WO2017097074A1 - Procédé de calcul du volume d'écoulement de sang d'un vaisseau sanguin par unité de temps et de la vitesse d'écoulement de sang - Google Patents

Procédé de calcul du volume d'écoulement de sang d'un vaisseau sanguin par unité de temps et de la vitesse d'écoulement de sang Download PDF

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WO2017097074A1
WO2017097074A1 PCT/CN2016/104655 CN2016104655W WO2017097074A1 WO 2017097074 A1 WO2017097074 A1 WO 2017097074A1 CN 2016104655 W CN2016104655 W CN 2016104655W WO 2017097074 A1 WO2017097074 A1 WO 2017097074A1
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blood flow
curve
value
region
gray
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PCT/CN2016/104655
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涂圣贤
楚淼
杨璐璐
刘冰
陈亚珠
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博动医学影像科技（上海）有限公司
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    • 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
    • A61B6/504—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 diagnosis of blood vessels, e.g. by angiography
    • 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
    • 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
    • A61B6/46—Arrangements for interfacing with the operator or the patient
    • A61B6/467—Arrangements for interfacing with the operator or the patient characterised by special input means
    • A61B6/469—Arrangements for interfacing with the operator or the patient characterised by special input means for selecting a region of interest [ROI]
    • 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
    • A61B6/503—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 diagnosis of the heart
    • 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
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5217—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data extracting a diagnostic or physiological parameter from medical diagnostic data

Definitions

  • the invention relates to the application in the medical field, in particular to an accurate, rapid and non-invasive calculation of blood flow and blood flow velocity per unit time based on image.
  • vascular stenosis caused by plaque affects myocardial blood supply and poses a threat to human health.
  • Coronary angiography can show the severity of coronary stenosis, but it does not reflect the functional significance of stenosis.
  • the blood flow reserve fraction (FFR) was evaluated as the gold standard for the diagnosis of coronary function, which is defined as the ratio of the maximum blood flow that the coronary artery can provide to the myocardium and the maximum blood supply flow when the coronary artery is completely normal. In the maximum hyperemia state, the ratio of the pressure at the distal end of the stenotic lesion to the proximal pressure of the stenosis is calculated.
  • Invasive invasive pressure measurements of blood vessels by pressure sensors are not only labor intensive, but also risk of damaging blood vessels.
  • the geometric model of the coronary system can be obtained by three-dimensional or two-dimensional quantitative coronary angiography for computer hydrodynamic analysis.
  • the current speed acquisition method is obtained by semi-automatic (artificial + computer) method, and the reconstruction process needs to accurately outline the blood vessel boundary. Longer and the operator has a lot of experience, and needs to manually determine the starting position of the contrast agent into the coronary artery (starting frame) and the end position (end frame) filling the target distal end.
  • the contrast agent is fully in the microcirculation.
  • the filling process during expansion is relatively short, and the vessel segment of interest typically only occupies a certain period of a heartbeat cycle, which results in a very large difference in blood flow velocity determined during different periods of the heartbeat cycle.
  • FFR blood flow reserve score
  • TIMI frame method see comparison file 2 (Tu S, Barbato E, Koszegi Z et al. Fractional flow reserve calculation from 3-dimensional quantitative coronary angiography and TIMI frame count: a fast computer model to quantify the functional significance of moderately obstructed coronary Arteries [J]. JACC Cardiovascular interventions, 2014, (7): 768-777), this document 2 discloses the following scheme: playing a coronary angiography image, observing the contrast agent entering the proximal anatomical landmark of the target vessel to the distal anatomical landmark The number of frames experienced by the point, according to the frame rate of the contrast image, obtains the transmission time of the contrast agent from the proximal marker point to the distal marker point. The three-dimensional reconstruction of coronary angiography is used to obtain the distance between the marker points, and the transmission time of the contrast agent is obtained. The distance divided by the transmission time is approximated as the blood flow velocity.
  • Doppler guide wire method See Comparative Document 1, which also discloses that a Doppler guide wire is inserted into a coronary vessel, and the blood flow velocity is measured by the Doppler effect generated between the ultrasonic vibration source and the relatively moving blood.
  • Temperature dilution method The pressure guide wire is inserted into the coronary blood vessel, and the room temperature physiological saline is injected into the coronary artery, which is diluted with the flow of blood, and absorbs heat of the blood to raise the temperature. This temperature dilution process is detected by the thermistor in the front section of the catheter, and the temperature time dilution curve can be obtained by the detector recording. According to the thermal dilution theory, the blood flow velocity is inversely proportional to the average transit time of the indicator, and the blood flow velocity can be calculated from the temperature time dilution curve.
  • the measurement accuracy of blood flow velocity is limited by the estimation of the length of the blood vessel and the short overlap of the coronary angiography.
  • the contrast region of interest does not shift correspondingly as the target vessel position moves in the contrast sequence, resulting in a change in the gray value in the region of interest not only due to the transmission of the contrast agent in the target vessel, but also due to the target vessel Removal and migration of the side branch vessels result in inaccurate blood flow or blood flow velocity per unit of time calculated.
  • the technical problem to be solved by the present invention is to provide a new method for calculating blood flow and blood flow velocity per vascular unit time, and the specific solutions include:
  • a method for calculating blood flow per unit time of a blood vessel comprising: determining a region of interest of a blood vessel; calculating and fitting a grayscale fitting curve in the region of interest; determining a maximum grayscale within a predetermined time interval a value curve or a minimum gray value curve; calculating an area value of the area surrounded by the maximum gray value curve or the minimum gray value curve and the gray fitting curve in the predetermined time interval; and obtaining the area value based on the area value of the area The unit time blood flow.
  • a method for calculating a blood flow velocity of a blood vessel comprising: determining a region of interest of a blood vessel; calculating and fitting a grayscale fitting curve in the region of interest; determining a maximum gray value within a predetermined time interval a curve or a minimum gray value curve; calculating an area value of a region surrounded by a maximum gray value curve or a minimum gray value curve and a gray fitting curve in a predetermined time interval; and obtaining an area value corresponding to the area value based on the area value of the area Blood flow per unit time; based on the blood flow per unit time and the lumen area of the blood vessel, the blood flow velocity of the blood vessel is obtained.
  • the region of interest comprises a main branch vessel into which a contrast agent is injected and a branch thereof.
  • the change of the position of the region of interest at different heartbeat times is detected by the target image tracking, thereby obtaining an optimal region of interest.
  • the method further comprises: receiving an X-ray contrast image sequence of the blood vessel, selecting a region of interest; and selecting a gray-scale histogram in the region of interest in each frame of contrast before the start time is filled with the contrast agent,
  • the gray histogram calculates the gray value in the region of interest under each frame, and fits the gray level fitting curve of the gray level with time according to the gray value.
  • the method further comprises: determining a first time point, and a maximum value and a minimum value of the gray level fitting curve in a predetermined time interval centered on the first time point;
  • the maximum gray value curve is a curve obtained by using a maximum value of the gray level fitting curve in the predetermined time interval as an ordinate;
  • the minimum gray value curve is a gray level fitting curve in a predetermined time interval. The minimum value is the curve made by the ordinate.
  • the first time point is a time point at which the gradation value of the gradation fitting curve decreases the fastest; when the gradation fitting curve changes trend When rising, the first time point is the time point at which the gray value rises fastest in the gray fitting curve.
  • the slope of each point on the gradation fitting curve is calculated, and a point at which the slope is negative and the absolute value of the slope is the largest is obtained, and the point is a decrease in the gradation value.
  • the calculating process of the area area value further includes: when the gradation fitting curve change trend is decreasing, acquiring a first time point in the gradation fitting curve, where the first time point is Integrating the gray fitting curve in the predetermined time interval of the center, calculating the area value of the maximum gray value curve and the gray level fitting curve in the predetermined time interval; when the gray fitting curve changes When the potential is rising, acquiring a first time point in the gray level fitting curve, integrating the gray level fitting curve in the predetermined time interval centered on the first time point, and calculating the predetermined time interval The area value of the area surrounded by the minimum gray value curve and the gray level fitting curve.
  • the predetermined time interval is an integer number of cardiac cycles, and the integer is greater than or equal to 1.
  • the predetermined time interval is a cardiac cycle, including each half of the cardiac cycle before and after the first time point; wherein the first and second half of the cardiac cycle time interval is that the contrast agent begins to fill After the region of interest of the vessel, this period of time before the region of interest is not fully filled.
  • the blood flow per unit time corresponding to the area value of the area can be obtained, and the pair
  • the lumen area of the blood vessel can be obtained by a three-dimensional quantitative measurement method.
  • the fitting formula of the gradation fitting curve is:
  • g(t) a 0 +a 1 t+a 2 t 2 +...+a n t n ; where a 0 , a 1 , a 2 , ... a n are fitting coefficients, and t is time.
  • the original gray scale change curve is a raw data curve made by the gray value calculated by the gray histogram in the region of interest in each frame of the contrast image.
  • the obtained blood flow velocity can be used to evaluate the effect of blood vessel stenosis on blood flow velocity, or to calculate the FFR value of the stenotic blood flow reserve fraction.
  • the obtained unit time blood flow or blood flow velocity is used to evaluate changes in renal artery sympathetic nerve ablation before and after renal artery sympathetic nerve ablation, or for real-time use. Changes in blood flow and blood flow velocity per unit time during ablation were assessed.
  • the obtained unit time blood flow or blood flow velocity can be used to evaluate the change in blood supply before and after the treatment of the tumor to prompt the therapeutic effect.
  • the obtained blood flow velocity can be used to calculate a pressure drop or a blood flow reserve fraction (FFR) value of the stenotic blood vessel in the peripheral blood vessel.
  • FFR blood flow reserve fraction
  • the invention has the beneficial effects that the technical solution provides a new calculation method of blood flow and blood flow velocity per unit time, which ensures that the calculated blood flow per unit time and the blood flow velocity are the average values of blood flow velocity in an integer number of cardiac cycles. Thereby effectively avoiding the selection of inappropriate time periods, the calculated average unit time blood flow and blood flow velocity are calculation errors caused by the mean within the non-integer cardiac cycle.
  • Using the change of the gray value of the image of the region of interest to find the blood flow velocity with time can not only achieve non-invasive diagnosis, but also selectively increase or eliminate the side branch blood flow to adapt to different applications.
  • Figure 1 is a gray histogram of a coronary angiography image
  • 2A is a schematic diagram showing changes in gray scale of a blood vessel before filling of a contrast agent
  • 2B is a schematic view showing changes in blood gray scale after filling of a contrast agent
  • Figure 3 is a schematic diagram showing changes in blood flow velocity in different cardiac cycles measured by the Doppler guidewire method
  • FIG. 4 is a schematic diagram of an original gray scale variation curve and a gray scale fitting curve in different cardiac cycles of a region of interest
  • Figure 5 is a schematic diagram of the calculation principle of blood flow and blood flow velocity per unit time.
  • the present invention provides a method for calculating blood flow and blood flow velocity per vascular unit time, and specifically includes the following steps: First, determining a region of interest of a blood vessel (a preferred method is to select an angiogram by receiving X-ray angiography of the blood vessel a region of interest); secondly, calculating and fitting a grayscale fitting curve in the region of interest; secondly, obtaining a maximum grayscale value curve within a predetermined time interval; and secondly, calculating a maximum grayscale value within the predetermined time interval
  • the area value S surrounded by the curve and the gray fitting curve again, based on the area value S of the area, the blood flow Q per unit time corresponding to the area value is obtained; finally, the blood vessel is combined The lumen area, the blood flow velocity V of the blood vessel is obtained.
  • the method may further comprise: determining a first time point, and a maximum value and a minimum value of the gray level fitting curve in a predetermined time interval centered on the first time point.
  • the first time point is a time point at which the gray value in the gray fitting curve decreases the fastest.
  • the maximum gray value curve is a curve obtained by taking the maximum value of the gray fitting curve in the predetermined time interval as the ordinate.
  • the change of the position of the region of interest at different heartbeat moments can be detected by the target image tracking registration, thereby obtaining the best region of interest.
  • the region of interest in the prior art does not shift correspondingly as the target vessel position of the contrast sequence moves, resulting in a change in the gray value in the region of interest not only due to the transmission of the contrast agent in the target vessel, It is also possible that the calculated blood flow velocity is inaccurate due to the removal of the target blood vessel and the movement of the side branch vessels.
  • the movement of the target vessel position of the contrast sequence is very common and can be caused by the beating of the heart, the breathing and movement of the patient.
  • the filling speed of the contrast agent is faster, the filling of the entire region of interest usually takes a short time. Therefore, it is preferable to select the entire cardiac period (T) within the predetermined time interval, that is, two-thirds before and after the first time point.
  • the gradation fitting curve is integrated in the interval of one cardiac cycle to obtain the area value S.
  • the interval of one-half of the cardiac cycle time before and after the first time point is further preferably after the contrast agent begins to fill the region of interest of the blood vessel,
  • the period of time comprises myocardial and microcirculation perfusion, and therefore, preferably, the selected region of interest is a myocardium that is perfused with the vessel segment of interest.
  • the correspondence table is a correspondence table between different area values and blood flow rates of different unit time, and the table can pass multiple times and repeatability. A large number of routine experiments were obtained and the table was updated based on later experimental data.
  • a preferred calculation method is to obtain a cardiac cycle based on the electrocardiogram data.
  • calculate the cardiac cycle T m/f by calculating the number m of frames between the peak-to-peak value of the original gray-scale curve obtained from the histogram.
  • f represents the frame frequency of the contrast.
  • the original gray scale change curve is a curve obtained by directly calculating the gray value obtained from the contrast histogram of each frame, and is a raw data curve; the gray scale fitting curve is a curve obtained by fitting means according to the original data.
  • the first time point is a time point at which the gray value in the gray fitting curve decreases the fastest.
  • the point at which the slope is negative and the absolute value is the largest can be obtained by calculating the slope of each point on the gradation fitting curve.
  • the point is the time point at which the gray value drops the fastest.
  • the present embodiment analyzes the case where the gray value change in the case of general angiography is a downward trend, that is, in the case where the obtained gradation fitting curve is a descending curve, by selecting the curve The point at which the gray value decreases the fastest is the first time point, and the predetermined time interval is determined centering on the first time point, and the maximum gray value curve is obtained based on the maximum value of the gray fitting curve of the predetermined time interval. Thereby, the curve area enclosed by the maximum gradation value curve and the gradation fitting curve in the predetermined time interval centered on the first time point is calculated.
  • the gray value of the contrast agent is larger than the gray value before filling, and the gray value changes to an upward trend, that is, the obtained gray fitting curve is a rising curve, and at this time, It is necessary to detect the fastest rising time point in the gray fitting curve as the first time point; and obtain the minimum value of the gray fitting curve in the front and rear half of the cardiac cycle centered on the first time point; A minimum gray value curve is made for the ordinate; a curve area surrounded by the minimum gray value curve and the gray fitting curve in a predetermined time interval centered on the first time point is calculated. In this case, the slope of each point on the gradation fitting curve is calculated, and the slope is obtained as a positive value, and the point at which the value of the slope is the largest is the time point at which the gradation value rises the fastest.
  • coronary angiography uses human soft tissue and contrast agents to absorb different degrees of radiation in the contrast image.
  • the image has a different high contrast between the blood vessels and the surrounding tissue.
  • the color depth of each pixel in the contrast image is represented by a gray value, and the larger the gray value, the brighter the pixel.
  • the gray histogram is the simplest and most useful tool in digital images. It represents the number of pixels with a certain gray level in the image.
  • the horizontal coordinate is the gray value.
  • the value range is preferably 0-255, and the ordinate. Indicates the number of occurrences of the gray value in the image.
  • the value range is preferably 0-N, where N is the number of image pixels.
  • the region of interest As shown in Figure 2, we chose to include a narrow vessel as the region of interest, including the main branch of the contrast agent injected and its branches.
  • the blood vessels have higher gray values before they enter the contrast agent ( Figure A) and cannot be distinguished from the surrounding soft tissue.
  • Figure B contrast agent with blood Flow diffusion, because the contrast agent absorbs the radiation more strongly, the gray value of the region of interest decreases, and the blood vessel color becomes darker.
  • the contrast agent is diluted and the gray value of the region of interest is increased. Therefore, the rate of change of the gray value of the region of interest reflects the blood flow velocity within the lumen.
  • the average blood flow velocity is similar in each cardiac cycle, but the selection of different time periods has a great influence on the calculation of the average blood flow velocity.
  • the blood flow velocity curves were measured directly in different cardiac cycles using the Doppler guidewire method.
  • the average blood flow velocities obtained by different time periods T1 and T2 with the same time interval are greatly different. Therefore, in order to ensure accurate calculation values, it is preferable to select an integer number of cardiac cycles for blood flow velocity mean calculation, such as a whole cardiac cycle.
  • the gray value of each frame of the contrast region of interest is extracted, and the gray scale fitting curve g(t) is fitted.
  • the gray scale fitting curve g(t) is fitted.
  • the gray value in the region of interest under the frame, and fitting the gray fitting curve g(t) according to the gray value, the fitting formula is a polynomial fitting:
  • g(t) a 0 +a 1 t+a 2 t 2 +...+a n t n ;
  • a 0 , a 1 , a 2 , ... a n are fitting coefficients
  • t is the time at which the contrast agent fills the blood vessel The time is the time calculated from the first frame of image acquisition.
  • the cardiac cycle can be obtained from the ECG data.
  • a point (t0, g(t0)) at which the absolute value of the slope is maximum during the gradation of the gradation value is obtained, and the point is determined as the first time point.
  • the area value S of the area (shaded area in the figure) surrounded by the curve g(t) in the one-half cardiac cycle [t1, t2] and the maximum gray value curve g(t1) before and after the first time point is calculated.
  • the maximum gray value curve g(t1) is a curve made by the maximum value of the curve g(t) in the [t1, t2] time period;
  • the shadow area value S and a cardiac cycle blood flow Q is proportional to, that is, S ⁇ Q.
  • the X-ray angiography used in the embodiments of the present invention may be cardiac coronary angiography, peripheral angiography such as renal angiography, carotid angiography, or the like, or angiography before and after tumor treatment.
  • the unit time blood flow or blood flow velocity obtained based on the above different contrast modes can be used for key parameter indicators in different disease condition analysis, and obtains better accuracy than the prior art parameter indicators. Sex and precision.
  • calculation of blood flow velocity based on coronary angiography can be used to assess the effect of vascular stenosis on blood flow velocity, as well as subsequent calculation of pressure differences or flow reserve fraction (FFR) values for stenotic vessels;
  • renal angiography can be used in renal arteries
  • Sympathetic ablation is used to assess changes in blood flow per unit time of renal arteries before and after sympathetic nerve ablation, or to assess changes in blood flow and blood flow velocity per unit time during ablation in order to demonstrate the effect of ablation
  • Contrast calculation of blood flow or blood flow velocity per unit time can be used to assess changes in blood supply before and after treatment to suggest a therapeutic effect.
  • the present invention provides a method for calculating a blood flow reserve fraction FFR of a certain segment of blood vessels, based on the average blood flow velocity or maximum mean blood flow velocity obtained by the method for calculating blood flow velocity in the present invention. And combined with other geometric parameters of the segment of the blood vessel, the pressure drop or FFR value of the blood vessel is obtained by a corresponding calculation formula.
  • the method includes receiving geometric parameters of the segment of blood vessels, the blood vessel including a proximal end point and a distal end point, the geometric parameters including a first geometric parameter representing an area (or diameter) of a proximal cross section of the blood vessel segment; a second geometric parameter representing the area (or diameter) of the distal cross section of the vessel segment; a third geometric parameter representing a cross-sectional area (or diameter) of the vessel member at a first location between the proximal end and the distal end
  • the reference lumen diameter function and the geometric parameter difference function are calculated; the geometric parameter difference function is obtained at multiple scales a difference derivative function corresponding to a plurality of scales is obtained; the scale refers to a resolution, that is, a distance between two adjacent points when the derivative is numerically calculated; and the method for calculating the blood flow velocity is obtained by using the method of the present invention.
  • the vessel segment calculates its corresponding maximum mean blood flow velocity at the mean blood flow velocity of conventional coronary angiography; the blood is obtained based on the multi-scale difference derivative function and the maximum mean blood flow velocity Ratio at the first position of the second flow between the first pressure and blood pressure at the proximal end, i.e., fractional flow reserve.
  • One of the innovations of the present invention is that the blood flow rate in the whole cardiac cycle is calculated centering on the fastest position of the grayscale fitting curve, thereby more accurately calculating the blood flow and blood flow velocity per unit time, which is effective.
  • the error caused by the calculation of the inappropriate time interval is avoided.
  • the invention has the beneficial effects that the technical solution provides a new calculation method of blood flow and blood flow velocity per unit time, which ensures that the calculated blood flow per unit time and the blood flow velocity are the average values of blood flow velocity in an integer number of cardiac cycles. Thereby effectively avoiding the misalignment
  • the calculated unit time blood flow and the mean blood flow velocity are calculation errors caused by the mean within the non-integer cardiac cycle.
  • the blood flow rate not only achieves a non-invasive diagnosis, but also selectively increases or eliminates the side branch blood flow to suit different applications.

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Abstract

La présente invention concerne un procédé de calcul du volume d'écoulement de sang d'un vaisseau sanguin par unité de temps et de la vitesse d'écoulement de sang qui comprend : la sélection d'une région d'intérêt et le calcul et l'ajustement d'une courbe d'ajustement dans laquelle le niveau de gris de la région d'intérêt varie au cours du temps, dans une séquence d'images, le calcul d'un temps auquel la courbe d'ajustement de niveau de gris présente la vitesse descendante (ou ascendante) la plus élevée, et l'intégration de la courbe d'ajustement de variation de niveau de gris dans un intervalle de temps prédéfini en utilisant le temps en tant que centre, de manière à obtenir une valeur d'aire ; et l'obtention d'un volume d'écoulement de sang par unité de temps correspondant à la valeur d'aire, et en combinaison avec l'aire de lumière du vaisseau sanguin, de manière à acquérir en outre une vitesse d'écoulement de sang. Un volume d'écoulement de sang dans un temps de cycle cardiaque entier est calculé en utilisant la position à laquelle la courbe d'ajustement de niveau de gris présente la vitesse descendante (ou ascendante) la plus élevée en tant que centre, de sorte que le volume d'écoulement de sang par unité de temps et la vitesse d'écoulement de sang puissent être calculés plus précisément de manière à éviter efficacement les erreurs causées par un calcul dans des intervalles de temps incorrects.
PCT/CN2016/104655 2015-12-10 2016-11-04 Procédé de calcul du volume d'écoulement de sang d'un vaisseau sanguin par unité de temps et de la vitesse d'écoulement de sang WO2017097074A1 (fr)

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CN201510916119.8A CN105559810B (zh) 2015-12-10 2015-12-10 血管单位时间血流量与血流速度的计算方法
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CN113012108A (zh) * 2018-07-24 2021-06-22 博动医学影像科技（上海）有限公司 血管图像的处理方法、装置及成像设备
US11278206B2 (en) 2015-04-16 2022-03-22 Gentuity, Llc Micro-optic probes for neurology
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