Hemodynamic parameter determination method and device, electronic equipment and storage medium

Abstract

The invention discloses a hemodynamic parameter determination method and device, electronic equipment and a storage medium. The method comprises the following steps: acquiring a plurality of angiography images of a coronary artery in a cardiac cycle, and performing three-dimensional modeling to obtain a three-dimensional blood vessel model; registering the plurality of blood vessel three-dimensional models, and determining the real change data of the lumen area in the cardiac cycle; constructing a hemodynamic simulation model of the coronary artery; the initial flow of the coronary artery is obtained, the initial flow serves as an optimization starting point, iterative updating is conducted on the initial flow based on a preset optimization algorithm, and simulation change data of the coronary artery lumen area corresponding to the initial flow of each iteration round is determined based on the hemodynamic simulation model; under the condition that the function value of the target function is the minimum value, the target flow of the coronary artery is determined; a coronary fractional flow reserve is determined based on the target flow of the coronary artery. The accuracy of the coronary artery fractional flow reserve can be improved.

Description

Technical Field

[0001] The present invention relates to the field of hemodynamic simulation calculation, and in particular to a method, device, electronic equipment and storage medium for determining hemodynamic parameters. Background Art

[0002] With the improvement of living standards, cardiovascular diseases are becoming more and more a threat to human health, especially coronary artery disease (CAD). Currently, a gold standard for evaluating coronary artery lesions is the invasive Fractional Flow Reserve (FFR). However, due to the high economic and time costs and the allergies of the drugs used to some patients, the scope of use of this technology has been limited. Angiography FFR models blood vessels through angiography images; by counting the number of time frames when the contrast agent passes through the blood vessels, the time for blood flow to pass through the blood vessels is estimated. The blood flow calculation time is input as a boundary condition, and the angiography FFR calculation value of each point is finally obtained.

[0003] In the traditional angiography FFR calculation method, a key step is to estimate the time it takes for blood to flow through the blood vessels. This part is generally calculated by counting the number of frames flowing in and out. However, since the frame rate of angiography is generally not high, the general frame rate is 15 frames / s, and some low-frequency frame rates are 7.5 frames per second. But the time it takes for blood to flow through the blood vessels is generally 0.5s. When the frame rate is low, due to the problem of counting frames, it will cause more serious errors. Summary of the invention

[0004] The present invention provides a method, device, electronic equipment and storage medium for determining hemodynamic parameters, so as to solve the problem of large deviation in hemodynamic parameter calculation caused by low frame rate of angiography images.

[0005] According to one aspect of the present invention, a method for determining a hemodynamic parameter is provided, comprising:

[0006] Acquire multiple angiographic images of the coronary artery during the cardiac cycle, and perform three-dimensional modeling on the angiographic images respectively to obtain three-dimensional blood vessel models of the multiple angiographic images;

[0007] Registering the three-dimensional blood vessel models of the plurality of angiography images to determine real change data of the lumen area at each position of the coronary artery during the cardiac cycle;

[0008] Constructing a hemodynamic simulation model of the coronary artery; the hemodynamic simulation model is used to obtain simulated change data of the lumen area at each position of the coronary artery through simulation calculation;

[0009] Acquiring an initial flow rate of the coronary artery, taking the initial flow rate as an optimization starting point, iteratively updating the initial flow rate based on a preset optimization algorithm, and determining simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow rate of each iteration based on the hemodynamic simulation model;

[0010] When the function value of the objective function is the minimum value, determining the target flow rate of the coronary artery; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area;

[0011] A coronary flow reserve fraction is determined based on the target flow rate of the coronary artery.

[0012] According to another aspect of the present invention, there is provided a device for determining hemodynamic parameters, comprising:

[0013] A vascular three-dimensional model building module is used to obtain a plurality of angiographic images of the coronary artery during the cardiac cycle, and to perform three-dimensional modeling on the angiographic images respectively to obtain a vascular three-dimensional model of the plurality of angiographic images;

[0014] A vascular three-dimensional model registration module, used to register the vascular three-dimensional models of the plurality of angiography images, and determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle;

[0015] A hemodynamic simulation model building module is used to build a hemodynamic simulation model of the coronary artery; the hemodynamic simulation model is used to obtain simulated change data of the lumen area at each position of the coronary artery through simulation calculation;

[0016] an initial flow optimization module, for obtaining the initial flow of the coronary artery, taking the initial flow as the optimization starting point, iteratively updating the initial flow based on a preset optimization algorithm, and determining, based on the hemodynamic simulation model, simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration round;

[0017] a target flow determination module, used for determining the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used for measuring the difference between the real change data and the simulated change data of the lumen area;

[0018] The coronary artery blood flow reserve fraction determination module is used to determine the coronary artery blood flow reserve fraction based on the target flow of the coronary artery.

[0019] According to another aspect of the present invention, an electronic device is provided, the electronic device comprising:

[0020] at least one processor; and

[0021] a memory communicatively connected to the at least one processor; wherein,

[0022] The memory stores a computer program executable by the at least one processor, and the computer program is executed by the at least one processor so that the at least one processor can execute the hemodynamic parameter determination method described in any embodiment of the present invention.

[0023] According to another aspect of the present invention, a computer-readable storage medium is provided, wherein the computer-readable storage medium stores computer instructions, and the computer instructions are used to enable a processor to implement the method for determining hemodynamic parameters described in any embodiment of the present invention when executed.

[0024] The technical solution of the embodiment of the present invention is to obtain a plurality of angiographic images of the coronary artery during the cardiac cycle and perform three-dimensional modeling to obtain a vascular three-dimensional model of the plurality of angiographic images; align the vascular three-dimensional models of the plurality of angiographic images to determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle; construct a hemodynamic simulation model of the coronary artery; obtain the initial flow of the coronary artery, take the initial flow as the optimization starting point, iteratively update the initial flow based on a preset optimization algorithm, and determine the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration based on the hemodynamic simulation model; determine the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area; and determine the coronary blood flow reserve fraction based on the target flow of the coronary artery. Taking the difference between the real change data and the simulated change data of the lumen area as the objective function, the flow in the coronary artery is optimized to obtain the target flow. The coronary blood flow reserve fraction is determined based on the target flow, which solves the problem of large deviation in the calculation of hemodynamic parameters due to the low frame rate of the angiography image. The coronary blood flow reserve fraction can be obtained without loss of precision, thereby improving the accuracy of the coronary blood flow reserve fraction.

[0025] It should be understood that the contents described in this section are not intended to identify the key or important features of the embodiments of the present invention, nor are they intended to limit the scope of the present invention. Other features of the present invention will become easily understood through the following description. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the following briefly introduces the drawings required for use in the description of the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0027] Figure 1 is a flow chart of a method for determining hemodynamic parameters provided in Embodiment 1 of the present invention;

[0028] Figure 2 is a structural schematic diagram of a device for determining hemodynamic parameters provided by Embodiment 2 of the present invention;

[0029] Figure 3 It is a structural schematic diagram of an electronic device provided in Embodiment 3 of the present invention. DETAILED DESCRIPTION

[0030] In order to enable those skilled in the art to better understand the scheme of the present invention, the technical scheme in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work should fall within the scope of protection of the present invention.

[0031] It should be noted that the terms "first", "second", etc. in the specification and claims of the present invention and the above-mentioned drawings are used to distinguish similar objects, and are not necessarily used to describe a specific order or sequence. It should be understood that the data used in this way can be interchanged where appropriate, so that the embodiments of the present invention described herein can be implemented in an order other than those illustrated or described herein. In addition, the terms "including" and "having" and any variations thereof are intended to cover non-exclusive inclusions, for example, a process, method, system, product or device that includes a series of steps or units is not necessarily limited to those steps or units that are clearly listed, but may include other steps or units that are not clearly listed or inherent to these processes, methods, products or devices.

[0032] Embodiment 1

[0033] Figure 1This is a flow chart of a method for determining hemodynamic parameters provided by the first embodiment of the present invention. This embodiment is applicable to the case of calculating coronary blood flow reserve fraction by coronary angiography. The method can be executed by a hemodynamic parameter determination device. The hemodynamic parameter determination device can be implemented in the form of hardware and / or software. The hemodynamic parameter determination device can be configured in electronic devices such as computers and servers. Figure 1 As shown, the method includes:

[0034] S110 , acquiring a plurality of angiographic images of the coronary artery during a cardiac cycle, and performing three-dimensional modeling on each of the angiographic images to obtain three-dimensional blood vessel models of the plurality of angiographic images.

[0035] Among them, the angiographic image refers to an image captured at a certain frame rate within the cardiac cycle when performing angiography on the coronary arteries. It should be noted that each heart beat is a cardiac cycle. In this embodiment, during the angiography of the coronary arteries, angiographic images of the coronary arteries at different periods are continuously captured at a preset frame rate, and the angiographic images within each cardiac cycle form a sequence. For the angiographic images of the same sequence, the angiographic images are three-dimensionally modeled respectively to generate a three-dimensional model of the blood vessel for each angiographic image. The three-dimensional model of the blood vessel includes the centerline and lumen diameter of the blood vessel.

[0036] S120, registering the three-dimensional blood vessel models of the multiple angiography images to determine real change data of the lumen area of ​​each position of the coronary artery during the cardiac cycle.

[0037] In this embodiment, the vascular three-dimensional models of multiple angiography images of the same sequence are registered, and when the registration is satisfactory, the real change data of the lumen area at each position of the coronary artery during the cardiac cycle is determined. The real change data of the lumen area refers to the change data of the lumen area at any position over time, and the real change data of the lumen area includes the lumen area and the time corresponding to the lumen area. It can be understood that the lumen area can be determined based on the lumen contour diameter in the vascular three-dimensional model.

[0038] It should be noted that the registration standard is that the contour of the vascular three-dimensional model generated by each angiography image can find corresponding contour points in the vascular three-dimensional model of the angiography image of other frames.

[0039] Based on the above embodiment, optionally, registering the vascular three-dimensional models of the multiple angiography images to determine the real change data of the lumen area of ​​each position of the coronary artery during the cardiac cycle includes: inputting the vascular three-dimensional models of the multiple angiography images into a registration model for registration to obtain the real change data of the lumen area of ​​each position of the coronary artery during the cardiac cycle; the registration model is trained for a training set based on manual registration results.

[0040] The registration model is used to register the vascular three-dimensional models of the same sequence of angiographic images. The registration model is obtained by training the training set based on the manual registration results. Specifically, the registration model can be. In this embodiment, the vascular three-dimensional models of multiple angiographic images are input into the registration model for registration to obtain the change data of the lumen diameter at each position of the coronary artery during the cardiac cycle; further, the real change data of the lumen area is determined based on the change data of the lumen diameter.

[0041] In some embodiments, optionally, the 3D blood vessel models of multiple angiography images may be manually registered.

[0042] S130, constructing a hemodynamic simulation model of the coronary artery; the hemodynamic simulation model is used to obtain simulated change data of the lumen area at each position of the coronary artery through simulation calculation.

[0043] In this embodiment, the hemodynamic simulation model of the coronary artery is constructed, and the coronary artery can be simulated based on the hemodynamic simulation model to determine the simulated change data of the lumen area at each position of the coronary artery. The simulated change data refers to the change data of the lumen area over time calculated by simulating the coronary artery, and the simulated change data includes the simulated lumen area and the simulation time corresponding to the simulated lumen area.

[0044] Specifically, the hemodynamic simulation model includes a coronary artery flow continuity sub-model, an energy sub-model, a vessel wall force sub-model and a vessel diameter change sub-model.

[0045] For any segment of the coronary artery, the flow continuity submodel of the segment is as follows:

[0046]

[0047] Among them, V n+1 represents the volume of the vessel segment at the n+1th time step, V n represents the volume of the vessel segment at the nth time step, represents the inlet flow at the n+1th time step, represents the outlet flow at the n+1th time step.

[0048] For any segment of the coronary artery, the energy submodel of the segment is as follows:

[0049] E in (u)+p in =E out (u)+p out -p loss

[0050] Among them, E in (u) represents the kinetic energy at the entrance of the blood vessel segment, E out (u) represents the kinetic energy at the outlet of the blood vessel segment, u is the flow velocity, p in represents the static pressure at the inlet of the blood vessel segment, p out represents the static pressure at the outlet of the blood vessel segment, p loss It refers to the static pressure loss caused by friction, turbulence and other factors when blood passes through a blood vessel segment.

[0051] It should be noted that Where ρ is the blood density, Q V is the volume flow rate (which can be calculated from the lumen area S and velocity u, i.e. Q v =Su).

[0052] The pipe wall force submodel is as follows:

[0053] P=-ρQ v (u out -u in )+p in *S in +p out *S out

[0054] Where P represents the force on the tube wall, ρ represents the blood density, and u out represents the blood flow velocity at the coronary artery outlet, u in Blood flow velocity, p in represents the blood pressure at the entrance of the coronary artery, p out represents the blood pressure at the coronary artery outlet, S in represents the cross-sectional area at the entrance of the coronary artery, S out Represents the cross-sectional area at the coronary artery outlet.

[0055] The pipe diameter change sub-model is as follows:

[0056]

[0057] Among them, P(z,t) represents the pressure at time t, P 0 (z) represents the initial pressure, r 0 (z) represents the initial lumen radius, S 0(z) represents the initial lumen area, S(z,t) represents the lumen area at time t, z represents the length along the centerline of the blood vessel, and k1, k2, and k3 are constants.

[0058] S140, obtaining the initial flow of the coronary artery, taking the initial flow as the optimization starting point, iteratively updating the initial flow based on a preset optimization algorithm, and determining the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration round based on the hemodynamic simulation model.

[0059] The initial flow is a preset flow value of the coronary artery, and the initial flow can be iteratively updated by a preset optimization algorithm. In this embodiment, the initial flow of the coronary artery is obtained, and the initial flow is used as the optimization starting point, and the initial flow is iteratively updated based on the preset optimization algorithm; for each iteration round, the simulated change data of the lumen area of ​​each position of the coronary artery corresponding to the initial flow of each iteration round is determined based on the hemodynamic simulation model. The preset optimization algorithm can be Newton's method, quasi-Newton's method, gradient descent method, etc., which are not limited here.

[0060] On the basis of the above embodiment, optionally, the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration round based on the hemodynamic simulation model includes: for each iteration round, determining the boundary conditions of the coronary artery in the current round, the boundary conditions include inlet boundary conditions and outlet boundary conditions, the inlet boundary conditions are inlet blood pressure, the outlet boundary conditions are outlet resistance, and the outlet resistance is the ratio of outlet pressure to the initial flow of the current round; simulating the hemodynamic simulation model based on the inlet blood pressure and the outlet resistance to determine the simulated change data of the lumen area at each position of the coronary artery in the current round.

[0061] In this embodiment, for each iteration round, the inlet blood pressure of the coronary artery entrance is used as the inlet boundary condition, and the outlet resistance of the coronary artery exit is used as the outlet boundary condition. The hemodynamic simulation model is simulated based on the inlet blood pressure and the outlet resistance. The sub-models in the hemodynamic simulation model are combined to calculate the simulated change data of the lumen area at each position of the coronary artery in the current round.

[0062] Exemplarily, the calculation formula of the outlet resistance is as follows:

[0063] R=P / Q

[0064] Among them, R represents the outlet resistance, P represents the outlet pressure, and Q represents the initial flow rate of the current round. It can be understood that in the simulation calculation process, the outlet resistance is a constant value.

[0065] S150. When the function value of the objective function is the minimum value, determine the target flow rate of the coronary artery; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area.

[0066] The objective function includes lumen area difference and time difference; the lumen area difference is used to measure the difference between the real lumen area and the simulated lumen area, and the time difference is used to measure the difference between the real time when the contrast agent arrives at each frame and the simulated time.

[0067] Specifically, the objective function is:

[0068] loss=loss1+loss2

[0069] The lumen area difference function is:

[0070]

[0071] The time difference function is:

[0072]

[0073] Among them, loss represents the objective function, loss1 represents the lumen area difference, loss2 represents the time difference, S cal represents the simulated lumen area, S represents the real lumen area, T cal represents the simulated time when the contrast agent arrives at each frame, and T represents the real time when the contrast agent arrives at each frame.

[0074] In this embodiment, the function value of the objective function is minimized, and when the function value of the objective function is the minimum value, the initial flow corresponding to the minimum value of the objective function is used to determine the target flow of the coronary artery. It can be understood that the initial flow is continuously updated with the iteration of the preset optimization algorithm.

[0075] Based on the above embodiment, optionally, determining the target flow of the coronary artery when the function value of the objective function is the minimum value includes: for any iterative round, determining the function value of the objective function based on the real change data and the simulated change data of the current round; and when the function value of the objective function is the minimum value, determining the initial flow of the current round as the target flow of the coronary artery.

[0076] In this embodiment, for any iterative round, the lumen area difference is determined based on the real lumen area in the real change data and the simulated lumen area in the simulated change data of the current round; the time difference is determined based on the real time in the real change data and the simulated time in the simulated change data of the current round; further, the function value of the objective function of the current round is determined according to the lumen area difference and the time difference; when the function value of the objective function of the current round is the minimum value, the initial flow of the current round is determined as the target flow of the coronary artery.

[0077] S160. Determine a coronary blood flow reserve fraction based on the target flow of the coronary artery.

[0078] Among them, the coronary artery blood flow reserve fraction (Fractional Flow Reserve, FFR) is a very important indicator in the field of cardiology, especially in the diagnosis and management of coronary artery disease. The coronary artery blood flow reserve fraction represents the ratio between the maximum blood flow that can be obtained in the myocardial area supplied by the stenotic coronary artery under the maximum hyperemia state and the maximum blood flow that can be obtained in the area when there is no stenosis in theory. In this embodiment, the boundary conditions are determined based on the target flow of the coronary artery, and the coronary artery blood flow reserve fraction is determined by simulation in the three-dimensional vascular model of the coronary artery.

[0079] Based on the above embodiment, optionally, determining the coronary blood flow reserve fraction based on the target flow of the coronary artery includes: determining the boundary conditions of the coronary artery based on the target flow of the coronary artery; performing blood flow simulation on the coronary artery based on the boundary conditions of the coronary artery to simulate the flow of blood in the coronary artery and determine the coronary blood flow reserve fraction.

[0080] In this embodiment, boundary conditions are set based on the target flow of the coronary artery. Specifically, the boundary conditions include inlet boundary conditions, outlet boundary conditions and vascular wall conditions. The inlet boundary conditions are usually set to conditions related to the flow of the aortic root, such as flow waveform and inlet blood pressure; the outlet boundary conditions can be outlet resistance. Further, the coronary artery is simulated based on the boundary conditions of the coronary artery to simulate the flow of blood in the coronary artery. In the simulation results, the pressure values ​​at the distal end of the stenosis and the aortic root are extracted. According to the definition of FFR (Pd / Pa×100%), the FFR value of the coronary artery is calculated. The FFR value reflects the degree of influence of stenosis on blood flow reserve, and is an important basis for evaluating the severity of coronary artery stenosis and guiding treatment decisions. Among them, the flow of blood in the coronary artery includes the distribution of parameters such as velocity, pressure, and shear force. These parameters are crucial for understanding hemodynamic characteristics and evaluating the impact of stenosis on blood flow.

[0081] The technical solution of this embodiment is to obtain a plurality of angiographic images of the coronary artery during the cardiac cycle and perform three-dimensional modeling to obtain a vascular three-dimensional model of the plurality of angiographic images; align the vascular three-dimensional models of the plurality of angiographic images to determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle; construct a hemodynamic simulation model of the coronary artery; obtain the initial flow of the coronary artery, take the initial flow as the optimization starting point, iteratively update the initial flow based on a preset optimization algorithm, and determine the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration based on the hemodynamic simulation model; determine the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area; and determine the coronary blood flow reserve fraction based on the target flow of the coronary artery. Taking the difference between the real change data and the simulated change data of the lumen area as the objective function, the flow in the coronary artery is optimized to obtain the target flow. The coronary blood flow reserve fraction is determined based on the target flow, which solves the problem of large deviation in the calculation of hemodynamic parameters due to the low frame rate of the angiography image. The coronary blood flow reserve fraction can be obtained without loss of precision, thereby improving the accuracy of the coronary blood flow reserve fraction.

[0082] Embodiment 2

[0083] Figure 2 Schematic diagram of the structure of a device for determining hemodynamic parameters provided by Embodiment 2 of the present invention. Figure 2 As shown, the device comprises:

[0084] A vascular three-dimensional model building module 210 is used to obtain a plurality of angiographic images of the coronary artery during a cardiac cycle, and to perform three-dimensional modeling on the angiographic images respectively to obtain a vascular three-dimensional model of the plurality of angiographic images;

[0085] A vascular three-dimensional model registration module 220, for registering the vascular three-dimensional models of the plurality of angiography images to determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle;

[0086] A hemodynamic simulation model building module 230 is used to build a hemodynamic simulation model of the coronary artery; the hemodynamic simulation model is used to obtain simulated change data of the lumen area at each position of the coronary artery through simulation calculation;

[0087] An initial flow optimization module 240 is used to obtain the initial flow of the coronary artery, take the initial flow as the optimization starting point, iteratively update the initial flow based on a preset optimization algorithm, and determine the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration based on the hemodynamic simulation model;

[0088] A target flow determination module 250 is used to determine the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area;

[0089] The coronary artery blood flow reserve fraction determination module 260 is configured to determine the coronary artery blood flow reserve fraction based on the target flow rate of the coronary artery.

[0090] The technical solution of this embodiment is to obtain a plurality of angiographic images of the coronary artery during the cardiac cycle and perform three-dimensional modeling to obtain a three-dimensional model of the blood vessels of the plurality of angiographic images; align the three-dimensional model of the blood vessels of the plurality of angiographic images to determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle; construct a hemodynamic simulation model of the coronary artery; obtain the initial flow of the coronary artery, take the initial flow as the optimization starting point, iteratively update the initial flow based on a preset optimization algorithm, and determine the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration based on the hemodynamic simulation model; determine the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area; and determine the coronary blood flow reserve fraction based on the target flow of each coronary artery. Taking the difference between the real change data and the simulated change data of the lumen area as the objective function, the flow in the coronary artery is optimized to obtain the target flow. The coronary blood flow reserve fraction is determined based on the target flow, which solves the problem of large deviation in the calculation of hemodynamic parameters due to the low frame rate of the angiography image. The coronary blood flow reserve fraction can be obtained without loss of precision, thereby improving the accuracy of the coronary blood flow reserve fraction.

[0091] On the basis of the above embodiment, optionally, the vascular three-dimensional model registration module 220 is specifically used to input the vascular three-dimensional models of the multiple angiography images into the registration model for registration, so as to obtain the real change data of the lumen area of ​​each position of the coronary artery during the cardiac cycle; the registration model is obtained by training the training set based on the manual registration results.

[0092] On the basis of the above embodiment, optionally, the hemodynamic simulation model includes a flow continuity sub-model, an energy sub-model, a vessel wall force sub-model and a vessel diameter change sub-model of the coronary artery.

[0093] Based on the above embodiment, optionally, the initial flow optimization module 240 includes a simulation change data determination unit, which is used to determine the boundary conditions of the coronary artery in the current round for each iteration round, wherein the boundary conditions include an inlet boundary condition and an outlet boundary condition, wherein the inlet boundary condition is the inlet blood pressure, and the outlet boundary condition is the outlet resistance, and the outlet resistance is the ratio of the outlet pressure to the initial flow of the current round; based on the inlet blood pressure and the outlet resistance, the hemodynamic simulation model is simulated and calculated to determine the simulated change data of the lumen area at each position of the coronary artery in the current round.

[0094] Based on the above embodiment, optionally, the target flow determination module 250 is used to determine the function value of the objective function for any iteration round based on the real change data and the simulated change data of the current round; when the function value of the objective function is the minimum value, the initial flow of the current round is determined as the target flow of the coronary artery.

[0095] Based on the above embodiment, optionally, the objective function includes lumen area difference and time difference; the lumen area difference is used to measure the difference between the real lumen area and the simulated lumen area, and the time difference is used to measure the difference between the real time when the contrast agent arrives at each frame and the simulated time.

[0096] Based on the above embodiment, optionally, the coronary blood flow reserve fraction determination module 260 is used to determine the boundary conditions of the coronary arteries based on the target flow of the coronary arteries; perform blood flow simulation on the coronary arteries based on the boundary conditions of the coronary arteries, simulate the flow of blood in the coronary arteries, and determine the coronary blood flow reserve fraction.

[0097] The hemodynamic parameter determination device provided in the embodiment of the present invention can execute the hemodynamic parameter determination method provided in any embodiment of the present invention, and has the corresponding functional modules and beneficial effects of the execution method.

[0098] Embodiment 3

[0099] Figure 31 is a schematic diagram of the structure of an electronic device provided in Embodiment 3 of the present invention. The electronic device 10 is intended to represent various forms of digital computers, such as laptop computers, desktop computers, workstations, personal digital assistants, servers, blade servers, mainframe computers, and other suitable computers. The electronic device may also represent various forms of mobile devices, such as personal digital processing, cellular phones, smart phones, wearable devices (such as helmets, glasses, watches, etc.) and other similar computing devices. The components shown herein, their connections and relationships, and their functions are merely examples and are not intended to limit the implementation of the present invention described and / or required herein.

[0100] like Figure 3 As shown, the electronic device 10 includes at least one processor 11, and a memory connected to the at least one processor 11, such as a read-only memory (ROM) 12, a random access memory (RAM) 13, etc., wherein the memory stores a computer program that can be executed by at least one processor, and the processor 11 can perform various appropriate actions and processes according to the computer program stored in the read-only memory (ROM) 12 or the computer program loaded from the storage unit 18 to the random access memory (RAM) 13. In the RAM 13, various programs and data required for the operation of the electronic device 10 can also be stored. The processor 11, the ROM 12, and the RAM 13 are connected to each other through a bus 14. An input / output (I / O) interface 15 is also connected to the bus 14.

[0101] A number of components in the electronic device 10 are connected to the I / O interface 15, including: an input unit 16, such as a keyboard, a mouse, etc.; an output unit 17, such as various types of displays, speakers, etc.; a storage unit 18, such as a disk, an optical disk, etc.; and a communication unit 19, such as a network card, a modem, a wireless communication transceiver, etc. The communication unit 19 allows the electronic device 10 to exchange information / data with other devices through a computer network such as the Internet and / or various telecommunication networks.

[0102] The processor 11 may be a variety of general and / or dedicated processing components with processing and computing capabilities. Some examples of the processor 11 include, but are not limited to, a central processing unit (CPU), a graphics processing unit (GPU), various dedicated artificial intelligence (AI) computing chips, various processors running machine learning model algorithms, a digital signal processor (DSP), and any appropriate processor, controller, microcontroller, etc. The processor 11 executes the various methods and processes described above, such as a hemodynamic parameter determination method.

[0103] In some embodiments, the hemodynamic parameter determination method may be implemented as a computer program, which is tangibly contained in a computer-readable storage medium, such as a storage unit 18. In some embodiments, part or all of the computer program may be loaded and / or installed on the electronic device 10 via the ROM 12 and / or the communication unit 19. When the computer program is loaded into the RAM 13 and executed by the processor 11, one or more steps of the hemodynamic parameter determination method described above may be performed. Alternatively, in other embodiments, the processor 11 may be configured to perform the hemodynamic parameter determination method in any other appropriate manner (e.g., by means of firmware).

[0104] Various implementations of the systems and techniques described above herein can be implemented in digital electronic circuit systems, integrated circuit systems, field programmable gate arrays (FPGAs), application specific integrated circuits (ASICs), application specific standard products (ASSPs), systems on chips (SOCs), load programmable logic devices (CPLDs), computer hardware, firmware, software, and / or combinations thereof. These various implementations can include: being implemented in one or more computer programs that can be executed and / or interpreted on a programmable system including at least one programmable processor, which can be a special purpose or general purpose programmable processor that can receive data and instructions from a storage system, at least one input device, and at least one output device, and transmit data and instructions to the storage system, the at least one input device, and the at least one output device.

[0105] The computer program for implementing the hemodynamic parameter determination method of the present invention can be written in any combination of one or more programming languages. These computer programs can be provided to a processor of a general-purpose computer, a special-purpose computer or other programmable data processing device, so that when the computer program is executed by the processor, the functions / operations specified in the flow chart and / or block diagram are implemented. The computer program can be executed entirely on the machine, partially on the machine, partially on the machine as a stand-alone software package and partially on a remote machine, or entirely on a remote machine or server.

[0106] Embodiment 4

[0107] Embodiment 4 of the present invention further provides a computer-readable storage medium, wherein the computer-readable storage medium stores computer instructions, and the computer instructions are used to enable a processor to execute a method for determining hemodynamic parameters, the method comprising:

[0108] Acquire multiple angiographic images of the coronary artery during the cardiac cycle, and perform three-dimensional modeling to obtain three-dimensional models of the blood vessels of the multiple angiographic images; align the three-dimensional models of the blood vessels of the multiple angiographic images to determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle; construct a hemodynamic simulation model of the coronary artery; acquire the initial flow of the coronary artery, take the initial flow as the optimization starting point, iteratively update the initial flow based on a preset optimization algorithm, and determine the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration based on the hemodynamic simulation model; determine the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area; determine the coronary blood flow reserve fraction based on the target flow of the coronary artery.

[0109] In the context of the present invention, a computer-readable storage medium may be a tangible medium that may contain or store a computer program for use by or in combination with an instruction execution system, device or equipment. A computer-readable storage medium may include, but is not limited to, electronic, magnetic, optical, electromagnetic, infrared, or semiconductor systems, devices or equipment, or any suitable combination of the foregoing. Alternatively, a computer-readable storage medium may be a machine-readable signal medium. A more specific example of a machine-readable storage medium may include an electrical connection based on one or more lines, a portable computer disk, a hard disk, a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disk read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the foregoing.

[0110] To provide interaction with a user, the systems and techniques described herein may be implemented on an electronic device having: a display device (e.g., a CRT (cathode ray tube) or LCD (liquid crystal display) monitor) for displaying information to the user; and a keyboard and a pointing device (e.g., a mouse or trackball) through which the user can provide input to the electronic device. Other types of devices may also be used to provide interaction with the user; for example, the feedback provided to the user may be any form of sensory feedback (e.g., visual feedback, auditory feedback, or tactile feedback); and input from the user may be received in any form (including acoustic input, voice input, or tactile input).

[0111] The systems and techniques described herein may be implemented in a computing system that includes backend components (e.g., as a data server), or a computing system that includes middleware components (e.g., an application server), or a computing system that includes frontend components (e.g., a user computer with a graphical user interface or a web browser through which a user can interact with implementations of the systems and techniques described herein), or a computing system that includes any combination of such backend components, middleware components, or frontend components. The components of the system may be interconnected by any form or medium of digital data communication (e.g., a communication network). Examples of communication networks include: a local area network (LAN), a wide area network (WAN), a blockchain network, and the Internet.

[0112] A computing system may include a client and a server. The client and the server are generally remote from each other and usually interact through a communication network. The client and server relationship is generated by computer programs running on the corresponding computers and having a client-server relationship with each other. The server may be a cloud server, also known as a cloud computing server or cloud host, which is a host product in the cloud computing service system to solve the defects of difficult management and weak business scalability in traditional physical hosts and VPS services.

[0113] It should be understood that the various forms of processes shown above can be used to reorder, add or delete steps. For example, the steps described in the present invention can be executed in parallel, sequentially or in different orders, as long as the desired results of the technical solution of the present invention can be achieved, and this document does not limit this.

[0114] The above specific implementations do not constitute a limitation on the protection scope of the present invention. It should be understood by those skilled in the art that various modifications, combinations, sub-combinations and substitutions can be made according to design requirements and other factors. Any modification, equivalent substitution and improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims

1. A method for determining hemodynamic parameters, characterized in that: include: Acquire multiple angiographic images of the coronary artery during the cardiac cycle, and perform three-dimensional modeling on the angiographic images respectively to obtain three-dimensional blood vessel models of the multiple angiographic images; Registering the three-dimensional blood vessel models of the plurality of angiography images to determine real change data of the lumen area at each position of the coronary artery during the cardiac cycle; Constructing a hemodynamic simulation model of the coronary artery; the hemodynamic simulation model is used to obtain simulated change data of the lumen area at each position of the coronary artery through simulation calculation; Acquiring an initial flow rate of the coronary artery, taking the initial flow rate as an optimization starting point, iteratively updating the initial flow rate based on a preset optimization algorithm, and determining simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow rate of each iteration based on the hemodynamic simulation model; When the function value of the objective function is the minimum value, determining the target flow rate of the coronary artery; the objective function is used to measure the difference between the real change data and the simulated change data of the lumen area; A coronary flow reserve fraction is determined based on the target flow rate of the coronary artery.

2. The method according to claim 1, characterized in that The registering of the three-dimensional blood vessel models of the plurality of angiography images to determine the real change data of the lumen area of ​​each position of the coronary artery during the cardiac cycle includes: The three-dimensional blood vessel models of the multiple angiography images are input into the registration model for registration to obtain the real change data of the lumen area of ​​each position of the coronary artery during the cardiac cycle; the registration model is trained for the training set based on the manual registration results.

3. The method according to claim 1, characterized in that The hemodynamic simulation model includes a flow continuity sub-model, an energy sub-model, a vessel wall force sub-model and a vessel diameter change sub-model of the coronary artery.

4. The method according to claim 1, characterized in that The method of determining the simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow rate of each iteration based on the hemodynamic simulation model includes: For each iteration round, determining the boundary conditions of the coronary artery in the current round, the boundary conditions including an inlet boundary condition and an outlet boundary condition, the inlet boundary condition being the inlet blood pressure, the outlet boundary condition being the outlet resistance, and the outlet resistance being the ratio of the outlet pressure to the initial flow of the current round; The hemodynamic simulation model is simulated and calculated based on the inlet blood pressure and the outlet resistance to determine simulated change data of the lumen area at each position of the coronary artery in the current round.

5. The method according to claim 4, characterized in that The step of determining the target flow rate of the coronary artery when the function value of the objective function is the minimum value comprises: For any iteration round, determining the function value of the objective function based on the real change data and the simulated change data of the current round; When the function value of the objective function is the minimum value, the initial flow rate of the current round is determined as the target flow rate of the coronary artery.

6. The method according to claim 5, characterized in that The objective function includes lumen area difference and time difference; the lumen area difference is used to measure the difference between the real lumen area and the simulated lumen area, and the time difference is used to measure the difference between the real time when the contrast agent arrives at each frame and the simulated time.

7. The method according to claim 1, characterized in that The determining of the coronary artery blood flow reserve fraction based on the target flow of the coronary artery comprises: determining a boundary condition of the coronary artery based on a target flow rate of the coronary artery; A blood flow simulation is performed on the coronary artery based on the boundary conditions of the coronary artery to simulate the flow of blood in the coronary artery and determine the coronary artery blood flow reserve fraction.

8. A device for determining hemodynamic parameters, characterized in that: include: A vascular three-dimensional model building module is used to obtain a plurality of angiographic images of the coronary artery during the cardiac cycle, and to perform three-dimensional modeling on the angiographic images respectively to obtain a vascular three-dimensional model of the plurality of angiographic images; A vascular three-dimensional model registration module, used to register the vascular three-dimensional models of the plurality of angiography images, and determine the real change data of the lumen area at each position of the coronary artery during the cardiac cycle; A hemodynamic simulation model building module is used to build a hemodynamic simulation model of the coronary artery; the hemodynamic simulation model is used to obtain simulated change data of the lumen area at each position of the coronary artery through simulation calculation; an initial flow optimization module, for obtaining the initial flow of the coronary artery, taking the initial flow as the optimization starting point, iteratively updating the initial flow based on a preset optimization algorithm, and determining, based on the hemodynamic simulation model, simulated change data of the lumen area at each position of the coronary artery corresponding to the initial flow of each iteration round; a target flow determination module, used for determining the target flow of the coronary artery when the function value of the objective function is the minimum value; the objective function is used for measuring the difference between the real change data and the simulated change data of the lumen area; The coronary artery blood flow reserve fraction determination module is used to determine the coronary artery blood flow reserve fraction based on the target flow of the coronary artery.

9. An electronic device, characterized in that: The electronic device comprises: at least one processor; and a memory communicatively connected to the at least one processor; wherein, The memory stores a computer program executable by the at least one processor, and the computer program is executed by the at least one processor so that the at least one processor can perform the hemodynamic parameter determination method according to any one of claims 1 to 7.

10. A computer-readable storage medium, characterized in that: The computer-readable storage medium stores computer instructions, and the computer instructions are used to enable a processor to implement the method for determining hemodynamic parameters according to any one of claims 1 to 7 when executed.

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