[0238] In one embodiment, where it is desirable that the catch
basin 150 to have a larger volume, a lower end of the catch basin
150 is provided with a beveled lower end wall 155 (FIG. 12). In
such an embodiment, a relatively narrow upper portion of the catch
basin 150 can still be provided for precise measurement and
collection of mid-density fractions G when the sample has a
relatively large amount of higher density fraction D and lower
density fraction E, by locating the mid-density fraction G within
the narrower upper portion of the catch basin 150. With such a
beveled lower end wall 155, an angle of this beveled lower end wall
is carefully selected so that lower portions of this end wall
adjacent the floor 114 are further from the spin axis A than upper
portions of this beveled lower end wall 155. In such a way, any
lower density fraction E beginning within a bottom of the catch
basin 150 can migrate up to the catch basin 150 and over the
spillway 140 into the reservoir 130 during centrifugation, rather
than trapping lower density fractions within the catch basin
150.
[0239] With particular reference to FIGS. 13-18, details of a
method of separating a sample A into differing density fractions,
and particularly a biological sample having a higher density
fraction "pellet" D, a lower density fraction E and a mid-density
"buffy coat" fraction G are described. This method is utilized for
the preferred tube 110 in a most preferred form of this method, but
could similarly operate with other tubes 110. Initially, a syringe
S or other source of sample K is coupled to the in port 117 and the
sample K is inputted into the reservoir 130. The sample K can be
sufficiently large that some portions of the sample K also
initially migrate into the catch basin 150.
[0240] The tube 110 is then placed within the cradle C' of a
centrifuge. Plugs 134, 154 are placed within the in port 117 and
out port 118 to keep the sample K contained within the tube 110
(FIG. 15). The centrifuge is then caused to spin about the spin
axis A (FIG. 16). Initially, the sample K is still homogenous and
migrates to completely fill the catch basin 150 and only partially
fill the reservoir 130. Because the taper of the face 122 is such
that the lip 124 on the dam 120 is further from the spin axis A
then other portions of the face 122, higher density fraction D
portions of the sample K migrate up the face 122, over the lip 124,
through the spillway 140 and into the catch basin 150. Similarly,
lower density fractions E that originally start within the catch
basin 150 can migrate up out of the catch basin 150 and over the
lip 124 of the dam 120, through the spillway 140 and into the
reservoir 130.
[0241] Such centrifugation continues until separation has been
completed to the satisfaction of the user, and the higher density
fraction D is located within the lower portion of the catch basin
150, with lower density fraction E fluid contained within the
reservoir 130, and possibly upper portions of the catch basin 150.
A mid-density fraction G, such as a buffy coat, resides in a
mid-portion of the spillway 140. Due to a thinness of the catch
basin 150 and elongate form, the buffy coat G which makes up a
small percentage of the overall sample K takes up a visually
significant readily discernible portion of the catch basin 150 for
ready measurement and collection therefrom.
[0242] In particular, the tube 110 is removed and placed upright
(FIG. 17). The various different fractions of the sample remain
separated by the dam 120. The plug 154 on the out port 118 is
removed and the syringe S coupled to the out port 118. Because the
withdrawal tube 152 in this embodiment extends down to a bottom of
the catch basin 150, the syringe is used to first extract the
higher density "pellet" portion of the biological sample. This
causes the mid-density fraction G "buffy coat" to migrate down to a
bottom of the catch basin 150 and portions of the lower density
fraction E to also migrate down somewhat within the catch basin
150. Once all of the higher density fluid D has been removed, the
syringe S can be decoupled from the outport 118 for discharge of
the higher density fraction D from the syringe S for separate
collection and potential use. The syringe S is then re-coupled to
the outport 118 and further extraction through the withdrawal tube
152 causes collection of the mid-density fraction G "buffy coat" of
the biological sample for collection and use.
[0243] With such a methodology, samples having somewhat differing
prevalence of differing density fractions can be accommodated
without requiring the withdrawal tube 152 to have a precise length
which would only be suitable for certain blood characteristics. For
instance, with changes in hematocrit levels, a greater or lesser
degree of higher density fraction D "pellet" portions of the
biological sample K are present. With the tube 110 configured as
depicted in FIGS. 19-21, the buffy coat G remains within the catch
basin 150 for all biological sample hematocrit levels. By having
the withdrawal tube 152 extend down to the floor 114, the higher
density fraction D is always first removed, followed by the
mid-density fraction buffy coat G. In such a manner, similar
collection protocols can be utilized for samples having differing
characteristics and reliable separation and collection is
achieved.
[0244] This disclosure is provided to reveal a preferred embodiment
of the invention and a best mode for practicing the invention.
Having thus described the invention in this way, it should be
apparent that various different modifications can be made to the
preferred embodiment without departing from the scope and spirit of
this invention disclosure. When structures are identified as a
means to perform a function, the identification is intended to
include all structures which can perform the function specified.
When structures of this invention are identified as being coupled
together, such language should be interpreted broadly to include
the structures being coupled directly together or coupled together
through intervening structures. Such coupling could be permanent or
temporary and either in a rigid fashion or in a fashion which
allows pivoting, sliding or other relative motion while still
providing some form of attachment, unless specifically
restricted.
* * * * *