WO2023130197A1 - Mesures de vitesse d'écoulement en utilisant des systèmes d'imagerie - Google Patents

Mesures de vitesse d'écoulement en utilisant des systèmes d'imagerie Download PDF

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Publication number
WO2023130197A1
WO2023130197A1 PCT/CN2022/070035 CN2022070035W WO2023130197A1 WO 2023130197 A1 WO2023130197 A1 WO 2023130197A1 CN 2022070035 W CN2022070035 W CN 2022070035W WO 2023130197 A1 WO2023130197 A1 WO 2023130197A1
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WIPO (PCT)
Prior art keywords
image
images
tube
determining
detection portion
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PCT/CN2022/070035
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English (en)
Inventor
Peiyan CAO
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Shenzhen Xpectvision Technology Co., Ltd.
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Priority to PCT/CN2022/070035 priority Critical patent/WO2023130197A1/fr
Priority to TW111147554A priority patent/TW202328661A/zh
Publication of WO2023130197A1 publication Critical patent/WO2023130197A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0261—Measuring blood flow using optical means, e.g. infrared light
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
    • A61B6/4233—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/507—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for determination of haemodynamic parameters, e.g. perfusion CT
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2576/00—Medical imaging apparatus involving image processing or analysis
    • A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0275—Measuring blood flow using tracers, e.g. dye dilution

Definitions

  • a radiation detector is a device that measures a property of a radiation. Examples of the property may include a spatial distribution of the intensity, phase, and polarization of the radiation.
  • the radiation measured by the radiation detector may be a radiation that has transmitted through an object.
  • the radiation measured by the radiation detector may be electromagnetic radiation such as infrared light, visible light, ultraviolet light, X-ray, or ⁇ -ray.
  • the radiation may be of other types such as ⁇ -rays and ⁇ -rays.
  • An imaging system may include one or more image sensors each of which may have one or more radiation detectors.
  • a method comprising: introducing an object into a tube at an introduction site of the tube, wherein a liquid flows in the tube; capturing M images of a scene which includes a detection portion of the tube, wherein the detection portion is downstream with respect to the introduction site, and wherein M is an integer greater than 1; determining a time point at which the object reaches the detection portion based on at least an image of the M images; and determining a flow speed of the liquid in the tube based on the time point and an introduction time at which the object is introduced into the tube.
  • the M images are captured one image at a time.
  • the tube is a blood vessel
  • the liquid is blood
  • the object is a liquid different from the blood.
  • the object comprises NaCl or iodine.
  • the tube is a blood vessel
  • the liquid comprises a mix of blood and a solution different from the blood
  • the object comprises blood and does not comprise the solution.
  • the solution comprises NaCl or iodine.
  • said capturing the M images is performed using an image sensor which is stationary with respect to the detection portion.
  • said capturing the M images comprises: sending X-ray photons from a radiation source toward the detection portion; and capturing the M images by using radiation of the X-ray photons that has transmitted through the detection portion.
  • each photon of the X-ray photons has an energy in a range of 100 eV to 1000 eV.
  • said determining the flow speed of the liquid is also based on a travel distance along the tube between the introduction site and the detection portion.
  • the flow speed of the liquid is equal to the travel distance divided by a time duration of a time period from the introduction time to the time point.
  • the M images are captured periodically.
  • said determining the time point comprises: identifying a first image of the M images in which at least a portion of the object is present; and determining that the time point is a time at which the first image is captured.
  • said identifying the first image comprises determining that the first image and a second image of the M images which is captured before the first image is captured is different.
  • the second image is captured first.
  • said determining that the first image and the second image are different comprises determining that a first sum of all picture elements of the first image and a second sum of all picture elements of the second image are different.
  • said determining that the first sum and the second sum are different comprises determining that a magnitude of a difference between the first sum and the second sum exceeds a pre-specified threshold value.
  • said identifying the first image comprises determining that an average picture element value of an object region of the first image differs from an average picture element value of the remaining region of the first image by an amount whose magnitude exceeds a pre-specified threshold value.
  • said determining the flow speed is also based on (A) a travel distance along the tube between the introduction site and the detection portion and (B) a position of the object region in the first image.
  • Also disclosed herein is a method, comprising: introducing P objects into a tube, wherein a liquid flows in the tube, wherein the P objects are introduced periodically one object at a time at an introduction site of the tube and at an introduction frequency, and wherein P is an integer greater than 1; capturing Q images of a scene which includes a detection portion of the tube, wherein the Q images are captured one image at a time, wherein the detection portion is downstream with respect to the introduction site, and wherein Q is an integer greater than 1; determining a same time duration which it takes for each of the P objects to travel in the tube from the introduction site to the detection portion based on (A) the Q images, and (B) the introduction frequency; and determining a flow speed of the liquid in the tube based on the time duration.
  • said determining the time duration comprises: determining, for each image of the Q images, a sum of all picture elements of said each image, resulting in Q sums which constitute a first function in time domain; applying Fourier transform to the first function resulting in a second function in frequency domain, wherein the second function comprises a particular component corresponding to the introduction frequency; applying reverse Fourier transform to the particular component of the second function, resulting in a third function in time domain; and determining the time duration based on the third function.
  • the Q images are captured periodically.
  • the Q images are captured at a frequency higher than the introduction frequency.
  • Fig. 1 schematically shows a radiation detector, according to an embodiment.
  • Fig. 2 schematically shows a simplified cross-sectional view of the radiation detector, according to an embodiment.
  • Fig. 3 schematically shows a detailed cross-sectional view of the radiation detector, according to an embodiment.
  • Fig. 4 schematically shows a detailed cross-sectional view of the radiation detector, according to an alternative embodiment.
  • Fig. 5 schematically shows a top view of a radiation detector package including the radiation detector and a printed circuit board (PCB) , according to an embodiment.
  • PCB printed circuit board
  • Fig. 6 schematically shows a cross-sectional view of an image sensor including the packages of Fig. 5 mounted to a system PCB (printed circuit board) , according to an embodiment.
  • PCB printed circuit board
  • FIG. 7A –Fig. 7B schematically show an imaging system in operation for blood flow speed measurement, according to an embodiment.
  • Fig. 8 shows a flowchart generalizing the operation of the imaging system, according to an embodiment.
  • Fig. 9 shows another flowchart generalizing the operation of the imaging system, according to an alternative embodiment.
  • Fig. 1 schematically shows a radiation detector 100, as an example.
  • the radiation detector 100 may include an array of pixels 150 (also referred to as sensing elements 150) .
  • the array may be a rectangular array (as shown in Fig. 1) , a honeycomb array, a hexagonal array, or any other suitable array.
  • the array of pixels 150 in the example of Fig. 1 has 4 rows and 7 columns; however, in general, the array of pixels 150 may have any number of rows and any number of columns.
  • Each pixel 150 may be configured to detect radiation from a radiation source (not shown) incident thereon and may be configured to measure a characteristic (e.g., the energy of the particles, the wavelength, and the frequency) of the radiation.
  • a radiation may include radiation particles such as photons (X-rays, gamma rays, etc. ) and subatomic particles (alpha particles, beta particles, etc. )
  • Each pixel 150 may be configured to count numbers of particles of radiation incident thereon whose energy falls in a plurality of bins of energy, within a period of time. All the pixels 150 may be configured to count the numbers of particles of radiation incident thereon within a plurality of bins of energy within the same period of time. When the incident particles of radiation have similar energy, the pixels 150 may be simply configured to count numbers of particles of radiation incident thereon within a period of time, without measuring the energy of the individual particles of radiation.
  • Each pixel 150 may have its own analog-to-digital converter (ADC) configured to digitize an analog signal representing the energy of an incident particle of radiation into a digital signal, or to digitize an analog signal representing the total energy of a plurality of incident particles of radiation into a digital signal.
  • ADC analog-to-digital converter
  • the pixels 150 may be configured to operate in parallel. For example, when one pixel 150 measures an incident particle of radiation, another pixel 150 may be waiting for a particle of radiation to arrive. The pixels 150 may not have to be individually addressable.
  • the radiation detector 100 described here may have applications such as in an X-ray telescope, X-ray mammography, industrial X-ray defect detection, X-ray microscopy or microradiography, X-ray casting inspection, X-ray non-destructive testing, X-ray weld inspection, X-ray digital subtraction angiography, etc. It may be suitable to use this radiation detector 100 in place of a photographic plate, a photographic film, a PSP plate, an X-ray image intensifier, a scintillator, or another semiconductor X-ray detector.
  • Fig. 2 schematically shows a simplified cross-sectional view of the radiation detector 100 of Fig. 1 along a line 2-2, according to an embodiment.
  • the radiation detector 100 may include a radiation absorption layer 110 and an electronics layer 120 (which may include one or more ASICs or application-specific integrated circuits) for processing or analyzing electrical signals which incident radiation generates in the radiation absorption layer 110.
  • the radiation detector 100 may or may not include a scintillator (not shown) .
  • the radiation absorption layer 110 may include a semiconductor material such as silicon, germanium, GaAs, CdTe, CdZnTe, or a combination thereof.
  • the semiconductor material may have a high mass attenuation coefficient for the radiation of interest.
  • the radiation absorption layer 110 may include one or more diodes (e.g., p-i-n or p-n) formed by a first doped region 111, one or more discrete regions 114 of a second doped region 113.
  • the second doped region 113 may be separated from the first doped region 111 by an optional intrinsic region 112.
  • the discrete regions 114 may be separated from one another by the first doped region 111 or the intrinsic region 112.
  • the first doped region 111 and the second doped region 113 may have opposite types of doping (e.g., region 111 is p-type and region 113 is n-type, or region 111 is n-type and region 113 is p-type) .
  • each of the discrete regions 114 of the second doped region 113 forms a diode with the first doped region 111 and the optional intrinsic region 112.
  • the radiation absorption layer 110 has a plurality of diodes (more specifically, 7 diodes corresponding to 7 pixels 150 of one row in the array of Fig. 1, of which only 2 pixels 150 are labeled in Fig. 3 for simplicity) .
  • the plurality of diodes may have an electrical contact 119A as a shared (common) electrode.
  • the first doped region 111 may also have discrete portions.
  • the electronics layer 120 may include an electronic system 121 suitable for processing or interpreting signals generated by the radiation incident on the radiation absorption layer 110.
  • the electronic system 121 may include an analog circuitry such as a filter network, amplifiers, integrators, and comparators, or a digital circuitry such as a microprocessor, and memory.
  • the electronic system 121 may include one or more ADCs (analog to digital converters) .
  • the electronic system 121 may include components shared by the pixels 150 or components dedicated to a single pixel 150.
  • the electronic system 121 may include an amplifier dedicated to each pixel 150 and a microprocessor shared among all the pixels 150.
  • the electronic system 121 may be electrically connected to the pixels 150 by vias 131. Space among the vias may be filled with a filler material 130, which may increase the mechanical stability of the connection of the electronics layer 120 to the radiation absorption layer 110. Other bonding techniques are possible to connect the electronic system 121 to the pixels 150 without using the vias 131.
  • the radiation absorption layer 110 including diodes
  • particles of the radiation may be absorbed and generate one or more charge carriers (e.g., electrons, holes) by a number of mechanisms.
  • the charge carriers may drift to the electrodes of one of the diodes under an electric field.
  • the electric field may be an external electric field.
  • the electrical contact 119B may include discrete portions each of which is in electrical contact with the discrete regions 114.
  • the term “electrical contact” may be used interchangeably with the word “electrode.
  • the charge carriers may drift in directions such that the charge carriers generated by a single particle of the radiation are not substantially shared by two different discrete regions 114 ( “not substantially shared” here means less than 2%, less than 0.5%, less than 0.1%, or less than 0.01%of these charge carriers flow to a different one of the discrete regions 114 than the rest of the charge carriers) .
  • Charge carriers generated by a particle of the radiation incident around the footprint of one of these discrete regions 114 are not substantially shared with another of these discrete regions 114.
  • a pixel 150 associated with a discrete region 114 may be an area around the discrete region 114 in which substantially all (more than 98%, more than 99.5%, more than 99.9%, or more than 99.99%of) charge carriers generated by a particle of the radiation incident therein flow to the discrete region 114. Namely, less than 2%, less than 1%, less than 0.1%, or less than 0.01%of these charge carriers flow beyond the pixel 150.
  • Fig. 4 schematically shows a detailed cross-sectional view of the radiation detector 100 of Fig. 1 along the line 2-2, according to an alternative embodiment.
  • the radiation absorption layer 110 may include a resistor of a semiconductor material such as silicon, germanium, GaAs, CdTe, CdZnTe, or a combination thereof, but does not include a diode.
  • the semiconductor material may have a high mass attenuation coefficient for the radiation of interest.
  • the electronics layer 120 of Fig. 4 is similar to the electronics layer 120 of Fig. 3 in terms of structure and function.
  • the radiation When the radiation hits the radiation absorption layer 110 including the resistor but not diodes, it may be absorbed and generate one or more charge carriers by a number of mechanisms.
  • a particle of the radiation may generate 10 to 100,000 charge carriers.
  • the charge carriers may drift to the electrical contacts 119A and 119B under an electric field.
  • the electric field may be an external electric field.
  • the electrical contact 119B may include discrete portions.
  • the charge carriers may drift in directions such that the charge carriers generated by a single particle of the radiation are not substantially shared by two different discrete portions of the electrical contact 119B ( “not substantially shared” here means less than 2%, less than 0.5%, less than 0.1%, or less than 0.01%of these charge carriers flow to a different one of the discrete portions than the rest of the charge carriers) .
  • a pixel 150 associated with a discrete portion of the electrical contact 119B may be an area around the discrete portion in which substantially all (more than 98%, more than 99.5%, more than 99.9%or more than 99.99%of) charge carriers generated by a particle of the radiation incident therein flow to the discrete portion of the electrical contact 119B. Namely, less than 2%, less than 0.5%, less than 0.1%, or less than 0.01%of these charge carriers flow beyond the pixel associated with the one discrete portion of the electrical contact 119B.
  • Fig. 5 schematically shows a top view of a radiation detector package 500 including the radiation detector 100 and a printed circuit board (PCB) 510.
  • PCB printed circuit board
  • the term “PCB” as used herein is not limited to a particular material.
  • a PCB may include a semiconductor.
  • the radiation detector 100 may be mounted to the PCB 510.
  • the wiring between the radiation detector 100 and the PCB 510 is not shown for the sake of clarity.
  • the package 500 may have one or more radiation detectors 100.
  • the PCB 510 may include an input/output (I/O) area 512 not covered by the radiation detector 100 (e.g., for accommodating bonding wires 514) .
  • the radiation detector 100 may have an active area 190 which is where the pixels 150 (Fig. 1) are located.
  • the radiation detector 100 may have a perimeter zone 195 near the edges of the radiation detector 100.
  • the perimeter zone 195 has no pixels 150, and the radiation detector 100 does not detect particles of radiation incident on the perimeter zone
  • Fig. 6 schematically shows a cross-sectional view of an image sensor 600, according to an embodiment.
  • the image sensor 600 may include one or more radiation detector packages 500 of Fig. 5 mounted to a system PCB 650.
  • the electrical connection between the PCBs 510 and the system PCB 650 may be made by bonding wires 514.
  • the PCB 510 may have the I/O area 512 not covered by the radiation detectors 100.
  • the packages 500 may have gaps in between. The gaps may be approximately 1 mm or more.
  • a dead zone of a radiation detector (e.g., the radiation detector 100) is the area of the radiation-receiving surface of the radiation detector, on which incident particles of radiation cannot be detected by the radiation detector.
  • a dead zone of a package (e.g., package 500) is the area of the radiation-receiving surface of the package, on which incident particles of radiation cannot be detected by the radiation detector or detectors in the package.
  • the dead zone of the package 500 includes the perimeter zones 195 and the I/O area 512.
  • a dead zone (e.g., 688) of an image sensor (e.g., image sensor 600) with a group of packages (e.g., packages 500 mounted on the same PCB and arranged in the same layer or in different layers) includes the combination of the dead zones of the packages in the group and the gaps between the packages.
  • the radiation detector 100 (Fig. 1) operating by itself may be considered an image sensor.
  • the package 500 (Fig. 5) operating by itself may be considered an image sensor.
  • the image sensor 600 including the radiation detectors 100 may have the dead zone 688 among the active areas 190 of the radiation detectors 100. However, the image sensor 600 may capture multiple partial images of an object or scene (not shown) one by one, and then these captured partial images may be stitched to form a stitched image of the entire object or scene.
  • image in the present specification is not limited to spatial distribution of a property of a radiation (such as intensity) .
  • image may also include the spatial distribution of density of a substance or element.
  • Fig. 7A –Fig. 7B schematically show an imaging system 700 for blood flow speed measurement, according to an embodiment.
  • the imaging system 700 may include a radiation source 710 and the image sensor 600 (Fig. 6) .
  • the imaging system 700 may be arranged such that a detection portion 720d of a blood vessel 720 is positioned between the radiation source 710 and the image sensor 600.
  • the imaging system 700 may be arranged such that the image sensor 600 may capture images of a scene (not shown) which includes the detection portion 720d.
  • the radiation source 710 may send a radiation beam 712 toward the detection portion 720d.
  • the radiation beam 712 may include X-ray photons.
  • each of the X-ray photons of the radiation beam 712 may have an energy in the range of 100 eV to 1000 eV.
  • the image sensor 600 may capture an image of the scene which includes the detection portion 720d using radiation of the radiation beam 712 that has transmitted through the detection portion 720d. As a result, the detection portion 720d and the material inside the detection portion 720d (if any) are present in the captured image.
  • the blood flow speed measurement may be performed as follows.
  • a salt water volume 730 NaCl solution
  • a salt water volume 730 may be introduced into the blood vessel 720 at an introduction site 720i.
  • the blood in the blood vessel 720 flows in a direction 725f.
  • the salt water volume 730 going with the flow of the blood in the blood vessel 720 also flows in the direction 725f. Therefore, the detection portion 720d is downstream with respect to the introduction site 720i.
  • the image sensor 600 may capture multiple images of the scene which includes the detection portion 720d.
  • these multiple images may be captured one image at a time (i.e., one by one) .
  • these multiple images may include 5 images (image #1, image #2, image #3, image #4, and image #5) which are captured one by one by the image sensor 600 in that order.
  • a time point at which the salt water volume 730 reaches the detection portion 720d may be determined based on at least an image of the multiple images. For example, assume that the salt water volume 730 is first present (partially or entirely) in image #3. As a result, the time at which image #3 is captured may be used as the time point at which the salt water volume 730 reaches the detection portion 720d.
  • the flow speed of the blood in the blood vessel 720 may be determined based on (A) the time point determined above and (B) the introduction time at which the salt water volume 730 is introduced into the blood vessel 720.
  • the travel distance along the blood vessel 720 between the introduction site 720i and the detection portion 720d is 1m.
  • Fig. 8 shows a flowchart 800 generalizing the blood flow speed measurement described above, according to an embodiment.
  • Step 810 includes introducing an object into a tube at an introduction site of the tube, wherein a liquid flows in the tube.
  • the salt water volume 730 is introduced into the blood vessel 720 at the introduction site 720i of the blood vessel 720, wherein blood flows in the blood vessel 720.
  • Step 820 includes capturing M images of a scene which includes a detection portion of the tube, wherein the detection portion is downstream with respect to the introduction site, and wherein M is an integer greater than 1.
  • Step 830 includes determining a time point at which the object reaches the detection portion based on at least an image of the M images. For example, in the embodiments described above, with reference to Fig. 7A –Fig. 7B, the time point at which the salt water volume 730 reaches the detection portion 720d is determined based on image #3 of the 5 images.
  • Step 840 includes determining a flow speed of the liquid in the tube based on the time point and an introduction time at which the object is introduced into the tube.
  • image #1 is captured when the salt water volume 730 has not reached the detection portion 720d.
  • image #2 may be compared with image #1. Assume that image #2 is not different from image #1. As a result, it can be determined that the salt water volume 730 has not reached the detection portion 720d at the time image #2 is captured.
  • image #3 may be compared with image #1. Assume that image #3 is different from image #1. As a result, it can be determined that the salt water volume 730 has reached the detection portion 720d at the time image #3 is captured.
  • image #3 may be considered different from image #1 if the sum of all picture elements of image #3 is different from the sum of all picture elements of image #1.
  • the sum of all picture elements of an image is the sum of the values of all picture elements of that image. For example, assume that image #1 has 28 picture elements which have respectively 28 values. Then, the sum of all picture elements of image #1 is the sum of these 28 values.
  • the sum of all picture elements of image #3 may be considered different from the sum of all picture elements of image #1 if the magnitude of the difference between (A) the sum of all picture elements of image #3 and (B) the sum of all picture elements of image #1 exceeds a pre-specified threshold value.
  • the image sensor 600 may capture the images of the scene periodically (i.e., one after another by the same time period) .
  • the 5 images image #1, image #2, image #3, image #4, and image #5 may be captured by the image sensor 600 periodically (e.g., every 5 seconds) .
  • the image sensor 600 may be stationary with respect to the detection portion 720d of the blood vessel 720 during the blood flow speed measurement described above.
  • both the image sensor 600 and the radiation source 710 may be stationary with respect to the detection portion 720d of the blood vessel 720 during the blood flow speed measurement described above.
  • the object includes the solution of salt (i.e., the salt water volume 730 of Fig. 7A –Fig. 7B) .
  • the object may include a liquid that is different from blood.
  • the object may include a solution of iodine.
  • the salt water volume 730 (as the object of step 810) is actively introduced into the blood vessel 720 (as the tube of step 810 in Fig. 8) .
  • the object of step 810 may be passively introduced into the tube as in the following example.
  • salt water may be injected into the blood vessel 720 resulting in a mix of blood and salt water flowing from the introduction site 720i toward the detection portion 720d.
  • the injection of salt water at the introduction site 720i may be stopped at a stop time resulting in blood without salt water as the object flowing from the introduction site 720i toward the detection portion 720d.
  • the object (blood without salt water) starts being introduced into the blood vessel 720 at the stop time.
  • the introduction of the object (blood without salt water) into the blood vessel 720 is considered “passive” because the act of stopping injecting something (salt water) in effect creates the object (blood without salt water) in the blood vessel 720.
  • an iodine solution may be used in place of salt water.
  • the time point at which the salt water volume 730 reaches the detection portion 720d is determined by comparing the captured images (e.g., image #2 is compared with image #1, then image #3 is compared with image #1, and so on until a difference is found) .
  • the time point at which the salt water volume 730 reaches the detection portion 720d may be determined by analyzing the captured images individually in the order in which the images are captured. For example, image #1 may be analyzed first, then image #2 is analyzed, and so on.
  • image #3 yields that the values of the picture elements of image #3 are not uniform across image #3. Specifically, assume it is found that an average picture element value of an object region of image #3 differs from an average picture element value of the remaining region of image #3 by an amount whose magnitude exceeds a pre-specified threshold value. Then, it can be determined that the object region of image #3 is the image of a portion (or all) of the salt water volume 730. As a result, the time point at which the salt water volume 730 reaches the detection portion 720d can be determined to be the time at which image #3 is captured.
  • the flow speed of blood in the blood vessel 720 may be determined based on (A) the travel distance along the blood vessel 720 between the introduction site 720i and the detection portion 720d and (B) the position of the object region in image #3.
  • the flow speed of blood in the blood vessel 720 is determined by analyzing one or some images of the scene that includes the detection portion 720d. In an alternative embodiment, the flow speed of blood in the blood vessel 720 may be determined by analyzing all the captured images of the scene that includes the detection portion 720d as follows.
  • P salt water volumes may be introduced into the blood vessel 720, wherein the P salt water volumes are introduced periodically one by one at the introduction site 720i and at an introduction frequency (e.g., every 5 seconds or 0.2 Hz) , and wherein P is an integer greater than 1.
  • the image sensor 600 may capture Q images (one by one) of the scene that includes the detection portion 720d, wherein Q is an integer greater than 1.
  • the Q images may be captured periodically.
  • the Q images may be captured at a frequency higher than the introduction frequency.
  • a same time duration which it takes for each of the P salt water volumes to travel in the blood vessel 720 from the introduction site 720i to the detection portion 720d may be determined based on (A) the Q images, and (B) the introduction frequency (e.g., 0.2 Hz) .
  • the time duration may be determined as follows. Firstly, in an embodiment, for each image of the Q images, a sum of all picture elements of said each image may be determined, resulting in Q sums which constitute a first function in time domain.
  • Fourier transform may be applied to the first function resulting in a second function in frequency domain, wherein the second function comprises a particular component corresponding to the introduction frequency (e.g., 0.2 Hz) .
  • reverse Fourier transform may be applied to the particular component of the second function, resulting in a third function in time domain.
  • the time duration may be determined based on the third function.
  • the flow speed of blood in the blood vessel 720 may be determined based on the time duration.
  • the time duration which it takes for each of the P salt water volumes to travel in the blood vessel 720 from the introduction site 720i to the detection portion 720d is determined to be 10s.
  • the travel distance along the blood vessel 720 between the introduction site 720i and the detection portion 720d is 1m.
  • Step 910 includes introducing P objects into a tube, wherein a liquid flows in the tube, wherein the P objects are introduced periodically one object at a time at an introduction site of the tube and at an introduction frequency, and wherein P is an integer greater than 1.
  • the P salt water volumes are introduced into the blood vessel 720, wherein blood flows in the blood vessel 720, wherein the P salt water volumes are introduced periodically one by one at the introduction site 720i of the blood vessel 720 and at the introduction frequency (0.2 Hz) , and wherein P > 1.
  • Step 920 includes capturing Q images of a scene which includes a detection portion of the tube, wherein the Q images are captured one image at a time, wherein the detection portion is downstream with respect to the introduction site, and wherein Q is an integer greater than 1.
  • the Q images of the scene which includes detection portion 720d of the blood vessel 720 are captured by the image sensor 600, wherein the Q images are captured one image at a time, wherein the detection portion 720d is downstream with respect to the introduction site 720i, and wherein Q is an integer greater than 1.
  • Step 930 includes determining a same time duration which it takes for each of the P objects to travel in the tube from the introduction site to the detection portion based on (A) the Q images, and (B) the introduction frequency.
  • the same time duration which it takes for each of the P salt water volumes to travel in the blood vessel 720 from the introduction site 720i to the detection portion 720d is determined based on (A) the Q images, and (B) the introduction frequency (0.2 Hz) .
  • Step 940 includes determining a flow speed of the liquid in the tube based on the time duration. For example, in the embodiments described above, with reference to Fig. 7A –Fig. 7B, the flow speed of blood in the blood vessel 720 is determined based on the time duration.

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Abstract

L'invention concerne un procédé comprenant : l'introduction d'un objet dans un tube au niveau d'un site d'introduction du tube, un liquide s'écoulant dans le tube (810) ; la capture de M images d'une scène qui comprend une portion de détection du tube, la portion de détection étant en aval par rapport au site d'introduction, et M étant un nombre entier supérieur à 1 (820) ; la détermination d'un instant auquel l'objet atteint la portion de détection sur la base d'au moins une image des M images (830) ; et la détermination d'une vitesse d'écoulement du liquide dans le tube sur la base de l'instant (840).
PCT/CN2022/070035 2022-01-04 2022-01-04 Mesures de vitesse d'écoulement en utilisant des systèmes d'imagerie WO2023130197A1 (fr)

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TW111147554A TW202328661A (zh) 2022-01-04 2022-12-12 利用成像系統的流速測量方法

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CN105559810A (zh) * 2015-12-10 2016-05-11 上海交通大学 血管单位时间血流量与血流速度的计算方法
CN107077740A (zh) * 2014-11-07 2017-08-18 富川安可股份公司 用于确定移动流体表面的速度的方法和系统
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CN109512450A (zh) * 2018-10-18 2019-03-26 深圳市孙逸仙心血管医院（深圳市心血管病研究所） 测量血管血流速度的方法
WO2021016793A1 (fr) * 2019-07-29 2021-02-04 Shenzhen Xpectvision Technology Co., Ltd. Systèmes et procédés d'imagerie tridimensionnelle
CN112535465A (zh) * 2020-11-03 2021-03-23 佛山科学技术学院 一种基于片层光的三维血流速度成像方法及装置
US20210192739A1 (en) * 2019-12-19 2021-06-24 Siemens Healthcare Gmbh Computer-implemented method for processing x-ray images

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* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101711683A (zh) * 2009-10-30 2010-05-26 中国人民解放军第三军医大学第一附属医院 一种测量动脉血液流速的方法
CN107077740A (zh) * 2014-11-07 2017-08-18 富川安可股份公司 用于确定移动流体表面的速度的方法和系统
CN105559810A (zh) * 2015-12-10 2016-05-11 上海交通大学 血管单位时间血流量与血流速度的计算方法
US20180330507A1 (en) * 2017-05-15 2018-11-15 Pie Medical Imaging B.V. Method and Apparatus for Determining Blood Velocity in X-Ray Angiography Images
CN109512450A (zh) * 2018-10-18 2019-03-26 深圳市孙逸仙心血管医院（深圳市心血管病研究所） 测量血管血流速度的方法
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CN112535465A (zh) * 2020-11-03 2021-03-23 佛山科学技术学院 一种基于片层光的三维血流速度成像方法及装置

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