Patent Application
20120282649
The present invention relates to a fluorescence detecting apparatus and a fluorescence detecting method, by which a fluorescence signal of fluorescence emitted from an object to be measured irradiated with laser light is processed, and a fluorescence signal processing method.
In medical and biological fields, flow cytometers are widely used. A flow cytometer uses a photoelectric converter, such as a photomultiplier tube or an avalanche photodiode, that receives fluorescence emitted from objects to be measured, such as cells or genes, irradiated with laser light to determine the kind of object to be measured and the number of the objects to be measured and further analyze the characteristics of each of the objects to be measured.
Specifically, in such a flow cytometer, objects to be measured obtained by labeling objects to be analyzed such as biological substances (e.g., cells, DNA, RNA, enzymes, proteins) with a fluorochrome are allowed to flow in a sheath fluid flowing in a tube under pressure at a speed of about 10 m/s or less to form a laminar sheath flow. The flow cytometer irradiates the objects to be measured in the flow with laser light, receives fluorescence emitted from the fluorochrome attached to the objects to be analyzed, and identifies the objects to be analyzed by using the fluorescence as a label for identifying the objects to be analyzed.
The flow cytometer can measure, for example, the intracellular relative amounts of DNA, RNA, enzymes, proteins, etc. in a cell and analyze their activities in a short period of time. Further, the flow cytometer identifies predetermined types of cells or chromosomes based on fluorescence and selectively collects only the identified cells or chromosomes in a living state in a short period of time with the use of a cell sorter or the like.
When the flow cytometer is used, a larger number of objects to be measured are required to be accurately identified in a shorter period of time from information about fluorescence.
For example, a fluorescence detecting apparatus and a fluorescence detecting method are known which are capable of accurately identifying many kinds of objects to be measured in a short period of time by calculating the fluorescence lifetime (fluorescence relaxation time) of fluorescence emitted from a fluorochrome in the objects to be measured irradiated with laser light (Patent Literature 1).
In such a fluorescence detecting apparatus, an object to be measured is irradiated with laser light whose intensity is modulated, fluorescence emitted from the object to be measured is received by a photoelectric converter, the phase shift of a fluorescence signal outputted from the photoelectric converter with respect to a modulation signal used to modulate the intensity of laser light is determined, and a fluorescence relaxation time is calculated from the phase shift.
The phase shift used to calculate a fluorescence relaxation time is calculated by eliminating the influence of a phase shift caused by the characteristics of the photoelectric converter itself that receives fluorescence and eliminating the influence of a phase shift caused by the optical path lengths of laser light and of fluorescence and the length of an electrical circuit in the apparatus. However, the phase shift used to calculate a fluorescence relaxation time slightly changes depending on the output level of the fluorescence signal outputted from the photoelectric converter, and therefore a fluorescence relaxation time is not always calculated accurately. Particularly, calculation of an accurate fluorescence relaxation time is required to, for example, determine the presence or absence of FRET (Fluorescence Resonance Energy Transfer).
In order to solve the above problem, it is an object of the present invention to provide a fluorescence detecting apparatus and a fluorescence detecting method, which are capable of calculating an accurate fluorescence relaxation time when a fluorescence signal of fluorescence emitted from an object to be measured irradiated with laser light is processed, and a fluorescence signal processing method for use in the fluorescence detecting apparatus and the fluorescence detecting method.
An aspect of the invention is a fluorescence detecting apparatus for processing a fluorescence signal of fluorescence emitted from an object to be measured irradiated with laser light. The apparatus includes:
a light source unit that emits laser light whose intensity is modulated using a modulation signal with a predetermined frequency;
a light-receiving unit including an output level-adjustable light-receiving element that receives fluorescence emitted from an object to be measured irradiated with the laser light and outputs a fluorescence signal at an adjusted output level;
a first processing unit that mixes the fluorescence signal and the modulation signal with the frequency to generate fluorescence data including information about phase and intensity; and
a second processing unit that calculates a first phase shift of the fluorescence with respect to the modulation signal using the fluorescence data, calculates a second phase shift by making a correction to the calculated first phase shift depending on conditions for adjusting the output level, and calculates a fluorescence relaxation time of the fluorescence using the calculated second phase shift.
The light-receiving unit preferably includes an adjusting section that adjusts the output level using an adjustment parameter value given to the light-receiving element.
Then, the second processing unit preferably uses a correction formula determined depending on the adjustment parameter value, when making the correction,
Further preferably, the second processing unit previously stores a value of a constant used in the correction formula and calls and uses the value of the constant when making the correction.
The second processing unit preferably includes an output level adjusting section that extracts the value of the constant used in the correction formula when a relationship between the adjustment parameter value and the output level indicates that the output level of the light-receiving element is not saturated. The relation ship is determined by changing, in advance, the adjustment parameter value given to the light-receiving element.
When a reference object having a known fluorescence relaxation time is used as the object to be measured, the output level adjusting section preferably extracts the value of the constant so that the fluorescence relaxation time calculated from the second phase shift approximates the known fluorescence relaxation time of the reference object by the correction.
For example, the light-receiving element may be a photomultiplier tube and the adjustment parameter value is a voltage applied to an electrode of the photomultiplier tube.
Then, the correction formula is preferably represented by the following formula: θτ=X−θmeas−A·V(−1/2), where X and A are constants. The voltage applied to the electrode is represented by V, and the first phase shift is represented by θmeas, and the second phase shift is represented by θτ.
An adjustable neutral density filter is preferred to be provided in front of a light-receiving surface of the light-receiving element.
Other aspect of the invention is a fluorescence detecting method for use in a fluorescence detecting apparatus for processing a fluorescence signal of fluorescence emitted from an object to be measured irradiated with laser light. The method includes the steps of:
emitting laser light whose intensity is modulated using a modulation signal with a predetermined frequency;
allowing a light-receiving element to receive fluorescence emitted from an object to be measured irradiated with the laser light and output a fluorescence signal at an adjusted output level;
mixing the fluorescence signal and the modulation signal with a predetermined frequency to generate fluorescence data including information about phase and intensity; and
calculating a first phase shift of the fluorescence with respect to the modulation signal using the fluorescence data, calculating a second phase shift by making a correction to the calculated first phase shift depending on conditions for adjusting the output level, and calculating a fluorescence relaxation time of the fluorescence using the calculated second phase shift.
Other aspect of the invention is a method for allowing a fluorescence detecting apparatus to process a fluorescence signal of fluorescence emitted from a reference object having a known fluorescence relaxation time by irradiation with laser light. The method includes:
a first step of emitting laser light whose intensity is modulated using a modulation signal with a predetermined frequency;
a second step of allowing a light-receiving element to receive fluorescence emitted from a reference object irradiated with the laser light and output a fluorescence signal at an adjusted output level;
a third step of mixing the fluorescence signal and the modulation signal with a predetermined frequency to generate fluorescence data including information about phase and intensity;
a fourth step of calculating a first phase shift of the fluorescence with respect to the modulation signal using the fluorescence data and storing a pair of the calculated first phase shift and an adjustment parameter value given to the light-receiving element to adjust the output level;
a fifth step of storing two or more pairs of the first phase shift and the adjustment parameter value by repeating the first to fourth steps while varying the adjustment parameter value;
a sixth step of calling the two or more stored pairs and approximating a regression formula expressing a relationship between the adjustment parameter value and the first phase shift to a relationship represented by the two or more called pairs, to extract a value of an unknown constant included in the regression formula; and
a seventh step of storing the extracted value of the constant.
The adjustment parameter value is preferably changed so that the output level is reduced every time the first to fourth steps are repeated.
The fluorescence to be received by the light-receiving element is preferably attenuated by a neutral density filter before being received by the light-receiving element so that the output level of the fluorescence signal outputted by the light-receiving element is not saturated.
The fluorescence detecting apparatus and the fluorescence detecting method according to the above aspects of the present invention make it possible to calculate an accurate fluorescence relaxation time when a fluorescence signal of fluorescence emitted from an object to be measured irradiated with laser light is processed.
Further, the fluorescence signal processing method according to the above aspect of the present invention makes it possible to efficiently determine the value of a constant for use in a correction formula for calculating an accurate fluorescence relaxation time.
Hereinbelow, a fluorescence detecting apparatus, a fluorescence detecting method, and a fluorescence signal processing method according to the present invention will be described in detail.
The flow cytometer 10 includes a signal processing device 20 and an analyzing device (computer) 80. The signal processing device 20 detects and processes a fluorescence signal of fluorescence emitted from a sample 12 as an object to be measured when the sample 12 is irradiated with laser light. The analyzing device (computer) 80 calculates a fluorescence intensity and a fluorescence relaxation time from a processing result obtained by the signal processing device 20. Hereinbelow, the flow cytometer 10 will be described with reference to a case where the sample 12 used as an object to be measured is a cell (object to be analyzed) X2 labeled with a fluorescent protein (fluorochrome) X1. The fluorochrome used in this embodiment may be one other than a fluorescent protein. The object to be analyzed used in this embodiment may be one other than a cell, and examples thereof include biological substances such as DNA, RNA, enzymes, and proteins and artificially-produced microbeads. It is to be noted that the sample 12 illustrated in
The signal processing device 20 has a laser light source unit 22, light-receiving units 24 and 26, a control•processing unit 28, and a tube 30. The control•processing unit 28 has a control unit that modulates the intensity of laser light emitted from the laser light source unit 22 at a predetermined frequency and a signal processing unit that processes a fluorescence signal of fluorescence emitted from the sample 12. The tube 30 allows the samples 12 to flow in a high-speed flow of sheath fluid to produce a flow of the samples 12.
A recovery container 32 is provided at the outlet of the tube 30. The flow cytometer 10 may include a cell sorter for separating biological substances such as predetermined cells in the samples 12 in a short period of time by irradiation with laser light to sort biological substances into different recovery containers.
The laser light source unit 22 emits laser light with a predetermined wavelength. A lens system is provided to focus the laser light on a predetermined position in the tube 30, and a measurement point of the sample 12 is provided at this focus position.
The laser light source unit 22 emits intensity-modulated laser light with a wavelength in the visible light range.
The laser light source unit 22 has a light source 22a. The light source 22a emits, as CW (continuous wave) laser light, laser light L with a wavelength that excites the fluorescent protein X1 while modulating the intensity of the laser light L using a modulation signal with a predetermined frequency f.
Further, the laser light source unit 22 has a lens system 23 and a laser driver 34. The lens system 23 focuses the laser light L onto the center of the tube 30 to provide a measurement point. The laser driver 34 drives the light source 22a.
As the light source that emits the laser light L, for example, a semiconductor laser is employed. The output power of the laser light L is, for example, about 5 to 100 mW.
On the other hand, the frequency (modulation frequency) f used to modulate the intensity of the laser light L has a modulation period slightly longer than a fluorescence relaxation time and is, for example, 10 to 50 MHz.
The light source 22a oscillates at a predetermined wavelength band so that the fluorochrome is excited by the laser light L and emits fluorescence of a specific wavelength band. The sample 12 to be excited by the laser light L is irradiated with the laser light L at the measurement point in the tube 30 when passing through the measurement point. At this time, the fluorescent protein X1 emits fluorescence at a specific wavelength.
The light-receiving unit 24 and the laser light source unit 22 are arranged on opposite sides of the tube 30. The light-receiving unit 24 has a photoelectric converter that receives the laser light forward-scattered by the sample 12 passing through the measurement point and outputs a detection signal of the sample 12 to announce that the sample 12 passes through the measurement point. The detection signal outputted from the light-receiving unit 24 is supplied to the control•processing unit 28 and the analyzing device 80 and used as a trigger signal that announces timing, at which the sample 12 passes through the measurement point in the tube 30, to start processing, an ON signal for starting processing, and an OFF signal.
On the other hand, the light-receiving unit 26 is arranged in a direction perpendicular to both a direction in which the laser light emitted from the laser light source unit 22 travels and a direction in which the sample 12 moves in the tube 30. The light-receiving unit 26 has a photomultiplier tube that receives fluorescence emitted from the sample 12 irradiated with the laser light at the measurement point. In this embodiment, a well-known photoelectric converter such as an avalanche photodiode may be employed instead of the photomultiplier tube.
The light-receiving unit 26 illustrated in
The lens system 26a is configured to focus fluorescence that has entered the light-receiving unit 26 onto a light-receiving surface of the photomultiplier tube 27.
The ND filter 26b attenuates fluorescence that has entered the light-receiving unit 26. As will be described later, the light-receiving unit 26 uses the ND filter 26b to attenuate fluorescence to prevent the output level of a fluorescence signal from being saturated even when a control voltage applied to an anode of the photomultiplier tube 27 is maximized.
The bandpass filter 26c is a filter that is provided in front of the light-receiving surface of the photomultiplier tube 27 and transmits only fluorescence of a predetermined wavelength band.
The photomultiplier tube 27 is a light-receiving element that converts light received by its photoelectric surface into an electrical signal and outputs a fluorescence signal. The output level of the fluorescence signal outputted by the photomultiplier tube 27 is adjusted. Fluorescence received by the photomultiplier tube 27 is derived from the laser light whose intensity is modulated at a predetermined frequency, and therefore the intensity of the outputted fluorescence signal also varies at the predetermined frequency. The fluorescence signal outputted by receiving fluorescence is supplied to the control•processing unit 28.
When light enters the cathode 27a, photoelectrons are emitted from a photoelectric surface of the cathode 27a into a vacuum within the vacuum vessel. The photoelectrons are directed by the focusing electrode 27b toward the photomultiplier section 27c. The photoelectrons are attracted to the anode 27d1 and collide with a dynode 27c1 of the photomultiplier section 27c, and the dynode 27c1 emits secondary electrons. Further, the secondary electrons emitted from the dynode 27c1 are attracted to the anode 27d2 provided in front of a dynode 27c2 and collide with the dynode 27c2, and the dynode 27c2 further emits secondary electrons. In this way, the electrons, being attracted by the anode 27dn (n is an integer of 2 or more but 10 or less), collide with dynodes 27c3 to 27c10, and sequential emission of secondary electrons from the dynodes 27c3 to 27c10, whereby the electrons are multiplied. The multiplied electrons are attracted by the anode 27d11 and collected at a dynode 27c11, and a fluorescence current is produced through the stem 27e.
At this time, the electron transfer rate of the electrons is determined by a voltage applied to the anodes 27d1 to 27d11, and the energy of electrons colliding with the dynodes 27c1 to 27c10 is determined by the electron transfer rate. Therefore, the amount of secondary electrons emitted from the dynodes 27c1 to 27c10 is adjusted by varying a voltage applied to the anodes 27d1 to 27d11. The flow cytometer 10 uses, as a control voltage for controlling the output level of the fluorescence signal (fluorescence current), a voltage applied to the anodes 27d1 to 27d11.
The voltage adjusting section 26d (see
As illustrated in
The signal generating section 40 generates a modulation signal for modulating the intensity of the laser light L at a predetermined frequency f.
Specifically, the signal generating section 40 has an oscillator 46, a power splitter 48, and amplifiers 50 and 52. The signal generating section 40 supplies the generated modulation signal to the laser driver 34 of the laser light source unit 22 and to the signal processing section 42. As will be described later, the reason why the modulation signal is supplied to the signal processing section 42 is that the modulation signal is used as a reference signal for detecting the fluorescence signal outputted from the photomultiplier tube 27. It is to be noted that the modulation signal is a signal obtained by adding a sinusoidal signal of a predetermined frequency to a DC signal component. The frequency is set to a value in the range of 10 to 50 MHz.
The signal processing section 42 extracts information about the phase shift of fluorescence emitted by irradiation with the laser light with the use of the fluorescence signal outputted from the photomultiplier tube 27. The signal processing section 42 has an amplifier 54, an IQ mixer 58, and a low-pass filter 62. The amplifier 54 amplifies the fluorescence signal outputted from the photomultiplier tube 27.
The IQ mixer 58 is a device that mixes the fluorescence signal supplied from the photomultiplier tube 27 and the modulation signal supplied from the signal generating section 40 as a reference signal. Specifically, the IQ mixer 58 multiplies the reference signal and the fluorescence signal (RF signal) to generate an I signal of the fluorescence signal, which contains a component in phase with the modulation signal, and a Q signal of the fluorescence signal, which contains a 90 degrees phase-shifted component with respect to the modulation signal. The I signal containing a component in phase with the modulation signal is generated by mixing the modulation signal and the fluorescence signal, and the Q signal containing a 90 degrees phase-shifted component with respect to the modulation signal is generated by mixing the modulation signal whose phase is shifted by 90° and the fluorescence signal.
The low-pass filter 62 filters a low-frequency signal of the I signal generated by the IQ mixer 58 and a low-frequency signal of the Q signal generated by the IQ mixer 58. By performing such filtering, the component (Re component) of the fluorescence signal, which is in phase with the modulation signal, and the component (Im component) of the fluorescence signal, which is phase-shifted by 90 degrees with respect to the modulation signal, are extracted as fluorescence data. The extracted components are sent to the signal control section 44. Hereinafter, a process including mixing by the IQ mixer 58 and filtering by the low-pass filter 62 is referred to as a frequency down conversion process, and data obtained by this process is referred to as fluorescence data.
The signal control section 44 amplifies the Re component and the Im component of the fluorescence signal sent from the signal processing section 42, and performs AD conversion.
Specifically, the signal control section 44 has a system controller 60 that provides directions for controlling the operation of each of the units and manages all the operations of the flow cytometer 10, an amplifier 64 that amplifies the Re component and the Im component generated by the signal processing section 42, and an A/D converter 66 that samples the amplified Re component and Im component. The amplifier 64 and the A/D converter 66 may be operated in the analyzing device 80 that will be described later.
The analyzing device 80 determines the phase shift angle of fluorescence with respect to the laser light from the Re component and the Im component A/D converted by the signal control section 44, and further determines a fluorescence relaxation time constant (fluorescence relaxation time) from the phase shift angle. Further, the analyzing device 80 determines a fluorescence intensity from the Re component and the Im component.
The analyzing device 80 is constituted from a computer including a CPU 82 and a memory 84. The analyzing device 80 further includes a phase shift calculating unit 86, a phase shift correcting unit 88, a fluorescence relaxation time calculating unit 90, a fluorescence intensity calculating unit 92, and an output level adjusting unit 94. Each of the units is a software module that performs its function by executing software on the computer. These units may be, of course, implemented by dedicated circuits.
The phase shift calculating unit 86 calculates, from the fluorescence data of fluorescence emitted from the fluorescent protein X1, the argument of a complex number whose real part is the Re component and imaginary part is the Im component (tan−1 (Im component of fluorescence data/Re component of fluorescence data)) as a phase shift angle θmeas. The phase shift calculating unit 86 provides the phase shift angle θmeas to the phase shift correcting unit 88.
The phase shift correcting unit 88 calculates a phase shift angle θτ derived from fluorescence emitted from the fluorescent protein X1 by correcting the phase shift angle θmeas calculated by the phase shift calculating unit 86. The correction is based on the control voltage (adjustment parameter value) applied to the anodes 27d1 to 27d11 of the photomultiplier tube 27, that is, the correction is based on conditions for adjusting the output level of the fluorescence signal performed by the voltage adjusting section 26d.
This correction is performed to prevent a change in the phase shift angle θ caused by a change in the transfer rate of photoelectrons and secondary electrons in the photomultiplier tube 27 to calculate an accurate fluorescence relaxation time. In the photomultiplier tube 27, the transfer rate of photoelectrons and secondary electrons varies depending on the control voltage. Therefore, the phase shift angle θmeas is corrected depending on the set control voltage.
When the length between a dynode that produces secondary electrons and an anode that attracts secondary electrons in the photomultiplier tube 27 is represented by l, the time t required for a photoelectron and a secondary electron to travel the length l is represented by the following formula (1):
t=(2 ml2/V/q)(1/2) (1)
wherein m is the mass of an electron, q is the amount of charge of an electron, and V is the control voltage.
On the other hand, the phase shift angle θ is proportional to the time t. Therefore, a phase shift angle (a phase shift angle derived from the photomultiplier tube 27) θpmt resulting from the time required for an electron to travel in the photomultiplier tube 27 is determined by the addition of a constant B and represented by the formula: θpmt=A·V(−1/2)+B, wherein A and B are constants.
On the other hand, the phase shift angle θmeas calculated by the phase shift calculating unit 86 can be represented by the following formula (2):
θmeas=θ0−(θpmt+θd+θτ) (2)
wherein θ0 is a reference phase shift angle (which is a constant), θpmt is a phase shift angle derived from the photomultiplier tube 27, θd is a phase shift angle derived from the total path length of the laser light, the path length of fluorescence, and the electrical circuit length of the fluorescence signal in the flow cytometer 10, and θτ is a phase shift angle derived from fluorescence emitted from the fluorescent protein X1.
Therefore, the phase shift angle θτ derived from fluorescence emitted from the fluorescent protein X1 is represented by the following formula (3):
θτ=θ0−(θpmt+θd+θmeas) (3)
Substitution of θpmt=A·V(−1/2)+B into the above formula (3) yields the following formula (4):
θτ=X−θmeas−A·V(−1/2) (4)
wherein X is represented as X=θ0−B−θd and is a constant independent of the control voltage.
The memory 84 of the analyzing device 80 previously stores the value of the constant X and the value of the constant A. The phase shift correcting unit 88 calls the values of the constant X and the constant A from the memory 84 and gives them to the formula (4) to prepare a correction formula. Then, the phase shift correcting unit 88 calculates, with the use of the prepared correction formula, the phase shift angle θτ from the phase shift angle θmeas provided by the phase shift calculating unit 86 and the control voltage V provided by the voltage adjusting section 26d.
The phase shift correcting unit 88 provides the calculated phase shift angle θτ to the fluorescence relaxation time calculating unit 90.
The fluorescence relaxation time calculating unit 90 calculates the fluorescence relaxation time τ of the fluorescent protein X1 according to the formula τ=1/(2πf)·tan(θτ), using the phase shift angle θτ calculated by the phase shift correcting unit 88. Here, f is a frequency used to modulate the intensity of the laser light L. The reason why the fluorescence relaxation time τ can be calculated according to the formula τ=1/(2πf)·tan(θτ) is that a fluorescence phenomenon shows a change in accordance with a primary relaxation process.
The fluorescence intensity calculating unit 92 determines the absolute value of a complex number whose real part is the Re component and imaginary part is the Im component from the fluorescence data sent from the AD converter 66 to calculate the fluorescence intensity of fluorescence emitted from the fluorescent protein X1.
The calculated fluorescence intensity, phase shift angle θτ, and fluorescence relaxation time τ of the fluorescent protein X1 are outputted as result information to an output device (not shown) such as a printer or a display. Further, the result information is used for a statistical processing as a measurement result obtained every time the sample 12 passes through the measurement point in the tube 30.
The output level adjusting unit 94 generates a control signal for setting the control voltage applied to the photomultiplier tube 27. The control voltage is arbitrarily set without saturating the output level of the fluorescence signal outputted from the photomultiplier tube 27. The output level adjusting unit 94 has at least information about the current control voltage applied to the photomultiplier tube 27. Further, the output level adjusting unit 94 performs calibration that will be described later to calculate the value of the constant X and the value of the constant A.
As can be seen from
Hereinbelow, a fluorescence detecting method used in the flow cytometer 10 will be described.
First, in the flow cytometer 10, the laser light source unit 22 emits, as irradiation light, laser light whose intensity is modulated at a predetermined frequency f.
Then, the light-receiving unit 26 receives fluorescence and outputs a fluorescence signal.
The control•processing unit 28 mixes the outputted fluorescence signal and a modulation signal for modulating the intensity of laser light L to generate fluorescence data including the phase shift angle of the fluorescence signal with respect to the modulation signal and intensity amplitude.
The phase shift calculating unit 86 of the analyzing device 80 calculates a phase shift angle θmeas from the generated fluorescence data. The phase shift correcting unit 88 calculates a phase shift angle θτ from the calculated phase shift angle θmeas according to the correction formula (4) to which the value of the constant X and the value of the constant A are given. Further, the fluorescence relaxation time calculating unit 90 calculates the fluorescence relaxation time τ of the fluorescent protein X1 using the phase shift angle θτ according to the formula: τ=tan(θτ)/(2πf). On the other hand, the fluorescence intensity calculating unit 92 calculates a fluorescence intensity by determining the absolute value of the generated fluorescence data.
The calculated fluorescence relaxation time, phase shift angle θτ, and fluorescence intensity are outputted from an output device not shown.
First, the output level adjusting unit 94 of the analyzing device 80 maximizes the control voltage V of the photomultiplier tube (hereinafter, referred to as “PMT”) 27 (Step S10). The maximization of the control voltage V is performed to achieve highly-sensitive detection of fluorescence even when the fluorescence is very weak. The control voltage is adjusted by the voltage adjusting section 26d.
Then, the output level adjusting unit 94 of the analyzing device 80 appropriately adjusts the ND filter 26b (Step S20). Attenuation of fluorescence by the ND filter is performed to prevent the output level of a fluorescence signal outputted from the PMT 27, which depends on the amount of light, from being saturated when the control voltage of the PMT 27 is maximized to maximize the sensitivity of the PMT 27. The ND filter 26b is set to, for example, intermediate level between minimum and maximum attenuation levels.
Then, the light source 22a emits laser light L whose intensity is modulated at a frequency f (Step S30). Then, the PMT 27 receives fluorescence emitted from the sample 12 irradiated with the laser light L when the sample 12 passes through the measurement point. Then, the PMT 27 outputs a fluorescence signal at an output level adjusted by the control voltage V (Step S40). The fluorescence signal is processed by the signal processing section 42 and the signal control section 44 so that fluorescence data including an Re component and an Im component is generated (Step S50). Then, the fluorescence intensity calculating unit 92 of the analyzing device 80 calculates a fluorescence intensity from the fluorescence data (Step S60). The fluorescence intensity is expressed as the absolute value of the fluorescence data.
Then, the output level adjusting unit 94 determines whether or not the set control voltage V is equal to or less than a predetermined voltage (Step S70).
When the determination result is negative, the output level adjusting unit 94 allows the voltage adjusting section 26d to reduce the control voltage V by a certain amount (Step S80). Then, the steps from Step S30 to Step S70 are repeated using the reduced control voltage V. That is, the control voltage V is adjusted in such a manner that the level of the fluorescence signal is reduced every time the steps from Step S30 to Step S70 are repeated. When the determination result in Step S70 is positive, the output level adjusting unit 94 further determines whether the fluorescence signal outputted from the PMT 27 is saturated or not using the change of the fluorescence intensity with respect to the control voltage V (Step S90).
The determination as to whether the fluorescence signal outputted from the PMT 27 is saturated or not may be made according to input given by an operator who has checked a graph displayed on a display (not shown) as a result of characteristics measurement. Alternatively, to determine whether the fluorescence signal is saturated or not, the analyzing device 80 may automatically analyze a graph illustrating a result of characteristics measurement displayed on a display (not shown). For example, as illustrated in
When the determination result is positive, the calibration process is returned to Step S20, and the steps from Step 20 to Step 80 are repeated.
When the determination result in Step 90 is negative, that is, when the PMT 27 is not in a saturated state, the output level adjusting unit 94 extracts the value of the constant X and the value of the constant A using a regression formula by approximation (Step S100) and the extracted value of the constant X and the extracted value of the constant A are stored in the memory 84 (Step S110). As the regression formula, the following formula (5) obtained by rearranging the above formula (4) is used.
θmeas=X−θτ−A·V(−1/2) (5)
wherein θτ=tan−1(2πfτ), f is the frequency (known) used to modulate the intensity of the laser light, and τ is the fluorescence relaxation time (known) of the fluorescent protein X1 for use in measurement.
The output level adjusting unit 94 extracts the value of the constant X and the value of the constant A from the measured phase shift angle θmeas using a regression formula such as the above formula (5) so that the phase shift angles θmeas predicted using the above formula (5) approximate the measured phase shift angles θmeas. In other words, the output level adjusting unit 94 extracts the value of the constant X and the value of the constant A so that the phase shift angle obtained by correcting the measured phase shift angle θmeasn using the above formula (4) (the right hand-side value of the formula (4)) approximates the phase shift angle θτ determined using the known fluorescence relaxation time τ. More specifically, the output level adjusting unit 94 extracts the value of the constant X and the value of the constant A so that a fluorescence relaxation time calculated from the corrected phase shift angle expressed on the right hand-side of the formula (4) approximates the known fluorescence relaxation time τ.
In the case illustrated in
As illustrated in
Therefore, the analyzing device 80 can accurately calculate the fluorescence relaxation time of fluorescence emitted from the fluorescent protein X1.
The fluorescence detecting apparatus, the fluorescence detecting method, and the fluorescence signal processing method according to the present invention have been described above in detail, but the present invention is not limited to the above embodiment. It is apparent that various changes and modifications may be made without departing from the scope of the present invention.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2010-001257 | Jan 2010 | JP | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/JP2011/000004 | 1/5/2011 | WO | 00 | 7/20/2012 |
