WO2008069062A1 - 血流速度画像化装置 - Google Patents
血流速度画像化装置 Download PDFInfo
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- WO2008069062A1 WO2008069062A1 PCT/JP2007/072907 JP2007072907W WO2008069062A1 WO 2008069062 A1 WO2008069062 A1 WO 2008069062A1 JP 2007072907 W JP2007072907 W JP 2007072907W WO 2008069062 A1 WO2008069062 A1 WO 2008069062A1
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- Prior art keywords
- blood flow
- flow velocity
- map
- pulsation
- arterial
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
- A61B3/1241—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes specially adapted for observation of ocular blood flow, e.g. by fluorescein angiography
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
- G01F1/704—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow using marked regions or existing inhomogeneities within the fluid stream, e.g. statistically occurring variations in a fluid parameter
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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
- G01P5/001—Full-field flow measurement, e.g. determining flow velocity and direction in a whole region at the same time, flow visualisation
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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
- G01P5/26—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 direct influence of the streaming fluid on the properties of a detecting optical wave
Definitions
- the present invention relates to a blood flow velocity imaging device for illuminating a biological tissue having blood cells with laser light and measuring and imaging a blood flow velocity based on a speckle signal reflected from the biological tissue. .
- an image sensor such as a solid-state imaging device (CCD or CMOS) is formed by irradiating a living tissue having blood cells such as the fundus of the subject's eye with a laser beam and using the reflected light of the blood cell force.
- the number of images is taken and stored continuously at predetermined time intervals, and a predetermined number of images are selected from the stored images, and the time variation of the output at each pixel of each image is selected.
- a blood flow velocity measuring device that calculates a value obtained by integrating the amounts and calculates a blood cell velocity (blood flow velocity) from this value.
- the blood flow distribution in the living tissue is calculated based on the calculated output fluctuation value of each pixel. It can also be displayed in color on a monitor screen as a three-dimensional image (blood flow map), and has been put into practical use, for example, as a fundus blood flow inspection apparatus.
- Patent Document 1 Japanese Patent Publication No. 5-28133
- Patent Document 2 Japanese Patent Publication No. 5-28134
- Patent Document 3 Japanese Patent Laid-Open No. 4242628
- Patent Document 4 JP-A-8-112262
- Patent Document 5 Japanese Patent Application Laid-Open No. 2003_164431
- Patent Document 6 Japanese Unexamined Patent Application Publication No. 2003-180641
- the pulsation of blood flow for each pixel of each image measured by a conventional blood flow velocity measuring device becomes blood flow data including statistical errors scattered around a certain blood flow value, and is therefore arranged in time series. In this case, it becomes a noisy profile instead of a clean pulsation profile, and it is very difficult to detect the peak time of pulsation necessary to distinguish between arterial and venous pulsatile regions. there were.
- the present invention applies and develops a conventional blood flow velocity measuring device, suppresses noise in noisy blood flow pulsation data, and displays an arterial pulsation part and a venous pulsation part on a map. It is an object of the present invention to provide a blood flow velocity imaging apparatus capable of displaying the above.
- the present inventor on a series of blood flow maps obtained by blood flow measurement for several seconds, shows changes in blood flow that appear periodically in synchronization with the heartbeat at each site in the observation field of view! / Analyzing and introducing a numerical value that can distinguish between an arterial sharp! / Part with a rising waveform and a part with a venous, gently rising and falling waveform, and distinguishing both parts to display a two-dimensional map It has succeeded in developing a method and apparatus that can determine which part is at risk of becoming ischemic.
- the invention described in claim 1 of the present invention includes a laser light irradiation system for irradiating a biological tissue having blood cells with laser light, and a plurality of images for detecting reflected light from the biological tissue.
- a light receiving system having a light receiving unit composed of an element, an image capturing unit that continuously captures a plurality of images in a predetermined time of one heartbeat or more based on a signal from the light receiving unit, and an image storage unit that stores the plurality of images
- a calculation unit for calculating a blood flow velocity in the living tissue from a temporal change in output signals of corresponding pixels of the stored plural images, and a display for displaying a two-dimensional distribution of the calculation result as a blood flow map
- the calculation part has a detection part for detecting arteries and veins from the plurality of images of one or more heartbeats, and the arterial is displayed on the blood flow map of the display part. Pulsating part (arterial map) and venous
- the way of displaying the arteriovenous map on the blood flow map is not limited at all.
- a blood flow map and an arteriovenous map can be superimposed (invented in claim 9), arranged, slidably superimposed, or combined and displayed.
- the blood flow velocity imaging apparatus of the present invention can be added or incorporated with known mechanisms and means as required.
- the detection unit calculates a skewness (skew value) on the basis of fluctuations in blood flow velocity arranged in time series for each pixel, so that the arterial 2.
- a skewness skew value
- the detection unit considers fluctuations in blood flow velocity arranged in time series for each pixel as a probability density function, and calculates an expected value of the probability density function.
- the detection unit calculates kurtosis on the basis of fluctuations in blood flow velocity arranged in time series for each pixel, and thereby detects arterial beats.
- the detection unit considers a fluctuation in blood flow velocity arranged in time series for each pixel as a probability density function, and estimates that the probability density function is the maximum. 2.
- a mode value (mode) that can be calculated is calculated, and an arterial pulsation part and a venous pulsation part are detected.
- the detection unit statistically processes a blood flow value of one or more neighboring pixels with respect to a blood flow value of each pixel including many statistical errors. Calculates the average value and outputs one or more pulsating components arranged in a time series with less noise required to detect arterial and venous pulsatile parts!
- the blood flow velocity imaging device according to any one of claims 2 to 5.
- the invention described in claim 7 is characterized in that the detection unit extracts a pulsation component after averaging the temporal fluctuation of the blood flow of each pixel over a plurality of heartbeats into one heartbeat. 6.
- the blood flow velocity imaging device according to any one of claims 2 to 5, wherein the blood flow velocity is imaged.
- the detection unit detects a time variation of blood flow of each pixel over a plurality of heartbeats, for example, an external synchronization signal synchronized with a heartbeat such as an electrocardiograph. 6.
- a pulsation component is extracted after cutting out one heartbeat.
- the invention described in claim 9 is characterized in that the display unit displays the arterial pulsation part and the venous pulsation part on the blood flow map in a superimposed manner.
- the blood flow velocity imaging device according to claim 1. The invention described in claim 9 is a force in which a blood flow map and an arteriovenous map are displayed on the display unit so as to overlap each other. It is included in distinguishing and displaying the arterial pulsatile part and the venous pulsatile part above. Further, the technical feature of displaying the arterial pulsation part and the venous pulsation part on the blood flow map is described in any one of claims 2 to 8 of the present invention. It goes without saying that other inventions can be combined.
- the ratio does not have to be 1: 1, and in order to see the ischemic state more clearly, numerical values in the respective maps are used. You can also multiply and apply weight. As a result of weighting, for example, by taking the AND of the slow part of the blood flow map and the venous part of the arteriovenous map, the part of the ischemic state on the fundus can be recognized.
- the detection unit is specifically configured as in the invention described in claims 2 to 8, so that a plurality of blood flows of one heartbeat or more From the map, the component force obtained by distinguishing and distinguishing the arterial pulsatile part from the venous pulsatile part, and the ability to obtain an easy-to-use segmented map, the force S! /, Results are obtained.
- the blood flow map obtained with the apparatus of the present invention shows venous pulsation, blood flow is low, and the region may be diseased. Will be medically meaningful [0019]
- a venous pulsation can be displayed in black while a black arterial pulsation is displayed in red.
- a blood flow map is displayed in a gray scale map, a region where the blood flow is fast is white and a region where the blood is slow is black.
- the part where the blood flow is low and the part where the disease is recognized becomes black on the blood flow map, and the arteriovenous map also becomes venous pulsation Since it becomes black, if the arteriovenous map is displayed so as to be transparent to some extent, the diseased site displayed in black becomes easy to concentrate.
- the above-described overlay display method is characterized in that when the maps are overlaid, the color arterio-venous vein map is transmitted translucently and the blood flow map is displayed in grayscale (monochrome).
- the dark-colored part in the arteriovenous map is a part where a pulsation peak is particularly slow among venous pulsations, and some kind of disorder is suspected.
- the colored part that is not black is a healthy part that is shaped like a peak in the first half of the beat.
- the black part of the blood flow map has a fairly gentle flow, and it is considered that some kind of obstacle is blocking the blood flow, which is also a place where a disease is suspected.
- this part is displayed in grayscale (monochrome), it is displayed as a force, a dark black. Therefore, when you look at the map where the translucent arteriovenous map that is a color map and the gray scale blood flow map are overlaid, the parts that are displayed in black are displayed black because each other's map is dark. This will clearly show the place where it is considered that there is some kind of disease.
- FIG. 1 is a diagram showing a main part of a configuration of a blood flow velocity imaging apparatus according to the present invention.
- FIG. 2 is a diagram showing the pulsation of blood flow in each pixel.
- FIG. 3 is a diagram showing beats that have been smoothed and normalized.
- FIG. 4 is a diagram (actual color map) in which the degree of distortion obtained from the present invention is mapped.
- FIG. 5 is a diagram showing a flow for calculating skewness.
- FIG. 6 is a diagram showing a flow for calculating a simplified skewness.
- FIG. 7 is a black and white map of the degree of distortion obtained from the present invention.
- FIG. 8 is a diagram showing a main part of the configuration of the blood flow velocity imaging apparatus according to claim 8.
- FIG. 1 shows an outline of an optical system in the configuration of the blood flow velocity imaging apparatus of the present invention, wherein 1 is a laser light irradiation system, 2 is a light receiving system, and E is an eye to be examined.
- the laser light of the laser light irradiation system 1 is irradiated, for example, onto the fundus Er, for example, as a living tissue of the eye E through the half mirror 13.
- the light receiving system 2 includes a light receiving lens 4, a CCD (solid-state imaging device) 5 as a light receiving unit, and an amplifier circuit 6.
- the laser reflected light from the fundus Er is focused on the CCD 5 as a biological tissue image by the light receiving lens 4.
- the CCD 5 has a large number of pixels on its light receiving surface, converts the biological tissue image formed by the light receiving lens 4 into an electrical signal, reads out the signal charge by the frame accumulation method, and outputs it as a video signal.
- the video signal is amplified by the signal amplification circuit 6, and the video signal amplified by the signal amplification circuit 6 is output to the analog processing means 7 that performs gain control and the like, and is converted into a digital signal by the A / D converter 8. Is done.
- 9 is a timing pulse generator
- 10 is an electronic shutter control means
- 11 is a solid-state imaging element driving means
- the timing pulse generator 9 is timed to the electronic shutter control means 10 and the signal selection means 12 Output a pulse.
- the solid-state image sensor driving means 11 is driven based on the timing noise.
- a digital signal as a video signal A / D converted by the A / D converter 8 is input to the signal selection means 12, and the signal selection means 12 is based on the timing norse from the timing pulse generator 9. 12 is recorded in the image recording means 13.
- the image recording means 13 functions as an image capturing unit that captures a plurality of images at a predetermined time interval.
- the image captured by the image recording means 13 is synthesized by the blood flow map synthesizing means 14, for example, a 1-frame image taken at 1/30 second intervals, and the 1-frame image data is an image. It is stored in the image storage 15 as a storage unit.
- the image signal stored in the image memory 15 is input to the arithmetic unit 16, and the arithmetic unit 16 performs arithmetic processing described later.
- Reference numeral 17 denotes a TV monitor as a display unit.
- FIG. 2 shows a waveform of pulsation data of each pixel obtained by the blood flow velocity imaging apparatus of the present invention.
- the horizontal axis is time
- the vertical axis is the blood flow value.
- a plurality of continuous blood flow maps of one heart beat or more! It is possible to trace the time fluctuation of the flow and detect the part that becomes the maximum peak, and use the part with the fastest peak time as the arterial pulsation part and the slow part as the venous pulsation part.
- the blood flow obtained with a blood flow meter is highly dispersed due to statistical errors, so it is very difficult to detect the pulsation peak for each pixel.
- the arterial vein is determined from the rising and falling profiles up to the peak even in a state where the statistical error is included to some extent.
- the graphs shown in Fig. 3 were obtained by plotting on the same graph.
- the number of pixels that can obtain the same waveform as in Fig. 3 and maintain a certain amount of blood vessel travel, for example, when the blood vessel width is 12 pixels, the number of pixels is 6 pixels centered around the pixel 36 pixels It is preferable to calculate from the above.
- the area to be averaged is good for circles, crosses, and rhombuses that are squares.
- the average number of pixels may be increased. For example, the structure power of tissue blood flow 3 ⁇ 40 pixel square, 10 pixels square centered on a certain pixel 100 pixels Calculate from the above.
- the averaged area may be a circle, a cross, or a diamond shape.
- the rise of the artery (1 in Fig. 3) has a steep rise and declines quickly after the peak, and the rise of the vein (2 in Fig. 3) is slower than that of the artery. Also, it can be seen that there is a characteristic that it falls more slowly after the peak. Arteries and veins, but also different before and after the position of the peak, to rise the way and falling how to peak, that there is a greater difference force s Such.
- the difference between the rising methods of the two is first evaluated as one method by the skewness (skew value), which is a third-order moment generally referred to in statistics. Is worth it.
- the skewness is a parameter that compares the target of the function. When this skewness is applied to the blood flow, it becomes a large positive value for arterial pulsations and small for venous pulsations. There is a tendency to become a value.
- Fig. 4 shows the result of actually calculating the skewness and displaying the map.
- the gray part is the arterial pulsation part
- the black part is the venous pulsation part.
- the red and warm colors are the arterial beating parts
- the colder colors such as black and blue (black in Fig. 4).
- It is a venous beating site.
- the connection of the warm-colored parts is connected like a blood vessel, and this part is considered to be an artery.
- the connection of cold-colored parts is a vein.
- the skewness is actually calculated according to the procedure shown in FIG. That is, first, blood flow values are calculated from a plurality of speckle images by the blood flow calculation of FIG. 5, and a blood flow map arranged in time series of one heartbeat or more is obtained. Next, by smoothing, the blood flow values are averaged using the pixels around each pixel for each blood flow map obtained above. Next, in heart rate synthesis, the smoothed time series blood flow map of one or more heart beats obtained above is detected, and the map with the lowest average blood flow value of the entire map is detected to detect multiple pulsations. . The top maps of each beat are averaged to form a top map of one heart beat that is synthesized. Sequentially, the first map force and the next map are averaged to create one heartbeat data by combining the heartbeats.
- Ik_n (m, n) a normalized blood flow value at the kth map pixel (m, n) from the head of the heart rate map synthesized into one heartbeat.
- Ik (m, n) Blood flow value at the kth map pixel (m, n) from the top of the heart rate map synthesized for one heart rate.
- I (m, n) min The minimum blood flow in the time-series data of the heart rate map synthesized for one heartbeat at pixel (m, n).
- I (m, n) max Maximum blood flow in the time-series data of the heart rate map synthesized for one heartbeat at pixel (m, n).
- Skew (m, n) Skewness at pixel (m, n).
- A Scale factor
- b Number of maps for one heartbeat
- k Map order from the top of one heartbeat
- kth Map order from the top of one heartbeat
- ave (m, n) First moment of the profile in which blood flow values normalized to heartbeat are arranged in time series In general, it is called the expected value.
- stdev (m, n): The square root of the secondary mode of the profile in which blood flow values normalized in heart rate are arranged in time series, and is generally called standard deviation.
- Il_n (m, n) Normalized blood flow value at the first map pixel (m, n) from the beginning of the heart rate map synthesized for one heart rate.
- the process in the middle of blood flow calculation and skewness calculation is omitted by the procedure shown in FIG. 6, and continuous time-series data of only one heartbeat is obtained from a plurality of heartbeat data.
- the arteriovenous pulsatile separation is also possible by the method of calculating the extracted skewness.
- the map is obtained by multiplying the coefficient A so that the user can easily identify the arteriovenous vein, and dividing the arteriovenous into a TV monitor or the like. indicate.
- FIG. 7 is a black and white map of the skewness obtained as described above.
- the expected value is a value that fluctuates depending on the position before and after the pulsation peak, and the kurtosis increases as the mode value of the pulsation is sharp! If there is a low value! /, There is a characteristic. In the case of arterial pulsation, the peak of the pulsation is sharp and the value is high. If it is a venous beat, the value is low and separation is easy.
- the pulsation profile plots the blood flow value having a statistical error, so the mode value is not necessarily clean pulsation data. It is not only the case where the mode value of the pulsation is calculated. Therefore, in order to calculate a plausible mode value, it is preferable to average the blood flow values around the pixels according to the invention of claim 6 to reduce the noise and calculate the mode value.
- the mode obtained from the pulsation profile averaged for each pixel is obtained in the first half of the heart rate for arterial pulsation, and venous is obtained with a slight delay, resulting in arterial and venous pulsations. Can be separated.
- the arteriovenous pulsation distinguishing method such as the skewness is based on the ability to detect the lowest frame from a plurality of heartbeats and combine them into one heartbeat, or the time series data of one heartbeat between the lowest frames.
- This is a method of mapping by performing skewness calculation after extracting.
- an external heartbeat such as an electrocardiogram as in the invention described in claim 8.
- the external synchronization signal arrives at the arithmetic unit in synchronism with the beat, with the strength of the beat having a certain propagation delay time force.
- the calculation unit can take into account the propagation delay time, detect weak beats! /, And extract the next lowest frame from the lowest frame to create beat data for one heartbeat.
- Figure 8 shows the procedure for this method.
- 18 is an external synchronization signal detector.
- a blood flow velocity imaging apparatus capable of displaying an arterial pulsation part and a venous pulsation part on a blood flow map.
- this device not only the arteriovenous separation of blood vessels, but also the part where the blood flow is low and the part where the disease is recognized is black on the blood flow map, and the arterial vein is also black. This makes it easier to identify the affected area where damage is likely to occur. Therefore, the blood flow velocity imaging apparatus of the present invention introduces a new scale to the fundus blood flow evaluation method, and is expected as a clinically extremely useful diagnostic tool.
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US12/517,017 US20100056936A1 (en) | 2006-12-01 | 2007-11-28 | Blood flow rate imaging device |
JP2008548238A JP4803520B2 (ja) | 2006-12-01 | 2007-11-28 | 血流速度画像化装置 |
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JP2006326370 | 2006-12-01 | ||
JP2006-326370 | 2006-12-01 |
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WO2014175154A1 (ja) | 2013-04-23 | 2014-10-30 | ソフトケア有限会社 | 血流画像診断装置及び診断方法 |
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WO2014175154A1 (ja) | 2013-04-23 | 2014-10-30 | ソフトケア有限会社 | 血流画像診断装置及び診断方法 |
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Also Published As
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US20100056936A1 (en) | 2010-03-04 |
JP4803520B2 (ja) | 2011-10-26 |
JPWO2008069062A1 (ja) | 2010-03-18 |
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