WO2010092728A1 - Dispositif de mesure de vitesse - Google Patents

Dispositif de mesure de vitesse Download PDF

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Publication number
WO2010092728A1
WO2010092728A1 PCT/JP2009/070745 JP2009070745W WO2010092728A1 WO 2010092728 A1 WO2010092728 A1 WO 2010092728A1 JP 2009070745 W JP2009070745 W JP 2009070745W WO 2010092728 A1 WO2010092728 A1 WO 2010092728A1
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WIPO (PCT)
Prior art keywords
light emission
frame
speed
irradiation
light
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PCT/JP2009/070745
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English (en)
Japanese (ja)
Inventor
修司 一谷
博哲 洪
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コニカミノルタオプト株式会社
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Application filed by コニカミノルタオプト株式会社 filed Critical コニカミノルタオプト株式会社
Priority to JP2010550420A priority Critical patent/JPWO2010092728A1/ja
Publication of WO2010092728A1 publication Critical patent/WO2010092728A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01P—MEASURING LINEAR OR ANGULAR SPEED, ACCELERATION, DECELERATION, OR SHOCK; INDICATING PRESENCE, ABSENCE, OR DIRECTION, OF MOVEMENT
    • G01P5/00—Measuring speed of fluids, e.g. of air stream; Measuring speed of bodies relative to fluids, e.g. of ship, of aircraft
    • G01P5/18—Measuring speed of fluids, e.g. of air stream; Measuring speed of bodies relative to fluids, e.g. of ship, of aircraft by measuring the time taken to traverse a fixed distance
    • G01P5/20—Measuring speed of fluids, e.g. of air stream; Measuring speed of bodies relative to fluids, e.g. of ship, of aircraft by measuring the time taken to traverse a fixed distance using particles entrained by a fluid stream
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/10—Investigating individual particles
    • G01N2015/1027—Determining speed or velocity of a particle

Definitions

  • the present invention relates to a speed measuring device.
  • the movement distance of each blood cell is obtained from a plurality of blood flow images obtained by continuously photographing blood vessels, and the movement distance and the frame of the camera are obtained.
  • a method for calculating the velocity of each blood cell from the rate value has been proposed. In this method, a high-speed camera having a frame rate of 500 fps is used.
  • a method for measuring the velocity of fine particles other than blood cells has been proposed.
  • the strobe is caused to emit light twice at a high speed when photographing a jet from a nozzle, and the moving distance of particles in the jet from the obtained multiple-exposure image.
  • a method for calculating the velocity of the particle from the moving distance and the light emission interval of the strobe has been proposed. In this method, the strobe is continuously emitted at a time interval of 1.5 ⁇ sec.
  • Non-Patent Document 1 it is not necessary to recognize and track individual particles in the airflow by pattern matching a plurality of airflow visualization images continuously captured by a high-speed camera.
  • a method of creating a two-dimensional velocity map of airflow has also been proposed.
  • Patent Literature 1 and Non-Patent Literature 1 it is necessary to photograph at least two frames of the same blood cell or particle within the same imaging range, so that it is expensive depending on the velocity of the blood cell or particle. A high-speed camera is required, and the cost of the apparatus increases.
  • the blood cells are caused to flow through a predetermined flow path at a speed of about 3 to 7 mm / sec. Since the length of the flow path is about 30 ⁇ m, at least two frames of the same blood cell moving in this flow path are photographed to obtain an image as shown in FIGS. 18A and 18B.
  • the speed of particles can be calculated by continuously emitting light at high speed without requiring a high-speed camera
  • the density is high like blood cells in blood.
  • FIG. 18C multiple exposure may be performed on an image in which a plurality of blood cells overlap. As a result, complicated analysis processing such as separating overlapping blood cells and specifying each of them is necessary, and analysis cost increases.
  • the present invention has been made in view of the above circumstances, and an object thereof is to provide a speed measuring device capable of measuring the speed of an object at low cost.
  • Photographing means for photographing an object
  • An irradiating means (strobe) that irradiates light within the photographing range of the photographing means for a time shorter than the exposure time of the one frame for one frame in the photographing means
  • Light emission control means for controlling the irradiation means to switch between a light emission state and a non-light emission state
  • Speed calculating means for calculating the speed of the moving object from the image obtained by the photographing means
  • a speed measuring device comprising:
  • the photographing means includes Photographing the object at the light emission timing at which the irradiation means emits light during the exposure time of one frame
  • the light emission control means includes Control the light emission of the irradiation means so that the time interval of the light emission timing between two consecutive frames is shorter than the shooting time of the frame, and the light emission state in each frame is one
  • the speed calculation means includes Obtaining a moving distance of the object from two images obtained in the two frames,
  • the invention according to claim 4 is the speed measuring device according to any one of claims 1 to 3, Other irradiation that has a spectral intensity characteristic different from that of the irradiation unit and irradiates light within the imaging range of the imaging unit for a time shorter than the exposure time of the one frame for each frame of the imaging unit.
  • the time interval of other light emission timings emitted by the other irradiation means between two consecutive frames in a combination different from the irradiation means is made shorter than the shooting interval of the frame, and in each frame
  • the photographing unit photographs the object at the other light emission timing in the exposure time of one frame, and spectral sensitivity characteristics corresponding to the spectral intensity characteristics of the irradiation unit and the other irradiation unit.
  • a plurality of image sensors having The light emission control means and the other light emission control means are configured to emit light from the irradiation means and the other irradiation means so that the light emission states are different from each other within the exposure time of the same frame in the photographing means.
  • Control The speed calculation means obtains a moving distance of the object from two images obtained in two frames where the object is irradiated from the other irradiating means, and the moving distance and the distance between the two frames are calculated. The speed of the object is calculated from time intervals of other light emission timings.
  • the invention according to claim 7 provides: Photographing means (camera) for photographing an object; Exposure control means for controlling the exposure time and exposure timing of the photographing means; Irradiating means for irradiating light within the imaging range of the imaging means; Speed calculating means for calculating the speed of the moving object from the image obtained by the photographing means;
  • a speed measuring device comprising: The exposure control means controls the exposure so that the time interval of the exposure timing between two consecutive frames is shorter than the shooting interval of the frames, The speed calculation means includes The moving means calculates the moving distance of the object from the two images obtained in the two frames by shooting the object, and the moving distance and the time interval of the exposure timing between the two frames From the above, the velocity of the object is calculated.
  • the invention provides: Photographing means (camera) for photographing an object; A plurality of irradiation means for irradiating light within the imaging range of the imaging means; Light emission control means for controlling the plurality of irradiation means to switch between a light emitting state and a non-light emitting state; Speed calculating means for calculating the speed of the moving object from the image obtained by the photographing means;
  • a speed measuring device comprising: The plurality of irradiation means have different spectral intensity characteristics, The imaging unit has a plurality of imaging elements having spectral sensitivity characteristics corresponding to the spectral intensity characteristics of the plurality of irradiation units,
  • the light emission control means makes the plurality of irradiation means emit light only once at different light emission timings within the exposure time of the same frame in the photographing means,
  • the speed calculation means obtains a moving distance of the object from a plurality of images in the same frame obtained by the plurality of image sensors,
  • the invention according to claim 11 is the speed measuring device according to claim 10,
  • the plurality of irradiation means is three or more,
  • the light emission control unit is characterized in that each of the plurality of irradiation units is set in a light emission state so that time intervals between light emission timings of the irradiation units are different from each other.
  • an object at the light emission timing within the exposure time of one frame is photographed, and the time interval of the light emission timing between two consecutive frames is greater than the exposure time of one frame. Therefore, separate images having a time interval shorter than the frame shooting interval can be obtained from the two consecutive frames. That is, high-speed shooting at a rate higher than the frame rate of the shooting means can be performed.
  • the irradiation unit is controlled so that the light emission state in each frame becomes one, an image is obtained from each of the two frames. Even when a dense object is measured, a plurality of objects are There is no multiple exposure on overlapping images. This eliminates the need for complicated analysis processing for separating the overlapping objects and specifying each of them. Therefore, unlike the conventional case, an expensive high-speed camera does not require complicated analysis processing with high analysis cost, and the speed of the object can be measured at low cost.
  • the light emission of the irradiation means having different spectral intensity characteristics and the other irradiation means are controlled so that the light emission states are different from each other within the exposure time of the same frame.
  • Photographing is performed using a plurality of imaging elements having spectral sensitivity characteristics corresponding to the spectral intensity characteristics of the irradiation means and the other irradiation means.
  • the frame shooting interval is shorter than the frame shooting interval. Even separate images with short time intervals are obtained. That is, high-speed shooting at a rate higher than the frame rate of the shooting means can be performed.
  • the exposure control unit controls the exposure state in each frame to be one, an image can be obtained from each of the two frames, and a plurality of objects can be obtained even when a dense object is a measurement target. Are not overexposed on the overlapping images. This eliminates the need for complicated analysis processing for separating the overlapping objects and specifying each of them. Therefore, unlike the conventional case, an expensive high-speed camera does not require complicated analysis processing with high analysis cost, and the speed of the object can be measured at low cost.
  • a plurality of irradiation means having different spectral intensity characteristics are brought into a light emitting state at different light emission timings, corresponding to the spectral intensity characteristics of each irradiation means.
  • Photographing is performed using a plurality of imaging elements having spectral sensitivity characteristics.
  • the eleventh aspect of the present invention since the three or more irradiating means are set in the light emitting state so that the time intervals between the light emission timings of the irradiating means are different from each other, at least two sets of images having different time intervals are displayed. You can take a picture. Thereby, the speed of a fast object can be calculated from an image having a short time interval, and the speed of a slow object can be calculated from an image having a long time interval. That is, the speeds of two or more types of objects having different speeds can be measured.
  • FIG. 1 is a block diagram showing the overall configuration of a blood test apparatus 100 including a speed measuring device according to the present invention.
  • the blood test apparatus 100 guides blood from the supply tank 4 through the filter 2 to the discharge tank 5 and measures the velocity of blood cells in the blood from the information acquired in the process. This is to check the fluidity.
  • blood test apparatus 100 mainly includes a speed measurement apparatus 1 that measures the speed of blood cells, a filter 2 that is a blood flow path for measuring the speed of blood cells, and a blood flow in filter 2. And a differential pressure control unit 3 for controlling the pressure.
  • the blood test apparatus 100 includes a plurality of solution bottles connected to a flow path via a mixer 6 so that a liquid such as physiological saline or a physiologically active substance can be mixed with blood and guided to the filter 2. 7 etc. are further provided.
  • the differential pressure control unit 3 controls the pressurizing pump 8 and the decompressing pump 9 to adjust the differential pressure before and after the filter 2. By doing so, the filter 2 flows by a desired amount.
  • the valve 4 a of the supply tank 4 and the like are integrated and controlled by the sequence control unit 10.
  • the speed measuring device 1 includes a TV camera 11, a strobe 12, a frame memory 13, a timing control unit 14, a personal computer (PC) 15, and a display 16.
  • the TV camera 11 is installed facing the glass flat plate 24 so that a predetermined range of the flow path portion 25 in the filter 2 is an imaging range, and exposure time of one frame (also referred to as exposure time or shutter speed). ),
  • the blood cells in the blood in the flow path portion 25 at the light emission timing when the strobe 12 emits light are photographed over the glass plate 24 (see FIG. 2).
  • the TV camera 11 has an image sensor 111 that is a CCD image sensor.
  • the strobe 12 is an irradiating means for irradiating light within the photographing range of the TV camera 11, and in the present embodiment, it is capable of continuous light emission at least at a light emission time of 1/3000 sec.
  • the frame memory 13 is storage means for storing a blood flow image taken by the TV camera 11.
  • the timing control unit 14 controls the shooting timing of the imaging device 111 of the TV camera 11 and controls the light emission timing by switching the strobe 12 between the light emitting state and the non-light emitting state.
  • the personal computer 15 includes an arithmetic processing unit 151 that calculates the velocity of a moving blood cell from a blood flow image captured by the TV camera 11 and stored in the frame memory 13. As such an arithmetic processing unit 151, a conventionally known one can be used.
  • the personal computer 15 is configured to be able to control the timing control unit 14.
  • the display 16 displays a blood flow image taken by the TV camera 11.
  • FIG. 2 is a sectional view of the filter 2.
  • the filter 2 includes a base plate 21, silicon single crystal substrates 22 and 22, an outer plate 23, and a glass flat plate 24.
  • the base plate 21 is formed in a flat plate shape, and has an introduction hole 21a that communicates the upper surface near the center and the outer surface, and a discharge hole 21b that communicates the upper surface near one side end and the outer surface. .
  • the introduction hole 21a and the discharge hole 21b are connected to the supply tank 4 and the discharge tank 5 from the outer surface of the base plate 21 via a blood tube (not shown).
  • the two silicon single crystal substrates 22 and 22 are both formed in a substantially flat plate shape, and are arranged in parallel on the upper surface of the base plate 21 with a predetermined gap therebetween.
  • An introduction hole 21 a of the base plate 21 is opened in the gap between the two silicon single crystal substrates 22 and 22.
  • a protruding portion 22a extends in the direction in which the silicon single crystal substrates 22 and 22 are juxtaposed (the X direction in the drawing).
  • a plurality of hexagonal bank portions 22b are arranged in the X direction with the top surface in contact with the glass flat plate 24 (see FIG. 3).
  • the outer plate 23 is fixed to the upper surface end of the base plate 21 so as to surround the silicon single crystal substrates 22 and 22.
  • a predetermined gap is provided between the outer plate 23 and the silicon single crystal substrates 22, 22, and a discharge hole 21 b of the base plate 21 is opened in this gap.
  • the glass flat plate 24 is formed in a flat plate shape and is fixed to the upper surface of the outer plate 23. Further, between the lower surface of the glass flat plate 24 and the upper surface of the raised portion 22a, a channel portion 25 of a fine channel group is formed.
  • FIGS. 3A and 3B are diagrams for explaining the flow path section 25.
  • FIG. 3A is a view (plan view) of the flow path portion 25 as viewed from above, and
  • FIG. 3B is a side sectional view.
  • the flow path portion 25 includes a plurality of gates 25a formed between a plurality of bank portions 22b at the upper end of the raised portion 22a, and the gate 25a.
  • the upper terrace 25b is a space on the center side of the filter 2 (upper side in the drawing) and the downstream terrace 25c is a space outside the filter 2 (lower side in the drawing) with respect to the gate 25a.
  • the width t of the gate 25a is narrower than the blood cell diameter of red blood cells (about 8 ⁇ m) in the present embodiment.
  • the lengths la, lb, and lc in the width direction (Y direction in the drawing) of the raised portion 22a in the upstream terrace 25b, the gate 25a, and the downstream terrace 25c are all formed to be about 30 ⁇ m. Yes.
  • the blood introduced from the supply tank 4 through the introduction hole 21a passes through the flow path portion 25 and is then discharged to the discharge tank 5 through the discharge hole 21b.
  • blood cells for example, red blood cells
  • in the blood flowing through the flow path portion 25 first pass through the upstream terrace 25b, then pass through the gate 25a while being deformed, and finally pass through the downstream terrace 25c. Become.
  • pressure sensors E1 and E2 are provided upstream and downstream of the filter 2, and the pressure sensors E1 and E2 are configured to provide a difference between the measured filter upstream pressure P1 and filter downstream pressure P2.
  • the pressure is output to the pressure control unit 3.
  • the differential pressure control unit 3 is connected to the sequence control unit 10, the pressure pump 8, and the pressure reduction pump 9, and controls the differential pressure before and after the filter 2 in accordance with a control command from the sequence control unit 10. Yes. More specifically, the differential pressure control unit 3 controls the pressure pump 8 upstream of the filter 2 and the pressure reduction pump 9 downstream of the filter 2 so that the filter upstream pressure P1 and the filter downstream pressure P2 become predetermined pressures. To do. Note that the differential pressure control unit 3 and the sequence control unit 10 may be configured integrally with the personal computer 15.
  • FIGS. 4 (a) and 4 (b) are timing charts when blood velocity is imaged by the speed measurement device 1.
  • FIG. 4A and 4B are timing charts when blood velocity is imaged by the speed measurement device 1.
  • the timing control unit 14 sets the strobe so that the light emission state in each frame of the TV camera 11 is one, that is, the light is emitted only once in each frame. 12 light emission is controlled. More specifically, the timing control unit 14 determines that the flashing state of the strobe 12 is the last time point of the previous first frame and the subsequent second frame in two consecutive frames of the first frame and the second frame. The flash 12 is controlled to emit light for 1/3000 sec at any time.
  • the timing control unit 14 causes the strobe 12 to continuously emit light at a light emission time of 1/3000 sec at the boundary portion between the first frame and the second frame.
  • the flash 12 may not emit light at the last time point of the previous frame and the first time point of the subsequent frame, and the time interval of the light emission timing between two consecutive frames is a frame shooting time.
  • the interval (the reciprocal of the frame rate), that is, shorter than 1/60 sec.
  • the light emission time of the strobe 12 is shorter than the exposure time of one frame. That is, the strobe 12 emits light during the exposure time, and an object is photographed at that light emission timing.
  • the exposure time of one frame is substantially the same as the frame shooting interval.
  • the timing control unit 14 turns on the flash 12 at the last time point of the third frame and the first time point of the fourth frame, and the same applies to the fifth and subsequent frames.
  • the light emission of the strobe 12 is controlled.
  • the timing control unit 14 stops moving image shooting by the TV camera 11 and light emission of the strobe 12 when 1 sec elapses from the start of shooting.
  • the blood flow image thus photographed is stored in the frame memory 13 and displayed on the display 16.
  • the blood cell velocity is calculated by the arithmetic processing unit 151 of the personal computer 15.
  • the arithmetic processing unit 151 extracts all blood flow images from the frame memory 13.
  • the arithmetic processing unit 151 specifies the blood cell for calculating the velocity from the two blood flow images obtained in the two frames of the first frame and the second frame, and the movement of the blood cell between these frames Find the distance.
  • the arithmetic processing unit 151 calculates the blood cell velocity by dividing the moving distance of the blood cell by the time interval of the light emission timing between the two frames, that is, 1/3000 sec.
  • the arithmetic processing unit 151 calculates the blood cell velocity from the images obtained in the third frame and the fourth frame, similarly to the first frame and the second frame, and similarly calculates the velocity for the fifth and subsequent frames. To do. In this way, the speed calculation is performed once every two frames, and the speed calculation is performed about 30 times in 1 sec.
  • the speed measurement device 1 of the present embodiment an object at the light emission timing in the exposure time of one frame is photographed, and the time interval of the light emission timing between two consecutive frames is a frame. Therefore, separate blood flow images having a time interval shorter than the frame imaging interval can be obtained from the two consecutive frames. That is, high-speed shooting at a rate higher than the frame rate of the TV camera 11 can be performed.
  • the strobe 12 is controlled so that the light emission state in each frame becomes one, a blood flow image is obtained from each of the two frames, and multiple exposure is performed on a blood flow image in which a plurality of blood cells overlap. There is nothing. This eliminates the need for complicated analysis processing for separating and identifying the overlapping blood cells.
  • the timing controller 14 emits the strobe 12 at the last time point of the previous frame and the first time point of the subsequent frame in two consecutive frames.
  • the strobe 12 may be kept in a light emitting state at the last time of the previous frame and the first time of the subsequent frame.
  • each TV camera 11 is provided with a shutter that can be opened and closed at high speed, instead of the strobe 12, and the shutters of the two TV cameras 11 are set to 1/3000 sec. The same effect as described above can be obtained even when the TV camera 11 is exposed by being opened and closed with a shift.
  • FIGS. 5A and 5B are timing charts when blood flow is imaged by the velocity measuring device 1.
  • the timing control unit 14 controls the exposure time and the exposure timing in each frame of the TV camera 11. More specifically, the timing control unit 14 determines the exposure timing of the image sensor 111 at the last time point of the previous first frame and the subsequent second frame in two frames of the first frame and the second frame that are continuous. The exposure of the image sensor 111 is controlled so that the exposure is 1/3000 sec at any time.
  • the exposure by the image sensor 111 may not be continuous between the last time of the previous frame and the first time of the subsequent frame, and the time interval of the exposure timing between two consecutive frames is It may be shorter than the shooting interval (reciprocal of the frame rate), that is, 1/60 sec.
  • the light emission time of the strobe 12 is equal to or longer than the exposure time of one frame. That is, the strobe 12 emits light during the exposure time, and an object is photographed at that light emission timing.
  • FIG. 5B is a modification corresponding to FIG. In FIGS. 5A and 5B, the light emission time in one frame is substantially the same as the shooting interval of the frame. That is, the strobe 12 performs continuous irradiation.
  • a light source such as an LED having a large amount of light may be used instead of the strobe 12.
  • the timing control unit 14 exposes the image sensor 111 at the last time point of the third frame and the first time point of the fourth frame, and also for the fifth and subsequent frames. Similarly, the exposure timing of the image sensor 111 is controlled. Thereafter, the timing control unit 14 stops moving image shooting by the TV camera 11 and light emission of the strobe 12 when 1 sec elapses from the start of shooting. The blood flow image thus photographed is stored in the frame memory 13 and displayed on the display 16.
  • the blood cell velocity is calculated by the arithmetic processing unit 151 of the personal computer 15 in the same manner as in the above embodiment shown in FIGS. Specifically, the arithmetic processing unit 151 calculates the blood cell velocity by dividing the moving distance of the blood cell by the time interval of the exposure timing between two frames, that is, 1/3000 sec.
  • the image sensor 111 continuously exposes and captures images over two frames, so that it corresponds to a high-speed camera with a frame rate of 3000 fps while using a general-purpose camera with a frame rate of 60 ftp without multiple exposure.
  • Speed calculation in high-speed shooting can be performed.
  • the speed measurement device 1 in the first modification of the present embodiment it is possible to achieve the same effects as in the above-described embodiment.
  • FIG. 6 is a block diagram showing an overall configuration of the blood test apparatus 100 including the speed measuring device 1 according to the second modification.
  • the strobe 12 of the speed measuring device 1 in the second modification is composed of three strobes.
  • the image sensor 111 includes three image sensors corresponding to the strobe.
  • the three strobes 12 are xenon light sources that irradiate light within the photographing range of the TV camera 11, and in this embodiment, continuous light emission is possible at least with a light emission time of 1/3000 sec.
  • the three strobes 12 are an R strobe 12R, a G strobe 12G, and a B strobe 12B, and have different spectral intensity characteristics as shown in FIG.
  • the R strobe 12R emits red light (R)
  • the G strobe 12G emits green light (G)
  • the B strobe 12B emits blue light (B).
  • all are constituted like strobe 12 in the above-mentioned embodiment.
  • the TV camera 11 takes a picture of blood cells in the blood in the flow path portion 25 at the light emission timing when the R strobe 12R or the B strobe 12B emits light during the exposure time of one frame.
  • the TV camera 11 has three image sensors 111 that are CCD image sensors.
  • the three image sensors 111 are an R image sensor 111R, a G image sensor 111G, and a B image sensor 111B. As shown in FIG. 8, the three image sensors 111 have spectral sensitivity characteristics corresponding to the spectral intensity characteristics of each of the three flash units 12. Have.
  • the R image sensor 111R has high sensitivity only for red light from the R strobe 12R
  • the G image sensor 111G has high sensitivity only for green light from the G strobe 12G
  • the B image sensor 111B has high sensitivity only with respect to the blue light from the B strobe 12B.
  • the TV camera 11 includes an infrared cut filter (not shown) so that infrared light from the three strobes 12 that are xenon light sources does not enter the three image pickup devices 111. .
  • an infrared cut filter not shown
  • the timing control unit 14 controls the shooting timing of the three image sensors 111 of the TV camera 11 and controls the light emission timing by switching the three strobes 12 between the light emitting state and the non-light emitting state.
  • FIGS. 9A and 9B are timing charts when blood flow is imaged by the velocity measuring device 1
  • FIGS. 10A to 10C are the R imaging element 111R and the B imaging element 111B.
  • two strobes an R strobe 12R (also referred to as a first strobe) and a B strobe 12B (also referred to as a second strobe), and two R imaging elements 111R and B imaging corresponding thereto. This is an example in which imaging is performed by the imaging element of the element 111B.
  • the timing control unit 14 has one light emission state of the R strobe 12R (first strobe) and the B strobe 12B (second strobe) in each frame of the TV camera 11.
  • the light emission of the R strobe 12R and the B strobe 12B is controlled so that the R strobe 12R and the B strobe 12B emit light only once in each frame.
  • the timing controller 14 controls the light emission of the R strobe 12R and the B strobe 12B so that the light emission states are different from each other within the exposure time of the same frame in the TV camera 11.
  • the timing control unit 14 determines that the light emission state of the R strobe 12R is the last time point of the previous first frame and the second time after the second frame of the first frame and the second frame.
  • the light emission of the R strobe 12R is controlled so that the light is emitted for 1/3000 sec at any point in time at the first time point of the frame. That is, the timing control unit 14 causes the R strobe 12R to continuously emit light at a light emission time of 1/3000 sec at the boundary portion between the first frame and the second frame.
  • the timing control unit 14 determines whether the light emission state of the B strobe 12B is the last time point of the previous second frame and the subsequent third frame in two frames of the second frame and the third frame.
  • the light emission of the B strobe 12B is controlled so that the light is emitted for 1/3000 sec at any time at the first time.
  • the B strobe 12B is set to the light emitting state in two consecutive frames in a different combination from the two consecutive frames in which the R strobe 12R is in the light emitting state. That is, the timing control unit 14 causes the B strobe 12B to continuously emit light at a light emission time of 1/3000 sec at the boundary portion between the second frame and the third frame.
  • the light emission of the R strobe 12R and the B strobe 12B does not have to be continuous between the last time of the previous frame and the first time of the subsequent frame, and is caused by the same strobe between two consecutive frames. It is only necessary that the time interval of the subsequent light emission timing is shorter than the frame shooting interval, that is, 1/60 sec.
  • the timing control unit 14 causes the R strobe 12R to emit light at the last time point of the third frame and the first time point of the fourth frame, as in the first frame and the second frame, and the last time point of the fourth frame.
  • the B strobe 12B is turned on in the same manner as in the second and third frames. Thereafter, similarly, the R strobe 12R and the B strobe 12B continuously emit light alternately. Thereafter, the timing control unit 14 stops the moving image shooting of the TV camera 11 and the light emission of the R strobe 12R and the B strobe 12B when 1 sec has elapsed from the start of shooting.
  • the R strobe 12R and the B strobe 12B emit light at different timings in each frame except the first frame and the final frame.
  • the R image sensor 111R is sensitive only to red light from the R strobe 12R and the B image sensor 111B is sensitive only to blue light from the B strobe 12B
  • the R strobe 12R and the B strobe 12B are sensitive only to blue light from the B strobe 12B.
  • the blood flow images photographed at the respective light emission timings can be decomposed into channels having different wavelength regions by the R image sensor 111R and the B image sensor 111B.
  • a blood flow image captured with red light from the R strobe 12R by the R image sensor 111R is stored in the R channel as shown in FIG.
  • the blood flow image photographed with blue light is stored in the B channel as shown in FIG. However, in the first frame and the final frame, only the R strobe 12R emits light, so only the R channel is provided. These blood flow images are stored in the frame memory 13 for each channel and displayed on the display 16.
  • the blood cell velocity is calculated by the arithmetic processing unit 151 of the personal computer 15.
  • the arithmetic processing unit 151 extracts all blood flow images from the frame memory 13.
  • the arithmetic processing unit 151 identifies the blood cell for calculating the velocity from the two blood flow images of the R channel obtained in the two frames of the first frame and the second frame, and the relevant blood flow between these frames is determined. Find the distance traveled by the blood cell.
  • the arithmetic processing unit 151 calculates the blood cell velocity by dividing the moving distance of the blood cell by the time interval of the light emission timing between the two frames, that is, 1/3000 sec.
  • the arithmetic processing unit 151 obtains the moving distance of the blood cell between these frames from the two blood flow images of the B channel obtained in the two frames of the second frame and the third frame, and this blood cell Is divided by the time interval of the light emission timing between two frames, that is, 1/3000 sec, to calculate the blood cell velocity.
  • blood cell velocities are sequentially calculated from blood flow images of the same channel in two consecutive frames.
  • the speed calculation is performed about 60 times in 1 sec, which is about twice that of the above embodiment.
  • the light emitting state can be obtained within the exposure time of the same frame as well as the same effect as the above embodiment.
  • the light emission of the R strobe 12R and the B strobe 12B having different spectral intensity characteristics is controlled so as to have different timings, and R imaging with spectral sensitivity characteristics corresponding to the respective spectral intensity characteristics of the R strobe 12R and the B strobe 12B.
  • Photographing is performed using the element 111R and the B imaging element 111B.
  • separate blood flow images can be obtained from the channels corresponding to the spectral sensitivity characteristics of the R strobe 12R and the B strobe 12B in one frame without multiple exposure.
  • the measurement accuracy can be improved by increasing the number of times of speed calculation.
  • the strobe 12, R strobe 12R, and B strobe 12B emit light for 1/3000 sec in each frame. However, the exposure time of one frame per TV camera 11 is shorter. What is necessary is just to irradiate light only for the time.
  • the timing control unit 14 performs the R strobe 12R or the R strobe 12R at the last time point of the previous frame and the first time point of the subsequent frame, respectively, in two consecutive frames.
  • the B strobe 12B is assumed to emit light, as shown in FIG. 9B, the R strobe 12R or the B strobe 12B is continued at the last time of the previous frame and the first time of the subsequent frame. You may make it light-emit.
  • the speed measuring device 1 includes the R strobe 12R and the B strobe 12B that emit red light and blue light. Instead of the R strobe 12R and the B strobe 12B, a single strobe that emits white light is used. A color filter that can be switched between red and blue is provided between the strobe and the filter 2, and photographing may be performed while switching the color filter.
  • the R strobe 12R and the B strobe 12B are used to emit red light and the blue light B channel, but the G strobe 12G is also used to emit green light.
  • the G channel may be used (see FIGS. 7 and 8).
  • the color may not be three colors of RGB.
  • FIG. 11 is a flowchart of blood cell velocity measurement
  • FIG. 12 is a timing chart when blood flow is imaged
  • FIG. 13 is a flowchart of analysis processing for extracting a blood cell edge.
  • FIGS. 14A to 14D are diagrams showing examples of blood flow images in the edge extraction flow.
  • step S1 blood flows through the filter 2 (step S1). Specifically, first, blood to be measured is poured into the supply tank 4, and physiological saline or the like is added to the solution bottle 7 as necessary. Then, a predetermined differential pressure is applied to the filter 2 by the differential pressure control unit 3, and blood flows through the filter 2.
  • step S2 a moving image of the blood flow passing through the flow path portion 25 of the filter 2 is captured by the TV camera 11 (step S2).
  • the timing control unit 14 performs each of the three strobes 12 once at a timing that does not overlap each other at different light emission timings within the exposure time of the same frame in the TV camera 11. Only turn it on. More specifically, the timing control unit 14 causes the R strobe 12R to emit light for 1/3000 sec at the beginning of each frame, continuously causes the G strobe 12G to emit light for 1/3000 sec, and further continuously applies the B strobe 12B to 1. / Emit light for 3000 sec. Then, the timing control unit 14 stops the moving image shooting of the TV camera 11 and the light emission of the three strobes 12 when 1 sec has elapsed from the start of shooting.
  • the three strobes 12 emit light at different timings in any frame, when viewed in units of frames, all images are multiple-exposed.
  • the R image sensor 111R has high sensitivity only to red light from the R strobe 12R
  • the G image sensor 111G has high sensitivity only to green light from the G strobe 12G
  • the B image sensor 111B has B sensitivity 12B. Therefore, the blood flow image captured at each light emission timing of the three strobes 12 is a channel corresponding to the spectral sensitivity characteristic of each of the three image sensors 111, that is, It can be decomposed into channels having different wavelength regions. As a result, the irradiating means having different spectral intensity characteristics do not result in multiple exposure images.
  • a blood flow image captured with red light from the R strobe 12R and blue light from the B strobe 12B is viewed in units of frames. As shown in FIG. 10A, the image is multiple-exposed. However, the blood flow image captured in response to the red light from the R strobe 12R by the R image sensor 111R is decomposed and stored in the R channel as shown in FIG. 10B, and is stored by the B image sensor 111B. The blood flow image photographed in response to the blue light from the B strobe 12B is stored after being decomposed into B channels as shown in FIG. 10 (c). That is, the image is not multiple-exposed in each channel having different spectral sensitivity characteristics.
  • the blood flow image is analyzed by the arithmetic processing unit 151 of the personal computer 15 and the blood cell edge is extracted (step S3). Since the blood flow image decomposed into each channel has different gradation characteristics in each channel (see FIG. 14A), an error is likely to occur in the analysis. Therefore, the blood cell edge is extracted by using a shadow that hardly causes a difference in each channel, and the blood cell is specified.
  • contrast adjustment is performed (step S31).
  • the arithmetic processing unit 151 unifies the dynamic range by linearly interpolating the brightness and darkness of the blood flow image for each channel. For example, when the gradation is 8 bits, linear interpolation is performed by setting the dark part to 0 and the bright part to 255. However, a method of balancing the histogram between channels may be used. By this contrast adjustment, the overall brightness is similar between the channels (see FIG. 14B).
  • step S32 binarization is performed so that only the blood cell edge remains (step S32).
  • the arithmetic processing unit 151 binarizes the blood flow image whose contrast has been adjusted using a different threshold for each channel.
  • This threshold value is a value suitable for the gradation characteristics for each channel, and by using such a threshold value, it is possible to accurately leave the edges of blood cells that are differently attached to the blood flow image for each channel (see FIG. 14 (c)).
  • step S33 the binarized edge is thinned. This thinning eliminates the difference in edge blur between the channels (see FIG. 14D). This processing is effective because it is easy to improve the matching accuracy, particularly when a plurality of images are compared by pattern matching.
  • the blood cell velocity is calculated by the arithmetic processing unit 151 as shown in FIG. 11 (step S4).
  • the arithmetic processing unit 151 obtains the moving distance of the blood cell between the two images from two images of the three images for each channel obtained by the three imaging elements 111 for each frame. Then, the arithmetic processing unit 151 calculates the blood cell velocity by dividing the moving distance of the blood cells by the time interval between the light emission timings of the strobes 12, that is, 1/3000 sec.
  • the calculation is performed twice for each frame. Speed calculation is performed, and speed calculation is performed about 120 times in 1 second.
  • a plurality of strobes 12 having different spectral intensity characteristics are continuously emitted at high speed within the exposure time of the same frame, so that a frame rate of 3000 fps can be used while using a general-purpose camera with a frame rate of 60 fps without multiple exposure. It is possible to calculate the speed in high-speed shooting equivalent to the high-speed camera.
  • the three strobes 12 having different spectral intensity characteristics are brought into the light emission state at different light emission timings within the exposure time of the same frame. Photographing is performed using three imaging elements 111 having different spectral sensitivity characteristics corresponding to the spectral intensity characteristics. Thereby, separate blood flow images having a time interval shorter than the exposure time of one frame can be obtained from the channel corresponding to each spectral sensitivity characteristic in one frame without multiple exposure. That is, high-speed shooting at a rate higher than the frame rate of the TV camera 11 can be performed.
  • blood flow images are obtained from the channels corresponding to each spectral sensitivity characteristic, blood flow images are obtained from the two frames, and multiple blood cells are exposed to multiple blood flow images. There is no. This eliminates the need for complicated analysis processing for separating and identifying the overlapping blood cells.
  • the three strobes 12 are in a light emitting state only once within the exposure time of the same frame, it is possible to reliably prevent multiple exposure for each strobe 12 having different spectral intensity characteristics.
  • the blood flow image obtained for each channel corresponding to the spectral sensitivity characteristics of each of the three imaging elements 111 is binarized with a different threshold for each channel, the blood flow image for each channel is different. It is possible to accurately extract the blood cell edge. Therefore, blood cells can be specified more accurately, and thus the blood cell velocity can be calculated more accurately.
  • FIG. 15 is a timing chart when blood flow is imaged in this modification.
  • the timing control unit 14 when the blood flow is photographed with the TV camera 11, the timing control unit 14 is configured so that the time intervals between the light emission timings of the strobes 12 are different from each other. Each is turned on. More specifically, the timing control unit 14 causes the R strobe 12R and the G strobe 12G to continuously emit light by 1/3000 sec at the beginning of each frame, and then the B strobe 12B is turned 1/3000 sec after 45/3000 sec. Make it emit light.
  • the three strobes 12 by causing the three strobes 12 to emit light at different time intervals, it is possible to simultaneously measure the speed of two types of blood cells having different speeds.
  • white blood cells are slower in speed than red blood cells, and do not move by 1 pix in high-speed imaging at intervals of 1/3000 sec. Therefore, as in this modification, the last B strobe 12B is delayed to emit light, whereby the velocity of red blood cells is calculated from the blood flow image by the light emission of the first R strobe 12R and G strobe 12G, and the next G
  • the velocity of white blood cells can be calculated from the blood flow images obtained by the light emission of the strobe 12G and the B strobe 12B.
  • a strobe 12 may be added to simultaneously measure three or more types of blood cells having different speeds.
  • the time interval between the light emission timings of the strobes 12 is not limited to the same effect as the above embodiment. Since the three or more strobes 12 are made to emit light so that they are different, at least two sets of blood flow images with different time intervals can be taken. Thereby, the speed of a fast blood cell can be calculated from a blood flow image with a short time interval, and the speed of a slow blood cell can be calculated from a blood flow image with a long time interval. That is, the speed of two or more blood cells having different speeds can be measured.
  • the velocity measuring device 1 calculates the velocity of blood cells in the blood.
  • the velocity measuring device 1 calculates the velocity of an object such as fine particles, not the velocity of the blood cells. Also good.
  • the velocity measuring device 1 extracts blood cell edges in order to identify blood cells
  • the velocity may be calculated using a color portion as follows.
  • particles composed of pigments used for color materials such as printing inks, electrophotographic toners, and ink jets are cyan (C), magenta (M), and yellow (Y). That is, it has a spectral reflectance that is complementary to RGB. Therefore, when the velocity of the particles having the spectral characteristics is measured by the velocity measuring device 1, as shown in FIG. 17, the M and Y color materials are easily captured in the R channel, and the C color material is not easily captured.
  • the G channel is easy to capture the C and Y color materials, and the M color material is difficult to capture.
  • the B channel is easy to capture the C and M color materials, and the Y color material is difficult to capture.
  • the edge is deleted and the color portion of the color material is left as a pattern, and then the image of each channel is compared to calculate the speed.
  • the speed can be calculated only for the Y color portion.
  • the speed of the C color portion can be calculated for the G channel and B channel images
  • the speed of the M color portion can be calculated for the B channel and R channel images.
  • the speed can be calculated without the need to specify the object.
  • the speed of an object that moves slowly between the channels is set. It is better to measure.
  • the speed measuring device 1 includes three strobes 12 that emit RGB colors. Instead of the three strobes 12, one strobe that emits white light, and a filter 2 from the strobe. In the meantime, a color filter that can be switched between red and blue may be provided, and photographing may be performed while switching the color filter.
  • the three strobes 12 may not emit RGB colors, and may emit light that does not overlap the wavelength regions of the spectral intensity characteristic and the spectral sensitivity characteristic so as not to be exposed multiple times.
  • Speed measurement device 11 TV camera (photographing means) 12 Strobe (irradiation means) 12B B strobe (first strobe, irradiation means) 12G G strobe (irradiation means) 12R R strobe (second strobe, irradiation means) 14 Timing control unit (light emission control means, other light emission control means, exposure control means) 15 PC 111 image pickup device 111B B image pickup device 111G G image pickup device 111R R image pickup device 151 arithmetic processing unit (speed calculation means)

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  • Engineering & Computer Science (AREA)
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  • General Physics & Mathematics (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)

Abstract

La présente invention concerne la mesure de la vitesse d'un objet à faible coût. L'invention concerne un dispositif de mesure de la vitesse équipé d'une caméra de télévision (11) permettant la capture d'une image d'une cellule sanguine, un stroboscope (12) pour l'application de lumière dans une distance de capture d'images de la caméra de télévision (11) pour un intervalle de temps plus court que le temps d'exposition d'une image de la caméra de télévision (11) dans chaque trame, une unité de commande de synchronisation (14) pour commander l'émission de lumière du stroboscope (12) de sorte que l'intervalle de temps entre les instants d'émission de lumière entre deux images consécutives soit plus court que le temps d'exposition d'une image et que l'état d'émission de lumière se produise une fois dans chaque trame, et une unité de traitement de calcul (151) pour rechercher la distance de déplacement de la cellule sanguine à partir de deux images obtenues dans les deux trames et pour calculer la vitesse de la cellule sanguine entre les instants d'émission de lumière entre les deux images.
PCT/JP2009/070745 2009-02-16 2009-12-11 Dispositif de mesure de vitesse WO2010092728A1 (fr)

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CN103926421A (zh) * 2014-05-07 2014-07-16 河北工业大学 一种用于细胞筛选的自相关速度探测装置
WO2018021035A1 (fr) * 2016-07-26 2018-02-01 ソニー株式会社 Dispositif, programme et procédé de traitement d'image.
CN110243739A (zh) * 2019-06-21 2019-09-17 衢州刚度智能科技有限公司 一种便携的火灾现场环境检测装置
JP2020126009A (ja) * 2019-02-06 2020-08-20 株式会社村田製作所 流路部品およびスラリー観察装置
JPWO2021177173A1 (fr) * 2020-03-05 2021-09-10

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JPH04361162A (ja) * 1991-06-07 1992-12-14 Ono Sokki Co Ltd 速度分布測定装置
JP2006300824A (ja) * 2005-04-22 2006-11-02 Kansai Electric Power Co Inc:The 流体可視化計測装置および流体可視化計測方法

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CN103926421A (zh) * 2014-05-07 2014-07-16 河北工业大学 一种用于细胞筛选的自相关速度探测装置
CN103926421B (zh) * 2014-05-07 2017-02-08 河北工业大学 一种用于细胞筛选的自相关速度探测装置
WO2018021035A1 (fr) * 2016-07-26 2018-02-01 ソニー株式会社 Dispositif, programme et procédé de traitement d'image.
JPWO2018021035A1 (ja) * 2016-07-26 2019-05-09 ソニー株式会社 画像処理装置および方法、内視鏡システム、並びにプログラム
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JP2020126009A (ja) * 2019-02-06 2020-08-20 株式会社村田製作所 流路部品およびスラリー観察装置
CN110243739A (zh) * 2019-06-21 2019-09-17 衢州刚度智能科技有限公司 一种便携的火灾现场环境检测装置
JPWO2021177173A1 (fr) * 2020-03-05 2021-09-10
JP7111275B2 (ja) 2020-03-05 2022-08-02 株式会社サタケ 光学式選別機

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