U.S. patent application number 10/430342 was filed with the patent office on 2003-11-06 for dna detector and dna detection method.
Invention is credited to Kambara, Hideki, Takahashi, Satoshi.
Application Number | 20030205472 10/430342 |
Document ID | / |
Family ID | 27526315 |
Filed Date | 2003-11-06 |
United States Patent
Application |
20030205472 |
Kind Code |
A1 |
Takahashi, Satoshi ; et
al. |
November 6, 2003 |
DNA detector and DNA detection method
Abstract
A method for determining a DNA sequence includes providing a
sample which contains first DNA fragments having adenines at an end
and labeled by first fluorophores, second DNA fragments having
thymines at an end and labeled by second fluorophores, third DNA
fragments having cytosines at an end and labeled by third
fluorophores, and fourth DNA fragments having guanines at an end
and labeled by fourth fluorophores, wherein each of the first to
fourth fluorophores is different. The sample is supplied into a
capillary and the sample is made to migrate in the capillary. A
sheath flow is formed around an end of the capillary where the
sample migrates, a light is irradiated into the sheath flow to
excite the fluorophores. Fluorescence emitted from the fluorophores
is detected and the fluorophores are identified.
Inventors: |
Takahashi, Satoshi;
(Kokubunji-shi, JP) ; Kambara, Hideki;
(Hachiouji-shi, JP) |
Correspondence
Address: |
ANTONELLI, TERRY, STOUT & KRAUS, LLP
1300 NORTH SEVENTEENTH STREET
SUITE 1800
ARLINGTON
VA
22209-9889
US
|
Family ID: |
27526315 |
Appl. No.: |
10/430342 |
Filed: |
May 7, 2003 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
10430342 |
May 7, 2003 |
|
|
|
09524269 |
Mar 13, 2000 |
|
|
|
6576108 |
|
|
|
|
09524269 |
Mar 13, 2000 |
|
|
|
09400438 |
Sep 21, 1999 |
|
|
|
6224733 |
|
|
|
|
09400438 |
Sep 21, 1999 |
|
|
|
09088849 |
Jun 2, 1998 |
|
|
|
5954932 |
|
|
|
|
09088849 |
Jun 2, 1998 |
|
|
|
08669915 |
Jun 25, 1996 |
|
|
|
5759374 |
|
|
|
|
08669915 |
Jun 25, 1996 |
|
|
|
08337412 |
Nov 7, 1994 |
|
|
|
5529679 |
|
|
|
|
08337412 |
Nov 7, 1994 |
|
|
|
08051324 |
Apr 23, 1993 |
|
|
|
08051324 |
Apr 23, 1993 |
|
|
|
08026592 |
Mar 5, 1993 |
|
|
|
5314602 |
|
|
|
|
08026592 |
Mar 5, 1993 |
|
|
|
07843232 |
Feb 28, 1992 |
|
|
|
5268080 |
|
|
|
|
Current U.S.
Class: |
204/452 |
Current CPC
Class: |
G01N 27/44721 20130101;
G01N 2035/00237 20130101; G01N 27/44782 20130101 |
Class at
Publication: |
204/452 |
International
Class: |
G01N 027/26 |
Foreign Application Data
Date |
Code |
Application Number |
Feb 28, 1991 |
JP |
3-34006 |
Sep 10, 1992 |
JP |
4-241727 |
Apr 24, 1992 |
JP |
4-106966 |
Claims
What is claimed is:
1. A method for determining a DNA sequence comprising the steps of:
providing a sample which contains first DNA fragments having
adenines at an end and labeled by first fluorophores, second DNA
fragments having thymines at an end and labeled by second
fluorophores, third DNA fragments having cytosines at an end and
labeled by third fluorophores, and fourth DNA fragments having
guanines at an end and labeled by fourth fluorophores, and each of
said first, second, third and fourth fluorophores being different;
supplying said sample into a capillary; making said sample migrate
in said capillary; forming a sheath flow around an end of said
capillary where said sample migrates; irradiating a light into said
sheath flow to excite said fluorophores; detecting fluorescence
emitted from said fluorophores; identifying said fluorophores.
2. A method for determining a DNA sequence according to claim 1,
wherein said light is irradiated into a vicinity of said end of
said capillary.
3. A method for determining a DNA sequence according to claim 1,
wherein a plurality of capillaries is provided, and said capillary
is one of said plurality of capillaries.
4. A method for determining a DNA sequence according to claim 3,
wherein different samples are supplied into each capillary of said
plurality of capillaries.
5. A method for determining a DNA sequence according to claim 3,
further comprising the step of determining a DNA sequence in each
capillary of said plurality of capillaries simultaneously.
6. A method for determining a DNA sequence according to claim 1,
wherein the step of providing a sample includes: dividing a sample
solution into four parts; making a polymerase reaction in each part
of divided sample solution, and using primers labeled by different
fluorophores for each type of terminal base; and mixing said focus
parts of said divided sample solution.
7. A method for determining a DNA sequence comprising the steps of:
providing a sample which contains a plurality of DNA fragments
labeled by a plurality of types of fluorophores; supplying said
sample into a capillary; making said sample migrate in said
capillary; forming a sheath flow around an end of said capillary
where said sample migrates; irradiating a light into said sheath
flow to excite said fluorophores; detecting fluorescence emitted
from said fluorophores; and identifying said fluorophores.
Description
[0001] This application is a continuation-in-part application of
our pending U.S. patent application Ser. No. 026,592 filed Mar. 5,
1993, which is a continuation application of Ser. No. 07/843,232
field Feb. 28, 1992, which corresponds to the Japanese Patent
Application 03-34006. Disclosures of the U.S. Patent Application
are hereby incorporated in reference.
BACKGROUND OF THE INVENTION
[0002] The present invention relates to a method of detection of
DNA and protein and of DNA base sequencing determination and to an
apparatus therefor.
[0003] It relates more particularly to the fluorescence detection
type gel electrophoresis apparatus.
[0004] For DNA base sequencing determination by electrophoresis gel
separation, a radioisotope label has been used as a label for a DNA
fragment. Due to the inconvenience of this method, however, a
method of using a fluorescence label has come to be increasingly
employed. (Refer to U.S. patent application Ser. No. 07/506,986
(U.S. Pat. No. 5,062,942) and Bio/Technology Vol 6, July 1988,
pp816-821, for example.) As an excitation light source this method
uses an argon laser with an output of 20 to 50 mw and a wavelength
of 488 nm or 515 nm to detect the DNA fragment of 10.sup.-16
mole/band to 2.times.10.sup.-18 mole/band. As fluorophores, the
method has used FITC (fluorescein isothiocyanate with a maximum
emission wavelength of 515 nm), SF (succinyl fluorescein with a
maximum emission wavelength of 510 nm to 540 nm), TRITC
(tetrarhodamine isothiocyanate with a maximum emission wavelength
of 580 nm) and Texas Red (sulforhodamine 101: a maximum emission
wavelength of 615 nm).
[0005] Normally, electrophoresis is performed with polyacrylamide
gel placed on the plate which is provided between two glass plates.
In recent years the capillary gel electrophoresis method has been
developed, where gel is formed in the capillary. Use of a capillary
having a smaller diameter increases the surface area per volume of
gel; this feature facilities the dissipation of Joule heat,
permitting application of high voltage. A high-speed
electrophoresis separation is provided by the capillary gel
electrophoresis method.
[0006] The first example of the capillary gel electrophoresis
method as a prior art is described in Nucleic Acid Research, Vol.
18. pp. 1415 to 1419 (1990), Journal of Chromatography, Vol. 516,
pp. 61-67 (1990), and-Science, Vol. 242, pp. 562-564 (1988).
Another method of using one migration lane for base sequence
determination is disclosed in Nature Vol. 321, pp. 674-679 (1986)
and others.
[0007] The above-mentioned conventional technique, however, has
disadvantages in that the sensitivity is insufficient, and the
entire equipment must be made greater in size because the Ar laser
is greater in size than a He--Ne laser.
SUMMARY OF INVENTION
[0008] The first object of the present invention is to provide a
solution to the above-said problems and to provide a method and
small-sized device in which extra-sensitive DNA detection is made
possible. To achieve the object, the present invention uses a
He--Ne laser with an emission wavelength of 594 nm in DNA base
sequencing determination by fluorescence detection type
electrophoresis gel separation, and adopts a highly efficient
photodetecting system.
[0009] The said examples of the prior art use one capillary, but
sufficient consideration has not been given to simultaneous
processing of two or more samples. In the capillary electrophoresis
apparatus, the decreasing size of the samples requires higher
detection sensitivity and simultaneous processing of two or more
samples. For fluorescence detection in the state of
electrophoresis, generally, the background from the gel, scattered
light from the inner and outer walls of the capillary as the gel
support or fluorescence from the capillary itself is produced in
addition to the fluorescence from the object fluorophore itself,
resulting in higher background level and reduced detection
sensitivity. One of the major problems in ensuring highly sensitive
fluorescence detection is how to cut off such backgrounds.
Improvement of processing capabilities and simultaneous processing
of two or more samples require an increase in migration speed, or
detection by migration of the DNA fragments through simultaneous
use of two or more capillaries which are migration lanes. In
practice, there remains a problem of how to cut off the background
to achieve highly sensitive fluorescence detection, as mentioned
above.
[0010] The second object of the present invention is to solve said
problems to provide a capillary electrophoresis apparatus and its
method which ensure fluorescence detection of two or more samples,
and high-speed highly sensitive DNA detection.
[0011] The measuring limit for the DNA fragment labeled by a
fluorophore in the process of electrophoresis gel migration is
determined by the intensity and fluctuation of the background
fluorescence from the gel with respect to fluorescence for
labeling. The background fluorescence from the gel is gradually
reduced with the increase of the emission wavelength.
[0012] Thus, the excited at the optimum wavelength, the quantity of
the fluorescence normalized by the background fluorescence from the
gel is the greatest in the case of Texas Red (sulforhodamine 101).
According to this normalized quantity of the fluorescence, the
sensitivity of the Texas Red is five to ten times that of FITC. In
the present invention, there has been used Texas Red or its
derivative as a labeling fluorophore, and a He--Ne laser with the
wavelength of 594 nm, which is close to the optimum wavelength, as
the excitation light source. The wavelength of 594 nm for the
excitation light is close to the maximum emission wavelength of the
Texas Red which is 615 nm. One of the problems was how to remove
the scattered light from the excitation light, and the present
invention has succeeded in removing this scattered light by using a
sharp-cutting fluorophore filter which will be described below. The
output from the He--Ne laser with the wavelength of 594 nm ranges
from 1 mw to 7 mw. The output from a typical model of the He--Ne
laser (594 nm) is as small as 2 mw, and greater emission strength
cannot be obtained; therefore, the detecting sensitivity greatly
depends on the fluctuation of the background fluorescence from the
gel. To solve this problem, the present invention has improved the
photodetecting system, and has adopted a photodetecting system
which receives a greater amount of light by two or more digits than
the excitation light scanning method. Namely, the excitation light
is made to be incident upon the gel plate through the side thereof,
and the entire measured area is irradiated simultaneously to
increase the overall emission strength. Furthermore, a cylindrical
lens is used to increase the photodetecting solid angle.
[0013] Changing the wavelength of the excitation light from 488 nm
to 594 nm has reduced the background fluorescence from the gel down
to approximately one fifth when the laser of the same output is
used. In addition, when the conventional argon laser (about 20 mw)
is employed, FITC is subjected to photodestruction, and this
results in reduced emission strength, and hence reduced
sensitivity. By contrast, under the 2.5 mw He--Ne laser
irradiation, photodestruction of the fluorophore hardly occurs to
the Texas Red during measurement. This permits the emission
strength normalized by the background fluorescence from the gel to
be greater by one digit than that of FITC.
[0014] In the laser scanning method, the area of 100 mm is swept by
the laser beam of approximately 0.3 mm in diameter. Even when the
conventional 50 mw laser is used, the average laser intensity with
which each point is irradiated is as small as 17 microwatts, since
the irradiation time at each point is reduced. When the 2.5 mw
laser is used, the average laser intensity is approximately 0.9
microwatts, and this almost cannot be put into practical use. The
irradiation intensity is 2.5 mw in the lateral incidence method
employed in one of the present embodiments, and this emission is
sufficient. However, in the scanning method the photodetecting
efficiency can be made approximately 2 percent, but in the
simultaneous irradiation method, the fluorescent image is received
in a reduced size; therefore the photodetecting efficiency is
reduced to 0.1 percent or less.
[0015] Defining a solid angle as .OMEGA. and the transmittance of
the filter or the like as T, the photodetecling efficiency n can be
expressed by the following formula (1): 1 = T 4 ( 1 )
[0016] Assuming the image reduction ratio as m and the f-number of
the lens as F, .OMEGA. is represented as: 2 = 4 ( m + 1 ) 2 F 2 ( 2
)
[0017] Thus, the photodetecting efficiency .eta. can be expressed
by the following formula (3): 3 = 1 16 ( m + 1 ) 2 F 2 ( 3 )
[0018] where m represents (length of the measured portion)/(length
of the detector). In the scanning method, m<1; and in the
lateral incident method, 120 cm/24 cm<m<120 cm/18 cm by way
of an example, namely m is approximately from 5 to 7. Accordingly,
the photodetecting rate of the lateral incident method is
approximately {fraction (1/50)}, because of the term of (m+1).sup.2
in formula (3), on the one hand. On the other hand, in the case of
the scanning method where light is not continuously received from
each measured point, the result is multiplied by {fraction
(3/1000)} to {fraction (5/1000)} as a factor due to duty cycle.
Thus, in total, the lateral incident method yields a greater
photodetecting efficiency than the scanning method. When the laser
having a smaller output such as a He--Ne laser is used, it is
important to find a means to obtain a sufficient photodetecting
efficiency. The present invention uses the cylindrical lens to
increase the photodetecting efficiency by, for example, four to
five times. This system provides a high photodetecting efficiency,
ensuring highly sensitive detection of the fluorescent image.
[0019] U.S. patent application Ser. No. 07/506,986 discloses the
case of using Texas Red and the He--Ne laser having a wavelength of
543 nm. Compared with the case of using the 594 nm He--Ne laser,
the excitation efficiency is as low as 1/3, and the output is also
as low as 1 mw.
[0020] To achieve the second object, in the electrophoresis
apparatus wherein samples DNA fragments, etc. labeled by the
fluorophore are subjected to separation by electrophoresis,
providing optical detection and analysis of the separated samples,
an optical detecting portion for sample detection, for which the
electrophoresis separation region provided between the vessel for
cathode electrode and vessel for anode electrode is composed of
capillaries, has the following configurations.
[0021] In the configuration (1) of said optical detecting portion;
the ends of said one pair or more pairs of capillaries are
connected to said vessel for cathode or anode electrode, and the
other ends are held at a specified gap, with their axes almost
matched to each other, and are laid face to face with each other in
the optical cell to form a migration lane which passes through said
optical cell; sheath solution is supplied into said optical cell
from the outside; the sample migrated from the capillary end of the
upstream migration lane, namely, the sample separation region, is
put in the sheath flow condition, and is then lead into the
downstream capillaries laid out face to face; while said gap is
used as an optical detecting portion, and light from the light
source is shed on this optical detecting portion, thereby detecting
the samples. In this configuration (1), two or more detecting
portions formed by two or more pairs of capillaries are laid out in
the optical cell. Furthermore, two or more pairs of capillaries are
arranged in the optical cell so that two or more detectors formed
by two or more pairs of capillaries are located in a straight line,
and the excitation light is shed along said straight line so that
all the optical detecting portions are simultaneously irradiated,
thereby ensuring simultaneous detection of the fluorescence at said
two or more optical detecting portions.
[0022] In the configuration (2) of the optical detecting portion;
two or more capillaries, the other ends of which are immersed in
the electrode vessel, are terminated in the optical cell, and
sheath solution is supplied into said optical cell from the
outside. Thus, the samples migrating from capillaries are made to
flow in the optical cell in the sheath flow condition. Using the
sheath flow region as the optical detecting portion, light is
irradiated on the optical detecting portion, thereby detecting the
samples. In this configuration (2), two or more capillaries are
laid out in the optical cell so that two or more optical detecting
portions are located in a straight line, and the excitation light
is shed along said straight line so that all the optical detecting
portions are simultaneously irradiated, thereby ensuring
simultaneous detection of the fluorescences issued from the samples
migrating from capillaries.
[0023] In configurations (1) and (2), the following configuration
is also possible.
[0024] The sample separation region is composed of the capillary
gel, and the sheath solution has the same components as those of
the buffer solution inside the capillaries. The denaturant for the
sample may be contained as required. The sheath solution level is
positioned higher than the liquid level in the downstream electrode
vessel, and the sheath solution is made to flow by the head of two
liquids.
[0025] In the configuration (3) of the optical detecting portion;
two or more capillaries, the other ends of which are immersed in
the electrode vessel, are terminated in the optical cell filled
with electrolyte. The optical detecting portion belongs to the
region close to the terminal to which the samples migrate from the
capillary gel as migration lane. The optical detecting portion
filled with electrolyte is formed as follows: two capillaries are
laid out in a straight line with their axes almost matched to each
other, and the ends laid face to face with each other are placed in
close contact with each other in the axial direction of the
capillary, while maintaining a specified gap. In this case, samples
are subjected to electrophoresis separation inside one of the
capillaries located in the upstream side of the migration lane,
while the gap serves as optical detecting portion to detect the
fluorescence emitted by samples. The gap length is preferred to be
1 mm or less. The two or more optical detecting portions formed by
two or more pairs of capillaries are linked with each other by the
electrolyte. Two or more optical detecting portions are arranged in
a straight line, and a single excitation light is shed along this
straight line, ensuring simultaneous detection of the fluorescences
issued from the two or more samples.
[0026] In the electrophoresis apparatus provided with optical
detecting portion according to said configuration (1), sheath
solution is supplied into the optical cell from the outside, so
samples migrating from the capillary end in the migration lane on
the upstream side where the samples are separated can be led to the
capillaries facing each other in the sheath flow condition, and
samples migrate continuously in capillaries on the upstream side
and those on the downstream side. Furthermore, the samples migrate
smoothly in the gap on the axis between the capillaries on the
upstream side and those on the downstream sides. This gap is used
as the optical detecting portion. Light can be irradiated on the
optical detecting portion in the sheath solution containing no
capillaries, detecting the samples by fluorescence. This eliminates
the possibility of backgrounds being emitted from capillaries or
capillary gels, ensuring highly sensitive fluorescence detection.
It allows use of the rectangular optical cell which can be
manufactured easily at lower cost. Two or more optical detectors
can be arranged in close proximity with each other in the optical
cell, resulting in substantial reduction of the system size.
Samples migrating from the capillaries are put into sheath flow
condition for each capillary when passing through the optical
detecting portion, and sheath flow is all put under the same
conditions. Sheath flow conditions such as flow speed are made
uniform for each capillary, resulting in improved accuracy in
optical detection of samples. Two or more optical detecting
portions are arranged in a straight line in one optical cell, and
excitation light is irradiated along this straight line, permitting
simultaneous irradiation of all optical detecting portions and
simultaneous fluorescence detection by two or more optical
detecting portions. Furthermore, two or more optical detecting
portions are linked with each other through the solution, so the
excitation light is not bent by capillaries, and the excitation
light intensity is not damped. This allows irradiation of the
optical detecting portions with sufficient light intensity,
providing high-precision highly sensitive fluorescence detection.
Use of the two-dimensional TV camera, etc. for light detector
permits simultaneous photodetection of the fluorescent images of
two or more optical detecting portions. Two or more optical
detecting portions can be positioned in close proximity with each
other in a straight line, and the length between the optical
detecting portions on the extreme ends of this straight line can be
reduced, permitting configuration of the smaller apparatus. Reduced
distance between optical detecting portions located on the extreme
ends will allow all optical detecting portions to be irradiated in
almost the same light beam diameter, even when the excitation light
is condensed by the lens or the like.
[0027] For example, when the laser light is condensed to 100 .mu.m
in terms of the focal point, the laser light diameter will be about
100 .mu.m over the range of about 10 mm on the front and rear of
the focal point. When capillaries having an outer diameter of 200
.mu.m and inner diameter of 100 .mu.m are arranged at the intervals
of 400 .mu.m, about 50 capillaries can be installed within the
range of about 10 mm on the front and rear of the focal point, and
they can be irradiated with the equivalent light beam diameter and
intensity. This allows the optical detecting portions to be
irradiated with the excitation light condensed, and the
fluorescence intensity to be increased, thereby ensuring highly
sensitive detection of the sample.
[0028] Moreover, it is also possible to make the downstream
capillaries hollow (i.e. open capillaries), allowing effective
flowing of the sheath solution. In addition to the capillaries, it
is also possible to use on the downstream side something that
performs the equivalent operations, for example, the plate provided
with holes and grooves in the same number as that of the upstream
capillaries. The flow of electricity at the gap (namely, the
optical detecting portion) can be ensured by making the sheath
solution have the equivalent components as that of the buffer
solution within the capillary, thereby providing electrophoresis of
samples. Furthermore, because the buffer solution has the same
components both inside and outside the capillary, there is no
possibility of the buffer solution inside the capillary flowing out
into the optical cell causing their composition to be changed.
Therefore, the sample separation function in electrophoresis is not
lost. When the samples are single-strand DNAs, denaturant can be
contained in the sheath solution, and it is possible to avoid
rebonding when DNA samples migrates in the gap (namely, the optical
detecting portion); this means improved detection accuracy. This
feature reduces the possibility of the denaturant contained in the
capillary leaking out into the optical cell, and eliminates the
loss of sample separation function.
[0029] The gap length is preferred to be 0.1 mm to 3.0 mm.
Generally, the smaller gap length provides easier electrophoresis
of the samples in the gap space, so the space distance should be
short. However, assembling of the apparatus is more difficult if
the gap length is very small; therefore, it is preferred to be 0.1
mm or more in practice. However, it can be set to 0.1 mm or less.
The limit is determined by the size of the excitation beam such as
laser light at the gap. Conversely, greater gap length will cause
easier dispersion of the samples. The gap length of about 3.0 mm
allows normal electrophoresis of the-samples on the line connecting
between capillaries.
[0030] In the electrophoresis apparatus provided with optical
detecting portion according to said configuration (2), samples
migrating in the capillaries flow in the optical cell in the sheath
flow state. By using the sheath flow region as optical detecting
portion and the same configuration as that of (1), it is also
possible to detect separately the samples migrating in the
capillaries, thereby obtaining the same results as configuration
(1). The layout of the optical detecting portion and irradiation of
the excitation light discussed in connection with the configuration
(1) are the same for configuration (2).
[0031] In the configuration (3.) of the electrophoresis apparatus;
samples are detected in the electrolyte without containing any gel,
eliminating the possibility of backgrounds being emitted from gel
supports such as the capillaries, ensuring highly sensitive
fluorescence detection. Moreover, it eliminates the need of making
the electrolyte, and provides simple configuration of the
apparatus. The gap is used as optical detecting portion to detect
the fluorescence of samples; it is also filled with electrolyte,
permitting electrophoresis. Since gel is produced in at least one
of the capillaries, formation of the migration lane is facilitated.
The preferred gap length is 0.1 mm to 1 mm. Generally, the smaller
gap length provides easier electrophoresis of the samples in the
gap space, so the space distance should be short. However,
assembling of the apparatus is more difficult if the gap length is
very small; therefore, it is preferred to be 0.1 mm or more in
practice. However, it can be set to 0.1 mm or less. The limit is
determined by the size of the excitation beam such as laser light
at the gap.
[0032] Conversely, greater gap length will cause easier dispersion
of the samples without migrating in a straight line in the gap;
samples will not migrate in the others of the paired capillaries.
The gap length of about 2 to 3 mm allows normal electrophoresis of
the samples; however, normal electrophoresis may take place,
depending on the conditions such as electrophoresis voltage. The
gap length of about 1 mm is preferred in practice. That is, the gap
length of 0.1 mm to 1.0 mm allows smooth and effective
electrophoresis of the samples. Two or more optical detecting
portions can be positioned in a straight line, and a single
excitation light can be irradiated simultaneously on two or more
optical detecting portions for fluorescence detection. Furthermore,
two or more optical detecting portions are linked with each other
through the solution, so the excitation light is not damped. This
allows irradiation of the optical detecting portions with
sufficient light intensity, providing high-precision highly
sensitive fluorescence detection.
[0033] To summarize the present invention, one or more samples are
subjected to electrophoresis separation using the plate gel and
capillary gel, and two or more migration lanes are irradiated
linearly by the laser from the direction which is almost
perpendicular to the migration direction for samples and which is
parallel to the surface formed by two or more migration lanes,
thereby providing real-time detection of the fluorescence emitted
from the fragments migrating in the migration lane. The present
invention relates especially to the fluorescence detection type
electrophoresis apparatus provided with the optical cell which is
intended for highly sensitive fluorescence detection of the DNA
fragments labeled by fluorophores, wherein one pair or more pairs
of capillary filled with gel and capillary are arranged in the
optical cell so that they are coaxial with each other and a
specified gap length is maintained. The sheath solution is poured
into the optical head by the cell and the samples migrating in the
gap are put in the sheath flow condition. Fluorescence detection is
performed in the gap free of capillary or gel. Or the buffer
solution is poured in the optical cell, and the gap is filled with
buffer solution, thereby forming the migration lane through the
gap, which is used for fluorescence detection using sulforhodamine
101 or rhodamine derivative as fluorophore, He--Ne laser light
having an emission wavelength of 594 nm is irradiated along the
straight line in which two or more gaps are arranged; then the
fluorophore is excited to permit fluorescence detection. Since the
fluorescence detection is performed in the gap free of capillary or
gel, it is possible to obtain a small type electrophoresis
apparatus which provides simultaneous electrophoresis of two or
more samples and their simultaneous detection, thereby ensuring
highly sensitive fluorescence detection, free from background
influence.
BRIEF DESCRIPTION OF THE DRAWINGS
[0034] FIG. 1 is a schematic view representing the DNA detector as
the first embodiment of the present invention;
[0035] FIG. 2 is a graph representing the spectrum in the
electrophoresis separation of the DNA fragment which is obtained by
letting the A phage be digested by the restriction enzyme and by
inserting the fluorescence label into the cut portion;
[0036] FIG. 3 is a block diagram representing the electrophoresis
region and laser irradiation system of the electrophoresis
apparatus according to the second Embodiment of the present
invention;
[0037] FIG. 4 is a block diagram representing the fluorescence
detection system of the electrophoresis apparatus according to the
second Embodiment of the present invention;
[0038] FIG. 5 is a block diagram representing the electrophoresis
region and laser irradiation system of the electrophoresis
apparatus according to the fourth Embodiment of the present
invention;
[0039] FIG. 6 is a block diagram representing the electrophoresis
region and laser irradiation system of the electrophoresis
apparatus according to the fifth Embodiment of the present
invention;
[0040] FIG. 7 is an oblique view representing the plate provided
with two or more grooves according to the sixth Embodiment of the
present invention;
[0041] FIG. 8 shows the optical cell of the electrophoresis region
of the electrophoresis apparatus according to the sixth Embodiment
of the present invention;
[0042] FIG. 9 is a block diagram representing the electrophoresis
apparatus according to the seventh Embodiment of the present
invention;
[0043] FIG. 10 is an enlarged view representing the optical cell
according to the seventh Embodiment of the present invention;
[0044] FIG. 11 is a block diagram representing the electrophoresis
apparatus according to the eighth Embodiment of the present
invention; and
[0045] FIG. 12 is an enlarged view representing the optical cell
according to the ninth Embodiment of the present invention;
DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0046] The following gives detailed description of the present
invention with reference to embodiments:
[0047] [Embodiment 1]
[0048] First embodiment of the present invention will be described
with reference to FIGS. 1 and 2. FIG. 1 is a schematic view
representing the detector. Light emitted from the 594 nm He--Ne
laser 1 irradiates the electrophoresis separation gel plate 4 from
the side. After being collected by the cylindrical lens 7, the
fluorescence emitted from the linearly irradiated portion is
filtered out by the band pass filter 6, and forms images on the
line sensor or secondary detector 8 through the lens for image
formation 5. Filter 6 is a 6-cavity multilayer interference filter
with a diameter of 50 mm, and transmittances for light having
wavelengths of 594 nm, 600 nm, 610-630 nm and 640 nm are 10, 10,
0.6 or more, and 0.01 or less, respectively.
[0049] The concentration of the acrylamide gel constituting the gel
plate 4 (concentration of the total quantity of monomer) is 4 to 6
percent (g/cc). When irradiated by the He--Ne laser with the
wavelength of 594 nm, the background fluorescence from the gel has
the same intensity as the fluorescence from Texas Red having a
concentration of 2.times.10.sup.-11 mole. The laser power is 2.5 mw
and the beam diameter is 0.3 mm. The positional resolution on the
linearly irradiated portion of 0.5 mm is sufficient. In FIG. 1, the
reference numeral 2 denotes a reflection mirror, 3a glass plate
sandwiching the gel plate 4 sandwiched, 9a control circuit, and 10a
data processor. The number of the photons I of the fluorescence
emitted from the 0.5 mm-long area irradiated by the laser beam can
be obtained from the following formula:
I.about.I.sub.0.multidot..phi..multidot.[1-e.sup.-1M].about.I.sub.0.phi..e-
psilon.1M (4)
[0050] where I.sub.0 denotes the number of incident photons, .phi.
denotes a quantum yield of the fluorophore, .epsilon. denotes a
molar absorption coefficient, 1 denotes a optical path length and M
denotes a mole concentration of the fluorophore. The number of the
photons emitted from the 2.5 mw laser per second (namely, I.sub.0)
is approximately 10.sup.16. When Texas Red of approximately 0.4 in
.phi. is irradiated with the light having the wavelength of 594 nm,
the absorption coefficient of Texas Red C is approx.
8.times.10.sup.4 cm.sup.-1(M).sup.-1, 1 is approx. 0.05 cm, and the
concentration M of Texas Red showing the same level of fluorescence
as that of the gel is approx. 2.times.10.sup.-11 moles/l. The
number of photons I from Texas Red which emits the same amount of
the fluorescence as that of background fluorescence from the gel is
estimated to be approximately 3.times.10.sup.8 per second.
[0051] When a 10 cm area is scanned by the laser beam, the duty
cycle is 0.5/100. Therefore, the average number of photons emitted
from the 0.5 mm-long area is 1.5.times.10.sup.6 per second. Even
when the lens having a greater F-value is used to receive light,
the photodetecting efficiency is 1 to 2 percent when consideration
is given to the filter transmittance (approximately 50%). When
consideration is given to the quantum yield (approximately 5%) on
the photodetecting surface, the number of photons to be received is
1000 per second or less. Thus, the scanning method fails to provide
high-precision measurement.
[0052] In the lateral incident method proposed in the present
invention, however, the duty cycle is 1.0, but since the reduced
image is formed on the detector, the photodetecting efficiency is
as small as approx. 0.05%. The number of protons emitted from the
0.5 mm-long area which enter the detector is approx.
7.5.times.10.sup.3 per second when the quantum efficiency on the
photodetecting surface and losses due to various factors are taken
into consideration. The detection sensitivity is determined by the
fluctuation of the background fluorescence to be measured.
[0053] In this case, the statistical fluctuation is approximately
.+-.1.2 percent. Generally, the relative value of the fluctuation
is reduced with the increase of the photodetecting quantity, and
even a slight signal can be measured. If the photodetecting
quantity is increased by N times, the relative fluctuation is
reduced to .+-.1/{square root}{square root over (N)}. For example,
when the photodetecting quantity is increased by four times, the
relative fluctuation is reduced by one half. To ensure highly
sensitive detection, the above-said fluctuation of approx. .+-.1.2%
must be further reduced, and the is photodetecting quantity must be
increased.
[0054] To realize this, the present invention uses a cylindrical
convex lens (focal distance f=25 mm, f-number F=1.0) which is
installed at a position approximately 25 mm away from the
irradiation section, and a cylindrical concave lens (f=-200 mm)
which is placed immediately before the lens for image formation so
that the image in the vertical direction will be formed in an
enlarged size; hence the photodetecting solid angle has been
increased four to five times. This has increased the photodetecting
quantity by four to five times, and has reduced fluctuation by half
down to approximately .+-.0.6% of the fluorescence emitted from the
gel, thereby ensuring a highly sensitive detection capability.
Namely, this detection system permits detection of Texas Red of
2.times.10.sup.-13 moles/l at an S/N ratio of approximately 1.
[0055] When the argon laser is used as an excitation light source,
and Texas Red is used as a labeling fluorophore, the excitation
efficiency is reduced by one digit compared with that of the
present embodiment, and the sensitivity is also reduced undesirably
by one digit. When the argon laser is used as an excitation light
source, and FITC is used as a labeling fluorophore, the background
fluorescence is increased by one digit compared with that of the
present embodiment, and the labeling fluorophore is subjected to
photodestruction during the measurement so that the effective FITC
concentration is reduced. As a result, the sensitivity is also
reduced undesirably by-two digits compared with that of the present
embodiment.
[0056] FIG. 2 represents an electrophoresis separation pattern of
the fragment which is digested by the enzyme wherein the terminal
of the .lambda. phage is labeled by Texas Red and the He--Ne laser
of 594 nm wavelength is employed. The cubic volume of the DNA band
is estimated at 1 .mu.l, and it is possible to read the signal from
the sample which is injected 2.times.10.sup.-19 moles.
[0057] By contrast, the quantity of the sample for which the signal
can be read is 1.times.10.sup.-17 moles per band in the
conventional case of using FITC and the argon laser, and is
2.times.10.sup.-18 moles per band in the conventional case of using
Texas Red and the argon laser.
[0058] The following Table shows the comparison between an example
of the He--Ne laser used in the present invention and an example of
the argon laser used in the conventional case. This reveals that
the He--Ne laser is smaller in size, lighter in weight and usually
less costly than the argon laser.
1 He--Ne-laser Argon laser Size (cm) Weight (kg) Size (cm) Weight
(kg) Power supply 8 .times. 15 .times. 15 2 15 .times. 40 .times.
30 20 Resonator 7 (dia.) .times. 4 2 15 .times. 15 .times. 35
10
[0059] Thus, the DNA detector of the present invention features not
only a higher sensitivity but also a smaller size than the
conventional device.
[0060] As described above, according to the present invention,
Texas Red or rhodamine derivatives having an emission band in the
long wave area of less background fluorescence from the gel can be
effectively excited by the yellow He--Ne laser with the wavelength
of 594 nm, so that this characteristic ensures a higher sensitivity
and a smaller configuration.
[0061] [Embodiment 2]
[0062] In the present Embodiment, DNA fragments labeled by
fluorescence are separated by electrophoresis and detection is made
by fluorescence. The following describes the case of using Texas
Red (Sulforhodamine 101, maximum emission wavelength of 615 nm) as
labeling fluorophore. The DNA fragments as samples are labeled by
fluophores. DNA fragments labeled by fluorophores are prepared by
DNA polymerase reaction, using the primer labeled by fluorophore
according to the well-known dideoxy sequencing method invented by
Sanger and his colleagues. The details of the method of preparing
samples according to Sanger's dideoxy sequencing method are
described in the Embodiment 3.
[0063] Firstly, the apparatus configuration will be described. FIG.
3 shows the electrophoresis region and laser irradiation system of
the electrophoresis apparatus according to the present Embodiment.
FIG. 4 represents the fluorescence detection system of the
electrophoresis apparatus. The electrophoresis apparatus includes
an arrangement of 20 capillaries serving as the electrophoresis
region to perform simultaneous detection of two or more samples.
The electrophoresis separation region uses 20 silica-made
capillaries 1a, 1b, 1c, 1d . . . 1t, all having the same form; an
inner diameter of 100 .mu.m, outer diameter of 375 .mu.m and length
of 40 cm, as well as 20 silica-made capillaries 2a, 2b, 2c, 2d . .
. 2t, having the same inner and outer diameters but a length of 10
cm.
[0064] The capillary gel is produced by filling capillaries 1a to
1t with polyacrylamide gel containing the denaturant urea. Firstly,
the capillary interior is washed and is subjected to silane
coupling treatment. Then solution of
N,N,N',N'-tetramethylethylendiamine and ammonium persulfate is
added to the degassed TRIS-borate buffer containing 3.84 percent of
acrylamide, 0.16 percent of N,N'-methylene bis-acrylamide, 7 M of
urea, and 2 mM of EDTA, and is poured into the capillaries; then
polyacrylamide gel is obtained by polymerization. Polyacrylamide
gel and capillaries are chemically bonded with each other, and the
gel does not come out of the capillaries during
electrophoresis.
[0065] Capillaries 2a to 2t are treated so that their inner
surfaces are positively charged. Firstly,
3-(2-aminoethylaminopropyl) trimethoxysilan solution is poured into
capillaries to cause reaction. It is then heat treated at the
temperature of 110.degree. C., and amino acid residue is introduced
on the inner walls of the capillaries to be positively charged.
This changes the direction of the electroosmotic flow from negative
to positive poles inside each of capillaries 2a to 2t.
[0066] The migration direction (from negative to positive poles) of
samples in capillaries 1a to 1t filled with polyacrylamide gel is
matched to the migration direction (from negative to positive
poles) of samples in capillaries 2a to 2t, ensuring the sample
migration. The ends of capillaries 1a to 1t and capillaries 2a to
2t are placed face to face in the optical cell, and are held at a
specified gap; then samples migrating in these gaps are detected
optically. According to the present invention, the fluorescent cell
is used to detect the samples by fluorescence. That is, the ends of
said capillaries 1a to 1t and capillaries 2a to 2t are placed
inside the rectangular quartz optical cell 104a (outer dimensions:
36 mm wide by 4.5 mm deep by 3 mm long; inner dimensions: 30 mm
wide by 2 mm deep by 3 mm long); where width denotes the horizontal
direction of the drawing (direction of capillaries 1a-->1t), the
depth the perpendicular direction of the drawing, and the length
the longitudinal direction (direction of samples migrating in
capillaries) of the drawing. They are arranged so that a pair of
capillary 1a and capillary 2a will be coaxial with each other, and
that they will face each other forming the gap 3a having a length
of 1 mm. Likewise, capillaries 1b and 2b, 1c and 2c, 1d and 2d . .
. 1t and 2t are arranged so as to form gaps 3b, 3c, 3d . . . 3t.
Gaps 3b, 3c, 3d . . . , 3t are arranged in a straight line at a
specified interval. To hold the capillaries in the optical cell,
use is generally made of the multi-capillary holder having 20
vertical holes at intervals of 0.6 mm provided on the plate-formed
block made of fluorine-contained polymer, for example,
tetrafluoroethylene polymer. Namely, each of capillaries 1a to 1t
is inserted in each of 20 vertical holes of multi-capillary holder
5a; then each of capillaries 2a to 2t is inserted in each of 20
vertical holes of multi-capillary holder 5b. The multi-capillary
holder 5a and multi-capillary holder 5b are fixed in close contact
with the top and bottom of optical cell 104a to ensure that
capillaries 1a and 2a, 1b and 2b, 1c and 2c, 1d and 2d . . . 1t and
2 are respectively coaxial.
[0067] Furthermore, since the gaps 3a to 3t are used as optical
detecting portions, adjustment is made of the length of capillaries
1a to 1t and 2a to 2t inside the optical cell 104a so that gaps 3a
to 3t are laid out in a straight line. The other ends of the
capillaries 1a to 1t and 2a to 2t are immersed in a vessel for
cathode electrode 106 and a vessel for anode electrode 107 supplied
with buffer solution (TRIS-borate-EDTA buffer solution with urea).
The inside of optical cell 104a is provided with sheath inlet 108
to be filled with sheath solution, so that sheath solution 11 in
the sheath solution bottle 100 can be supplied through the
tetrafluoroethylene polymer tube 109. Sheath solution 11 uses the
TRIS-borate-EDTA buffer solution with urea, having the same
composition as that of the buffer solution inside the capillary gel
of capillaries 1a to 1t, thereby preventing the components of the
capillary gel from leaking into the optical cell 104a.
[0068] Furthermore, if optical cell 104a incorporating capillaries
1a to 1t and capillaries 2a to 2t is filled with sheath solution
and the level of sheath solution 11 of sheath solution bottle 100
is made higher than that of the buffer solution in the vessel for
anode electrode 107, then sheath solution flows into the vessel for
anode electrode 107 through capillaries 2a to 2t. Under this
condition, optical cell 104a and capillaries 2a to 2t are filled
with sheath solution, namely, buffer solution, and capillaries 1a
to 1t are also filled with capillary gel. If the DC voltage is
applied between the vessel for cathode electrode 106 and the vessel
for anode electrode 107 by DC high voltage power supply 12, then
current will flow through capillary 1a, gap 3a and capillary 2a,
allowing the samples to migrate. When the level of sheath solution
11 of sheath solution bottle 100 is made higher than that of the
buffer solution in the vessel for anode electrode 107, sheath
solution flows inside the capillaries 2a to 2t, producing the flow
over the tops of the capillaries 2a to 2t, namely, around gaps 3a
to 3t. Samples migrating from capillaries 1a to 1t pass through
gaps 3a to 3t along the flow over capillaries 2a to 2t under the
sheath flow conditions, are led into each capillary and made to
migrate toward the vessel for anode electrode 107.
[0069] Capillaries 2a to 2t are treated so that their inside will
be positively charged, and electroosmotic flow inside the
capillaries 2a to 2t is directed from capillaries 1a to 1t vessel
for anode electrode 107, eliminating the possibility of reserve
flow of the solution into gaps, and ensuring stable flow of sheath
solution toward the vessel for anode electrode 107. Even when the
flow rate of sheath solution is especially low, stable flow of
sheath solution toward the vessel for anode electrode 107 is
ensured.
[0070] Electrophoresis is performed by application of DC power
between the vessel for cathode electrode 106 and the vessel for
anode electrode 107 by means of DC high voltage power supply 12.
The current flowing through capillary 1a and capillary 2a goes
mainly through gap 3a; likewise, the current flowing through
capillaries 1b and 2b, 1c and 2c, 1d and 2d, . . . 1t and 2t goes
mainly through 3b, 3c, 3d . . . 3t. Furthermore, as discussed
above, the samples migrating from capillaries 1a to 1t flow along
the stream over capillaries 2a to 2t, passing though the gaps 3a to
3t under the sheath flow condition; then they are led into
respective capillaries. Namely, samples migrating through the
capillaries and gaps are made to migrate without contacting the
samples migrating in the adjacent gaps. This permits fluorescence
detection of the samples migrating in each gap, without being
affected by the samples migrating in the neighboring gaps. In
addition, the samples do not contact the inner surface of optical
cell 104a; this feature eliminates the influence of the samples
being absorbed to the optical cell 104a, and provides spatial
removal of the scattered light on the surface of the optical cell
104a by means of slits or similar device. Thus, highly sensitive
fluorescence detection is possible.
[0071] Introduction of the DNA fragments labeled by fluorophores is
made possible by immersing one end of the capillary 1a on the
cathode side into the sample solution, and by application of the 6
kV-voltage between the sample solution and the vessel for anode
electrode 107 for about 20 seconds. After that, the end of the
capillary is put back to the original position of the vessel for
cathode electrode 106. This procedure is repeated for each of
capillaries 1a to 1t, to supply samples into the capillary gels of
capillaries 1a to 1t. Note that samples may be supplied to each
capillary in sequence, as described above, or they may be supplied
by immersing each of capillaries 1a to 1t into the sample solution
and by simultaneous application of voltage. The samples poured in
each of the capillaries 1a to 1t are made to move from the cathode
to anode by application of the 6 kV-voltage between the vessel for
cathode electrode 106 and the vessel for anode electrode 107 inside
the capillary gels of the capillaries 1a to 1t, and pass through
gaps 3a to 3t. Samples passing through gaps 3a to 3t are detected
by irradiating He--Ne laser light having a wavelength of 594 nm to
excite the Texas Red (Sulforhodamine 101) which is a labeling
fluorophore. The laser light is adjusted so that the laser light
irradiates gaps 3a to 3t arranged in a straight line simultaneously
or under much the same conditions (laser light diameter), and the
laser light is irradiated, thereby permitting fluorescence to be
detected. Namely, laser light 21 having a wavelength of 594 nm of
the He--Ne laser source 20 is condensed by lens 22 and irradiated
to excite the DNA fragments labeled by fluorophores passing through
gaps 3a to 3t. The laser having a beam diameter of about 0.7 mm,
and the lens 22 having a focal distance of 100 mm are used, and the
focus is set to the mid-position between gaps 3a and 3t. In this
case, spot size of the laser light at the focal point is about 150
.mu.m, and focal depth is about 20 mm. The distance between gap 3a
and 3t is equal to the distance from capillary 1a to capillary 1t.
In the case of the present embodiment, it is 0.6 mm by 19, namely
about 12 mm. That is, the laser light irradiates 20 positions of
the gaps 3a to 3t with much the same spot size, which is much the
same as that of the capillary gel (100 .mu.m). As discussed above,
the spot size of the laser light can be much the same as that of
the capillary gel. Uniform and efficient excitation of the DNA
fragments labeled by fluorophores which migrate through gaps 3a to
3t by selecting the light source and lens system so that all gaps
are irradiated with much the same spot size.
[0072] The fluorescence emitted from the DNA fragments labeled by
fluorophores which migrate through gaps 3a to 3t is detected from
the position perpendicular to the direction of laser irradiation.
This configuration is illustrated in FIG. 4. After the background
such as scattered light has been eliminated through interference
filter 32, fluorescence 30 emitted from the DNA fragments, and
forms the image on two-dimensional detector 34 such as CCD camera
through lens 33. Being controlled by controller 35, two-dimensional
detector 34 detects the fluorescent image of gaps 3a to 3t, and
provides continuous and simultaneous detection of the change of the
fluorescence intensity according to all gaps 3a to 3t, using data
processor 36 of the computer or the like. These results are
displayed on monitor 37, and are output on printer 38 or stored in
memory 39. This feature permits simultaneous and continuous
detection of migration patterns for each of capillaries 1a to it.
Note that, in the case of the present embodiment, the
one-dimensional detector such as a photodiode array can be used,
instead of the two-dimensional detector such as a CCD camera, since
the fluorescent images of the gaps are arranged on the
one-dimension basis. For effective detection of the fluorescence
emitted from the Texas Red, interference filter 32 uses the band
pass interference filter which permits transmission of a wavelength
band ranging from 610 to 630 nm.
[0073] The magnification of the lens is set so that the image of
gaps 3a to 3t will be condensed on the photo-detecting surface of
the two-dimensional detector. In the configuration shown in FIG. 4,
fluorescence from the linear laser irradiation region may be
collected by the cylindrical lens, as in the case of Embodiment 1,
for which the fluorescence detection system shown in FIG. 1. Since
the gaps are filled with buffer solution in the present embodiment,
the laser light irradiates gaps, without being affected by
scattered light of the capillaries. This permits simultaneous,
homogenous and efficient irradiation of samples migrating through
two or more capillaries. It leads to substantial reduction of such
background as scattered light and fluorescence from capillaries and
capillary gels, ensuring highly sensitive fluorescence detection.
The effect of reducing the background light is described: Compared
with the case where fluorescence detection is made by shedding the
laser light on the capillary itself the coating of which is
removed, for example, fluorescent detection made at the gap as in
the present embodiment reduces the detected background intensity to
about one tenth or less, permitting detection of samples with
smaller concentration. Arrangement of two or more gaps in a
straight line enables simultaneous and simple irradiation of all
gaps by the laser light, allowing simple apparatus configuration.
Since two or more pairs of capillaries can be held in one optical
cell, only one tube is sufficient for supply of sheath solution.
Sheath flow occurs only at the position close to the gaps, flow
rates are the same for all gaps, resulting in greater
reproducibility. The optical cell according to the present
embodiment has a simple structure; it is not necessary to use the
optical cell of complicated configuration as found in the sheath
flow chamber. In the present embodiment, the sample migration
position can be determined by holding a pair of capillaries face to
face with each other at a specified gap, and two or more
capillaries (the space between the adjacent capillaries set at 0.6
mm in the present embodiment) can be laid out at positions close to
each other. This allows reduction in the size of the optical cell.
This also makes it possible to reduce the laser light further to
irradiate two or more gaps. Excitation light density is increased,
and fluorescence measurement is facilitated.
[0074] According to the present embodiment, buffer solution can be
made to flow without using the mechanical means such as a liquid
chromatography pump. This simplifies the apparatus configuration,
and reduces the production cost. There is no pulsating flow which
may occur when the pump is used; this ensures a stable flow of
sheath solution and reduced feed rate variation, and reduced
variations of fluorescence intensity of samples flowing in the
gaps, resulting in detection accuracy. The flow rate of sheath
solution can be easily adjusted by changing the head between the
sheath solution level in the sheath solution bottle and buffer
solution level in the vessel for an anode electrode on the
downstream side for migration. This adjustment is also possible by
changing the inner diameter of the capillary on the downstream side
for migration. It is possible to make the sheath solution flow by
using a mechanical means such as a liquid chromatography pump. In
this case, the advantage is that the flow rate can be set directly.
However, fluorescent intensity Lends to change due to pulsating
flow of the pump, so such treatment as smoothing in data processing
is essential.
[0075] The sheath solution in the optical cell passes through
capillaries 2a to 2t on the downstream side and flows out of the
cell. Since the capillary generally has a small inner diameter, the
flow rate at the capillary is generally small. Therefore, the
volume of the sheath solution can be reduced, resulting in improved
maneuverability. In the present embodiment, processing is made to
ensure that the interior of capillaries 2a to 2t is positively
charged, that the electroosmotic flow inside the capillaries 2a to
2t is directed toward the vessel for anode electrode, and that
there is no reverse flow from capillaries 2a to 2t to the gaps.
This ensures a stable flow of the sheath solution to vessel for
anode electrode even when the flow rate of the sheath solution is
small. If the inner diameter of capillaries 2a to 2t is great and
the flow rate of the sheath solution in the gap is increased, the
effect of the electroosmotic flow is reduced; as a result,
treatment of the inner sides of capillaries 2a to 2t is not
necessary.
[0076] In the present embodiment, sheath solution and buffer
solution in the vessel for a cathode electrode and the vessel for
an anode electrode use the same components as that of the buffer
solution of the capillary gel. This prevents the capillary gel
components from leaking into optical cell 104a or the electrode
vessel, and permits reuse of the capillary gel, resulting in stable
electrophoresis featuring high separative power. It is also
possible to use the buffer solution which does not contain urea,
namely, DNA denaturant, but urea inside the capillary gel may flow
out from the capillary gel into the electrode vessel and
fluorescent cell with the lapse of time. In this case,
electrophoresis is possible as in the case of the buffer solution
containing urea; however, the frequency of repeated use will reduce
to some extent.
[0077] The used laser light source and fluorophores are not
restricted to He--Ne laser and Texas Red (Sulforhodamine 101); any
fluorophores and any suitable laser light source can be used. The
present embodiment has been described based on the detection of the
DNA fragments, but the principle applies to the analysis of the
protein and similar substances. In the present embodiment, two
capillaries having the same inner diameters have been used; a
combination of different inner diameters is also possible. For
example, if the inner diameter of the capillary on the downstream
side is made smaller than that on the upstream side, the
concentration of the sample solution will be increased when samples
migrating from the end of the upstream capillary are lead into the
downstream capillary, resulting in increased sample concentration,
hence highly sensitive detection.
[0078] If the inner diameter of the capillary on the downstream
side is made larger than that on the upstream side, samples
migrating from the upstream capillary can be lead into the
downstream capillary with greater ease and reliability.
[0079] Moreover, since fluorescence from the sample can be detected
without the excitation light passing through the capillary region
according the present embodiment, the capillary need not be
transparent. The capillary coating need not be removed; this
ensures handling ease. Furthermore, it also allows use of the
capillary made of opaque fluorine-contained polymer such as
tetrafluoroethylene polymer tube and tri-fluoro ethylene chloride
polymer.
[0080] The capillary made of fluorine-contained polymer features
little suction of samples, eliminating the need of treatment such
as surface treatment. It is also very resistant against damage and
chemicals, so use of fluorine-contained polymer capillaries
provides excellent maneuverability, and permits use of solvents
over an extensive range of pH values. In the present embodiment,
the case of two or more pairs of capillaries has been explained. In
the case of one pair of capillaries, electrophoresis separation of
samples, detection of the fluorescence and detection of sample
separation pattern are possible in the same way. In this case, the
photomultiplier can be used as the optical detector.
[0081] [Embodiment 3]
[0082] The following describes the DNA sequence determination
method using the apparatus introduced in Embodiment 2. DNA
fragments labeled by fluorophores are prepared by DNA polymerase
reaction, using the primer labeled by fluorophore according to the
well-known dideoxy sequencing method invented by Sanger and his
colleagues. The primer bonded with Texas Red (Sulforhodamine 101,
maximum emission wavelength of 615 nm) is used as primer. Firstly,
the labeled primer is added to the single-strand DNA and annealed,
so that labeled primer is bonded to the single-strand DNA. This
reaction solution is divided into four parts, which are subjected
to DNA polymerase reactions corresponding to A, C, G and T,
respectively. That is, four types of deoxynucleotide triphosphates
(dATP, dTTP, dCTP and dGTP) and ddATP which will be a terminator
are added to the single-strand DNA bonded with labeled primer to
cause DNA polymerase reaction. The above procedure provides DNA
fragments labeled by fluorophores having various lengths with
terminal A. Similar reactions are made for C, G and T. Four types
of reaction solution obtained in the above procedure are poured
into four of the capillaries 1a to 1t, for example, capillaries 1a,
1b, 1c and 1d, respectively. The pouring procedure is the same as
given in Embodiment 2. Reaction solution A is put into capillary
1a, reaction solution C into 1b, reaction solution G into 1c and
reaction solution T into 1d. After that, about 6 kV-voltage is
applied to cause electrophoresis. Using the He--Ne laser having a
wavelength of 594 nm to excite Texas Red (Sulforhodamine 101),
change of the intensity of fluorescence in gaps 3a to 3d is
measured with respect to time. Since the DNA fragments having
smaller molecular weight are made to migrate earlier, the base
sequence is determined by analyzing the fluorescence intensity at
each gap according to time sequence. The apparatus shown in
Embodiment 2 has 20 capillaries in which samples can be poured.
Said DNA base sequence determination method allows simultaneous
determination of base sequence of five types of DNA samples. This
permits determination of the base sequence of more DNA samples by
increasing the number of pairs of capillaries held in the optical
cell.
[0083] In the present embodiment, the Texas Red (Sulforhodamine
101) is used as fluorophore. However, it is also possible to detect
fluorescence emitted from two or more fluorophores. In that case,
for example, it is possible to Lake either of the following
steps:
[0084] (1) the optical detector sets comprising interference filter
32, lens 33 and detector 34 are prepared in numbers corresponding
to that of the fluorophores, and each of the said detector sets is
made to detect fluorescences of separate wavelength bands as shown
in FIG. 4, or
[0085] (2) the splitting prism is installed after lens 33 to
separate light into spectral components, and the image of each
component is formed on the two-dimensional detector such as a
camera. Then fluorescence intensity is measured for each migration
lane and wavelength.
[0086] Thus, the DNA base sequence can be determined even when the
apparatus which provides simultaneous detection of two or more
fluorophores has been configured. That is, each DNA is subjected to
polymerase reaction, using primers labeled by different
fluorophores for each type of the terminal base. Then reaction
solutions are mixed and electrophoresis is carried out; then
fluorescence of the DNA fragments passing through the gap spaces is
detected. The base type can be identified by identifying-the
fluorophore types, whereby the base sequence is determined.
[0087] The fluorophore types can be identified by comparing the
fluorescences at the maximum emission wavelength of four types of
fluorophores. In this case, the base sequence of the DNA samples
can be determined in the migration lane comprising a pair of
capillaries and gaps. When two or more migration lanes are present
as shown in FIG. 3, the base sequence of two or more DNA samples
can be determined simultaneously in the number corresponding to the
number of the migration lanes.
[0088] [Embodiment 4]
[0089] The gap is formed by a pair of capillaries in said
Embodiments 2 and 3, but the gap can also be made by other than the
capillary pair. For example, the molecular weight separation region
is composed of capillaries, as in said Embodiments. A gap can be
formed by the end of these capillaries and the plate provided with
fine holes. FIG. 5 shows the configuration of the electrophoresis
region and laser irradiation system of the electrophoresis
apparatus according to the fourth Embodiment. As in the case of
Embodiment 2, twenty capillaries 1a to 1t as electrophoresis
separation region are held by the multi-capillary holder 5a and are
fixed to the optical cell 60. The plate 62 provided with fine holes
61a to 61t having an inner diameter of 200 .mu.m is fixed on the
side opposite to the optical cell 60. Fine holes 61a to 61t are
provided at the positions respectively corresponding to capillaries
1a to 1t, resulting in formation of the gaps. When the sheath
solution flows, the sample migrating from each capillary is led to
each corresponding fine hole. The vessel for trapping solution 63
is laid out below plate 62 to temporarily store the solution coming
from the fine holes, and the solution is then led to the vessel for
electrode 65 through tube 64.
[0090] Electrophoresis is performed in the same way as in
Embodiment 2, by applying power to the vessel for electrode 65 and
another vessel for electrode (not illustrated). Irradiation of
laser and detection by fluorescence are also performed as in the
case of the Embodiment 2.
[0091] [Embodiment 5]
[0092] In Embodiment 2, it is also possible to design a
configuration where the samples are migrated by the flow of sheath
solution, using only the upstream capillaries, without using the
downstream ones. FIG. 6 shows the configuration of the
electrophoresis region of the electrophoresis apparatus. As in the
case of Embodiment 2, ends of capillaries 1a to 1t are arranged and
held in the optical cell 104a.
[0093] The bottom of optical cell 104a is connected with the seal
plate 70 and tetrafluoroethylene polymer tube 71, and the end of
tetrafluoroethylene polymer tube 71 is immersed in the vessel for
anode electrode 107, to permit flow of sheath solution. Sheath
solution is poured in optical cell 104a in the same way as in the
case of the Embodiment 2.
[0094] Electrophoresis is performed by DC voltage applied from DC
high voltage power supply 12 between the vessel for cathode
electrode 106 and the vessel for anode electrode 107. Immediately
below the capillaries, samples which migrate from capillaries do
not contact these samples which migrate through other capillaries;
they migrate through the optical cell 104a, finally going to the
vessel for anode electrode 107 samples are detected by irradiating
the laser light to 500 .mu.m downstream of the ends of the
capillaries in optical cell 104a, and by receiving
fluorescence.
[0095] The photodetecting system is designed in the same
configuration as in Embodiment 2. The sheath flow formation method
of the present Embodiment is basically different from that of
Embodiment 2. In the present Embodiment, sheath solution flows in
the entire optical cell in a laminar flow. As a result, the flow
rate of the sheath solution differs slightly, depending on the
position inside the optical cell, and the sample migration lane
also tends to vary; such unstable conditions occur. In terms of
sensitivity and simplicity in the apparatus configuration, however,
almost the same results can be obtained as those in Embodiment
2.
[0096] [Embodiment 6]
[0097] In the apparatus described in Embodiment 2, it is also
possible to form the gap by using the plate provided with two or
more grooves instead of the downstream capillaries. FIG. 7 is an
oblique view of the plate provided with two or more grooves. Said
Figure represents the case where four grooves corresponding to four
capillaries are provided. Grooves 81a, 81b, 81c and 81d are formed
on one side of the plate 80 conforming to the form inside the
optical cell. The form of the groove is made to correspond to the
size of the capillary for electrophoresis separation; for example,
the groove is designed to have a width of 300 .mu.m and a depth of
600 .mu.m. The pitch distance between grooves is 1 mm. Note that
the pitch and groove form can be changed as required. FIG. 8 is an
oblique view showing the sectional area of the optical cell of
electrophoresis region of the electrophoresis apparatus using the
said plate. Optical cell 84 has inner dimensions of 20 mm in width,
3 mm in depth and 40 mm in length. The flow cell is used, which has
the quartz glass plate having a thickness of 2 mm, with the top and
bottom ends opened. Said Figure also shows the optical cell without
the glass region located in its front. Plate 80 is inserted into
optical cell 84 in close contact, so that the four lanes comprising
the grooves 81a, 81b, 81c and 81d, and the glass (not illustrated)
in front of the optical cell are formed. Capillaries 82a, 82b, 82c
and 82d having an inner diameter of 100 .mu.m and an outer diameter
of 200 .mu.m (gel formed inside in the same procedure as in
Embodiment 2) are fixed inside the fluorescent cell 84 by
multi-capillary holder 83. The pitch distance between the
capillaries are 1 mm so as to match the pitch distance between
grooves, and adjustment is made to ensure that the capillary axis
is located at the center of each groove. This adjustment is
achieved by adjusting the position of the holes on multi-capillary
holder 83. Ends of capillaries 82a, 82b, 82c and 82d are arranged
inside the multi-capillary holder 83, and adjustment is made so
that each capillary end will be about 1 mm away from plate 80; then
capillaries are fixed in the optical cell.
[0098] Electrophoresis is made possible by bringing the bottom of
the optical cell 84 in contact with the buffer solution inside the
vessel for the anode electrode. As in the case of Embodiment 4 or
5, it is also possible to connect it to the vessel for the
electrode through the tube. Sheath solution is poured in the same
way as in the case of the Embodiment 2. Samples migrating from the
capillaries 82a to 82d are held in the sheath solution and made to
flow into optical cell 84; they are then led to the vessel for the
anode electrode through grooves 81a, 81b, 81c and 81d.
[0099] Electrophoresis, laser irradiation and fluorescence
detection are performed in the same method as in the case of the
Embodiment 2; the method provides an effective and simultaneous
detection of samples separated respectively by two or more
capillaries. In the present Embodiment, the downstream side is
formed by the plate constituting the grooves, not by the
capillaries. This allows easy adjustment of the distance between
each capillary end and the plate end ends of the grooves. The plate
is preferred to be made of quartz glass, where fluorescence is not
caused by laser irradiation.
[0100] [Embodiment 7]
[0101] In the present Embodiment, the DNA fragments labeled by
fluorophores are separated by electrophoresis and are detected by
fluorescence. Fluorescence detection is made at the region where
the samples separated by electrophoresis in the capillary migrate
from the capillary end into the buffer solution. The following
describes the case of using the Texas Red (sulforhodamine 101) for
labeling fluorophores:
[0102] FIG. 9 illustrates the configuration of the electrophoresis
apparatus of the present Embodiment. It uses two capillaries; a
silica capillary 101 having an inner diameter of 100 .mu.m, outer
diameter of 375 .mu.m and length of 30 cm and a silica capillary
102 having the same inner and outer diameters with a length of 5
cm. Five percent polyacrylamide gel containing urea as denaturant
is produced in capillaries 101 and 102, as in the case of the
capillaries 1a and 1b in Embodiment 2.
[0103] Each one end of capillaries 101 and 102 is held face to face
with the other in the optical cell, and the samples are detected
using detection of fluorescence. That is, each one end of
capillaries 101 and 102 is held face to face coaxially with the
other forming a 0.1 nm gap 103 inside rectangular quartz optical
cell 104b (outer 3 mm square, inner 1 mm square), and the gap space
is used as an optical detecting portion. The other ends of
capillary 101 and capillary 102 are immersed respectively in the
vessel for cathode electrode 106 and the vessel for anode electrode
107 filled with buffer solution (TRIS-borate-EDTA buffer solution).
Buffer solution containing glycerin is poured into optical cell
104b, and gap 103 is filled with buffer solution. DC high voltage
is applied between the vessel for cathode electrode 106 and the
vessel for anode electrode 107 by DC high voltage power supply 12.
When the voltage is applied, current runs through capillary 102,
gap 103 and capillary 101. Gap 103 is short and, in gap 103,
current flows along the line connecting the axes of capillary 102
and capillary 101. So the migrating sample flows out of capillary
101, and passes through gap 103 without much dispersion, flowing
into capillary 102. That is, the sample migrates without contacting
the optical cell 104b.
[0104] Buffer solution containing glycerin has been poured into
optical cell 104, namely, gap 103; addition of glycerin is intended
to reduce the influence of convection due to increased viscosity of
buffer solution and to improve the electric field intensity in gap
103. Controlled convection of the buffer solution and increased
electric field intensity reduces the dispersion of the sample in
gap 103, allowing easy migration of the sample from capillary 101
to capillary 102.
[0105] Glycerin is used in the present Embodiment. Other substances
can be used if they have high viscosity and are usable for
electrophoresis. For example, polyethylene glycol or succrose etc.
can be used. If gap 103 is sufficiently narrow, normal buffer
solution without glycerin may be used. To introduce DNA fragments
labeled by fluorophores which are samples, one end of capillary 101
on the cathode side is immersed in the sample solution temporarily,
and 5 kV voltage is applied between the sample solution and the
vessel for anode electrode 107 for about 20 seconds. Then the end
of capillary 101 is returned to the vessel for cathode electrode
106, and 10 kV DC voltage is applied between the vessel for cathode
electrode 106 and the vessel for anode electrode 107. Then the
samples migrate from cathode to anode sides in capillary 101 while
undergoing molecular weight separation, and pass through gap
103.
[0106] Laser light 21 having a wavelength of 594 nm from the He--Ne
laser source 20 is condensed to about 20 .mu.m by lens 22, and is
irradiated on the gap 103. Fluorescence 30 issued from the DNA
fragments is collected by lens 112 from the direction perpendicular
to the direction in which laser light is irradiated. Backgrounds
such as scattered light are eliminated by interference filter 113,
and the image is formed on slit 115 by lens 114. The light passing
through slit 115 is detected by photomultiplier 116, and amplified
by amplifier 117; then the electrophoresis pattern is processed by
data processor 118 of the computer or the like, and their results
are displayed on monitor 37, and are output on printer 38 or stored
in memory 39.
[0107] To ensure effective detection of the fluorescence issued
from the Texas Read, interference filter 113 uses the band pass
interference filter which permits transmission of a wavelength band
ranging from 610 to 630 nm. Lens systems 112 and 114 are configured
to have the equal magnifications.
[0108] The opening of slit 115 is set to 50 .mu.m in the direction
of electrophoresis and 100 .mu.m in the direction of laser light,
and adjustment is made to ensure that fluorescent image in gap 3 is
located at the center of the opening. Since samples migrate only
close to gap 3, the image of the scattered light of the laser light
at optical cell 104b is not formed on the opening of slit 115 and
is not detected by the photomultiplier 116 because of the
configuration of said optical system. Scattered light and
fluorescence are not produced by the capillary and gel, resulting
in substantially reduced background intensity.
[0109] FIG. 10 is an enlarged view representing the sectional area
of the optical cell 104b. Quartz optical cell 104b is fixed by
multi-capillary holders 123a and 123b. Liquid leakage is prevented
by insertion of the silicone rubber packings 122a and 122b between
optical cell 104b and holders 123a and 123b. Capillary 101 is fixed
to multi-capillary holders 123a by tetrafluoroethylene polymer
ferrule 124a and screw 125a. Likewise, capillary 102 is also fixed
by ferrule 124b and screw 125b. The gap between capillary 101 and
capillary 102 can be freely adjusted by specifying the length of
the capillary from the ferrule. In the present Embodiment, this is
0.1 mm, as described previously. The optical cell is provided with
solution inlet to pour buffer solution. It is also connected with
the valves 126a and 126b. The buffer outlet can be provided at the
optical cell holder. Optical cell 104b is filled with buffer
solution after fixing the capillary.
[0110] DNA fragments labeled by fluorophores can be detected by the
apparatus in the present Embodiment. The DNA fragments labeled by
fluorophores area prepared according to the well-known dideoxy
sequencing method invented by Sanger and his colleagues, under the
same conditions as in the case of the Embodiment. As discussed
above, the DNA fragment electrophoresis pattern can be measured by
introducing the samples into the capillary and measuring the
fluorescence intensity in the gap. As in the case of the Embodiment
2, compared to the case of fluorescence detection by irradiating
the laser light on the capillary without coating, the background
intensity is reduced by about one tenth or less in the present
Embodiment, permitting detection of samples of less concentration.
The method according to the present Embodiment provides highly
sensitive detection of samples using the gel, without loss of
electrophoresis characteristics. The buffer solution is not made to
flow, so a simple apparatus configuration can be obtained. The
laser equipment and fluorophores to be used are not restricted to
He--Ne laser and Texas Red (sulforhodamine 101); any fluorophores
and any suitable laser light source can be used. Furthermore, as in
the case of the Embodiment 3, the present method provides
simultaneous fluorescence detection of two or more fluorophores.
When the DNA base sequence is to be determined using the two or
more fluorophores in the apparatus according to the present
Embodiment, exactly the same procedure as in the case of the
Embodiment 3 is used. The present Embodiment has been explained
with reference to the detection of DNA fragments, but the same
method is applicable also to the analysis of protein, sugar and
similar substances. Furthermore, two capillaries having the same
inner diameter have been used for the description of the present
Embodiment. It is also possible to use a combination of capillaries
having different inner diameters. The effect resulting from the
difference between the inner diameters of capillaries 101 and 102
is the same as that described with reference to Embodiment 2.
Furthermore, the method for the present Embodiment permits
detection of the fluorescence without the excitation light passing
through the capillary region, so the capillary need not be
transparent; the capillary coating need not be removed. It allows
use of capillaries made of an opaque fluorine-contained polymer
such as tetrafluoroethylene polymer or trifluoro ethylene chloride
polymer.
[0111] [Embodiment 8]
[0112] The following describes the simultaneous fluorescence
detection apparatus with four capillaries arranged in parallel. The
number of capillaries is not limited to four; it can be any number.
FIG. 11 shows the configuration of the electrophoresis apparatus
for the present Embodiment. The 127a, 127b, 127c and 127d in the
Figure denote silica capillaries having an inner diameter of 100
.mu.m, outer diameter of 375 .mu.m and length of 30 cm. One end of
each of the capillaries (not shown) is immersed in the vessel for
the cathode electrode as in the case shown in FIG. 9. Likewise,
128a, 128b, 128c and 128d denote the silica capillaries having the
same inner and outer diameters with a length of 5 cm, and one end
of each is immersed in the vessel for the anode electrode (not
shown). According to the same method as given in the Embodiment 2,
five percent polyacrylamide gel containing urea as denaturant is
produced in these capillaries.
[0113] Each capillary is provided with silane coupling treatment so
that polyacrylamide gel and capillary wall are chemically bonded
together, with consideration given so as not to allow the capillary
to elude from the acrylamide during electrophoresis.
[0114] Capillary 127a to 127d and capillaries 128a to 128d are held
and fixed in rectangular quartz optical cell 104c, maintaining gaps
129a to 129d of specified intervals, as in the case of the
Embodiment 7, and are arranged in a straight line in close
proximity with each other, forming two or more gaps, namely,
optical detecting portions.
[0115] The capillaries are fixed by the capillary holders 142 and
143 of the block made of fluorine-contained polymer such as
tetrafluoroethylene, provided with four vertical holes at intervals
of 1 mm. Each capillary is inserted into each of four vertical
holes, and adjustment is so made that 127a and 128a, 127b and 128b,
127c and 128c, and 127d and 128d are respectively coaxial, and that
each length of gaps 129a to 129d will be 0.2 mm.
[0116] Buffer solution containing glycerin is poured into the
optical cell 104c, filling gaps 129a to 129d with buffer solution.
If voltage is applied under this condition, the sample led into
capillary 127a migrates to gap 129a, then to 128a. Samples led to
other capillaries also migrate in the same way. The glycerin in the
buffer solution restrains the convection of the buffer solution in
gaps, as in the case of embodiment 7 and ensures reliable and
smooth migration of the sample from capillaries 127a to 127d to
capillaries 128a to 128d.
[0117] Fluorescent detection of the DNA fragments passing through
gaps 129a to 129d is carried out as follows: Firstly, laser light
21 from laser source 20 is condensed by lens 22 to permit
simultaneous irradiation of two or more optical detecting portions,
namely, gaps 129a to 129d. The focal point is set at the
mid-position between the gaps 129b and 129c, and adjustment is made
to ensure that the maximum diameter of the irradiated spot size is
100 .mu.m between gaps 129a to 129d. When the focal distance of
about 150 mm is used as lens 22, for example, it is possible to
irradiate gaps 129a to 129d with much the same spot size.
[0118] Fluorescence 30 emitted from DNA fragments passing through
each gap is collected by lens 134 from the position perpendicular
to the direction in which the laser is irradiated, and the
background such as scattered light is removed by the interference
filter 32. Then it is collected by lens 33, and the image is formed
on line sensor 37 such as a photodiode array or CCD camera. In the
configuration in FIG. 11, using the fluorescence detection system
as in the case of the Embodiment 1 shown in FIG. 1, it is also
possible to collect the fluorescence from the linear laser
irradiation region by the cylindrical lens. After the data is
output from the output of line sensor 37, the electrophoresis
pattern and the like is subjected to data processing by data
processor 36 of the computer or similar device, and their results
are displayed on monitor 37, and are output on printer 38 or stored
in memory 39.
[0119] Using the He--Ne laser having a wavelength of 594 nm as a
laser light and Texas Red (sulforhodamine 101) solution as sample,
the sample is made to migrate in capillaries 127a to 127d. When
fluorescent images of samples migrating in gap spaces which are
optical detectors are detected by the line sensor 37, strong
fluorescence intensity is detected in four positions of the gaps
129a to 129d, namely, optical detecting portions corresponding to
migration lanes, each independently of the other optical detecting
portions. Continuous and simultaneous detection of the samples
migrating in the capillaries is possible by detecting the intensity
of the signals at the positions corresponding to migration lanes on
the line sensor.
[0120] The method according to the present Embodiment allows
fluorescence detection of samples migrating simultaneously and
under the same conditions by two or more optical detectors. It also
allows analysis over an extensive range, for example, DNA base
sequence determination for one or more samples, analysis of the
side strand or functional group using the fluorophores, and
detailed analysis of the samples separated by liquid
chromatography. Furthermore, pairs of capillaries are arranged in a
straight line in close proximity to form two or more gaps, so only
one fluorescence collecting means such as a lens is sufficient;
this feature ensures reduced cost and simple structure.
[0121] Furthermore, as in the case of the preceding Embodiments,
laser light is irradiated along the gaps where there is no
capillary. Then the laser is not scattered or refracted by the
capillary, so each gap can be irradiated by much the same spot
size, with much the same intensity and reduced background
intensity. This permits simple configuration of the apparatus which
provides effective excitation of two or more samples, hence highly
sensitive detection. Such an apparatus facilitates simultaneous
detection of many samples.
[0122] The DNA base sequence determination method using the
apparatus according to the method of the present Embodiment is the
same as that of Embodiment 3. Use of the Texas Red (sulforhodamine
101, maximum emission wavelength: 615 nm) as a labeling
fluorophore, and the He--Ne laser having a wavelength of 594 nm as
an excitation light source is especially preferred to ensure high
sensitivity.
[0123] [Embodiment 9]
[0124] The gap is formed by a pair of capillaries in said
Embodiments 7 to 8, but it can also be by other substances than
capillaries. For example, the electrophoresis separation region is
composed of capillaries, as in said Embodiments. A gap can be
formed by the end of these capillaries and the plate provided with
fine holes. FIG. 12 is an enlarged view representing the sectional
area of the optical cell in which the gap is formed by a capillary
and the plate provided with fine holes.
[0125] As in the case of the Embodiment 7, capillary 171 filled
with polyacrylamide gel and plate 173 provided with fine holes 172
(for example, a plate made of tetrafluoroethylene polymer) are
arranged face to face so that the axis of capillary 171 and that of
fine hole 172 will be almost matched to each other, and gap 174 is
formed. They are held inside the optical cell 175. This cell is a
rectangular optical cell having outer dimensions of 3 mm square and
inner dimensions of 1 mm square, with the top and bottom ends
opened. It is held, for example, by tetrafluoroethylene polymer
block 176 on the top, and held by plate 173 on the bottom and
fixed, so that buffer solution can be stored in the cell. The
tetrafluoroethylene polymer block 176 is provided with the hole
conforming to the outer dimensions of capillary 171. Capillary 171
is passed through that hole to hold the capillary 171, and the
length of gap 174 can be adjusted from 0.1 mm to 1.0 mm. The other
end of capillary 171 is immersed in the vessel for the cathode
electrode, as in the case of the Embodiment 7. The
tetrafluoroethylene polymer tube 177 is connected to the bottom of
plate 173 through tube holder 178, and is led to the vessel for the
anode electrode. Plate 173 can also be made to contact with the
vessel for the anode electrode. Although not shown in FIG. 12, the
buffer solution inlet is provided inside fluorescent cell 175, as
in the case of FIG. 10. The buffer solution is supplied through the
valve during electrophoresis, to fill optical cell 175, gap 174 and
tetrafluoroethylene polymer tube 177. After the supply of buffer
solution is stopped, the sample is made to migrate. The method of
the present Embodiment provides fluorescent detection with the
minimum background intensity as in the case of Embodiment 7, and
highly sensitive fluorescence detection.
[0126] Arrangement of fine holes on plate 173 in a straight line
permits configuration of the optical cell which has the same
effects as those in the case of the Embodiment 8.
[0127] The method of the present Embodiment ensures easy
installation of the apparatus since plate 173 is used on one
side.
[0128] As disclosed above, according to the present invention, one
or more samples are separated by electrophoresis separation by
using the plate gel or capillary gel, and the laser beam is
irradiated linearly on the two or more migration lanes from the
direction which is approximately perpendicular to the direction for
sample migration and which is parallel to the surface formed by two
or more migration lanes; thereby detecting fluorescence on a
real-time basis from the fragments migrating two or more migration
lanes. Use of Texas Red (sulforhodamine 101, maximum emission
wavelength: 615 nm) as labeling fluorophore, and He--Ne laser light
having an emission wavelength of 594 nm as an excitation light
source is particularly preferred to ensure high sensitivity in
Embodiments 1 to 9. In Embodiments 2 to 9, however, the fluorophore
and light source to be used are not restricted to Texas Red and
He--Ne laser having an emission length of 594 nm. For example,
rhodamine derivatives, FITC, SF, TRITC and ALPC (aluminum
phthalocyanine) complex (emission wavelength: about 700 nm) as
fluorophore, and argon ion laser (emission wavelength: 488 nm and
514.5 nm), He--Ne laser (emission wavelength: 632.8 nm), YAG laser
(second harmonic wavelength: 532 nm) and semiconductor laser
(emission wavelength: about 670 nm) as the laser light source can
be used.
* * * * *