Vascular pressure difference, microcirculation resistance analysis method, device, equipment and medium

Abstract

The application provides a blood vessel pressure difference, microcirculation resistance analysis method, device, equipment and medium, the blood vessel pressure difference analysis method comprises: obtaining blood flow velocity distribution data of at least one blood vessel section in a to-be-detected blood vessel section; based on a preset pressure difference model, the unit length pressure difference corresponding to each blood vessel section is calculated according to the blood flow velocity distribution data; numerical integration is carried out on the unit length pressure difference in the range of the to-be-detected blood vessel section, and the pressure difference of the to-be-detected blood vessel section is obtained. The blood vessel pressure difference analysis method can improve the accuracy of blood vessel pressure difference calculation by calculating the real-time unit length pressure difference according to the change of blood flow velocity with time at each position in the to-be-detected blood vessel section, and then integrating along the blood vessel to obtain the pressure difference of the entire to-be-detected blood vessel section.

Description

Technical Field

[0001] This invention relates to the field of intravascular interventional imaging medical devices, and in particular to a method, device, equipment and medium for analyzing vascular pressure difference and microcirculation resistance. Background Technology

[0002] Coronary artery disease (CAD) has become the leading cause of death worldwide, with atherosclerosis being the primary cause. Endovascular interventional imaging techniques refer to a series of methods that involve inserting catheters into diseased blood vessels through vascular puncture to perform imaging examinations of the affected area. Endovascular interventional imaging techniques are of great significance for accurately identifying atherosclerotic lesions and guiding clinical treatment plans. However, endovascular interventional imaging techniques are limited to assessing the morphological structure of atherosclerotic plaques and coronary artery stenosis; they cannot accurately reflect functional changes in coronary blood flow and supply caused by changes in vascular morphology.

[0003] Fractional flow reserve (FFR) measures the pressure difference between the distal and proximal ends of a stenotic segment of the coronary artery, effectively reflecting the impact of stenosis on vascular blood supply and assessing whether the lesion leads to ischemia of the myocardium perfused by the coronary arteries. Traditionally, FFR is measured using a pressure guidewire, but this procedure is complex, time-consuming, and requires expensive surgical consumables (FFR guidewires). Side effects from the injection of vasodilators can cause discomfort to patients, and the guidewire can easily damage the patient's blood vessels during intervention. These factors limit the widespread adoption of the pressure guidewire method for measuring FFR.

[0004] In addition, current clinical research has found that besides the pressure drop in the proximal and distal segments of blood vessels caused by coronary artery disease, the index of microcirculatory resistance (IMR) in downstream small vessels is also a major factor affecting myocardial blood supply. Obtaining microcirculatory resistance requires accurate measurement of blood flow velocity and pressure in distal vessels.

[0005] Currently, existing technologies primarily rely on imaging examinations to establish corresponding geometric models, and then input some measurement or empirical data to perform fluid dynamics calculations to obtain the required hemodynamic parameters (such as FFR and IMR). On the one hand, the quality of the model significantly affects the accuracy of the calculation results, and some models are based on empirical data and do not consider individual differences. On the other hand, obtaining accurate individualized pressure values ​​and blood flow velocities as boundary conditions for hemodynamic calculations is crucial, and current methods for measuring parameters such as blood flow are not yet highly precise, easily introducing errors into the calculations. Summary of the Invention

[0006] In view of the above-mentioned problems in the prior art, the purpose of the present invention is to provide a method, device, equipment and medium for analyzing vascular pressure difference and microcirculation resistance, which can improve the accuracy of vascular pressure difference calculation and improve the accuracy of microcirculation resistance calculation.

[0007] To address the above problems, this invention provides a method for analyzing vascular pressure differentials, comprising:

[0008] Obtain blood flow velocity distribution data for at least one cross-section of the blood vessel segment to be detected;

[0009] Based on a preset pressure difference model, the pressure difference per unit length corresponding to each of the blood vessel cross sections is calculated according to the blood flow velocity distribution data.

[0010] The pressure difference per unit length within the range of the blood vessel segment to be tested is numerically integrated to obtain the pressure difference of the blood vessel segment to be tested.

[0011] Further, acquiring blood flow velocity distribution data of at least one cross-section of the blood vessel segment to be detected includes:

[0012] Phase information from multiple scans at each of the aforementioned blood vessel cross sections was obtained;

[0013] The phase difference between each two adjacent scans is determined based on the phase information of each two adjacent scans;

[0014] The blood flow velocity distribution data of the blood vessel cross section is calculated based on the phase difference between each two adjacent scans.

[0015] Furthermore, the phase information is the phase information of optical coherence tomography signal or intravascular ultrasound signal.

[0016] Further, the step of numerically integrating the pressure difference per unit length within the range of the blood vessel segment to be detected to obtain the pressure difference of the blood vessel segment to be detected includes:

[0017] The pressure difference per unit length of the blood vessel segment to be tested is obtained by summing the cumulative pressure differences at each cross-section of the blood vessel segment to be tested.

[0018] Furthermore, the method also includes:

[0019] Obtain the distal blood flow of the blood vessel segment to be detected;

[0020] The pressure difference of the blood vessel segment to be detected is corrected based on the distal blood flow to obtain the corrected pressure difference.

[0021] Further, acquiring the distal blood flow of the blood vessel segment to be detected includes:

[0022] Obtain blood flow velocity distribution data at the distal cross-section of the blood vessel segment to be detected;

[0023] The distal blood flow rate of the vessel segment to be tested is calculated based on the blood flow velocity distribution data of the distal section.

[0024] Further, the step of calculating the distal blood flow of the vessel segment to be detected based on the blood flow velocity distribution data of the distal section includes:

[0025] Obtain an image of the vascular structure of the blood vessel segment to be detected;

[0026] The structural image of the distal section of the blood vessel segment to be detected is determined based on the vascular structure image;

[0027] The blood flow region of the distal section is determined based on the structural image of the distal section;

[0028] Based on the blood flow region of the distal section and the blood flow velocity distribution data, the blood flow velocity is numerically integrated within the blood flow region of the distal section to obtain the distal blood flow rate.

[0029] Another aspect of the present invention provides a method for analyzing microcirculation resistance, the method comprising:

[0030] The pressure difference and proximal pressure value of the blood vessel segment to be tested are obtained, and the pressure difference is determined based on the blood vessel pressure difference analysis method described above.

[0031] Obtain the distal blood flow of the blood vessel segment to be detected;

[0032] The distal pressure value of the blood vessel segment to be tested is determined based on the pressure difference and the proximal pressure value.

[0033] The microcirculatory resistance of the tested vascular segment is calculated based on the distal pressure value and the distal blood flow.

[0034] Another aspect of the present invention provides a vascular pressure differential analysis device, comprising:

[0035] The blood flow velocity acquisition module is used to acquire blood flow velocity distribution data of at least one cross section of the blood vessel segment to be detected.

[0036] The first pressure difference calculation module is used to calculate the pressure difference per unit length corresponding to each of the blood vessel cross sections based on the preset pressure difference model and the blood flow velocity distribution data.

[0037] The second pressure difference calculation module is used to perform numerical integration of the pressure difference per unit length within the range of the blood vessel segment to be detected, so as to obtain the pressure difference of the blood vessel segment to be detected.

[0038] Another aspect of the present invention provides a microcirculation resistance analysis device, characterized in that it comprises:

[0039] The first acquisition module is used to acquire the pressure difference and proximal pressure value of the blood vessel segment to be detected, wherein the pressure difference is determined based on the blood vessel pressure difference analysis method described above.

[0040] The second acquisition module is used to acquire the distal blood flow of the blood vessel segment to be detected;

[0041] The distal pressure calculation module is used to determine the distal pressure value of the blood vessel segment to be detected based on the pressure difference and the proximal pressure value.

[0042] The microcirculation resistance calculation module is used to calculate the microcirculation resistance of the blood vessel segment to be tested based on the distal pressure value and the distal blood flow.

[0043] In another aspect, the present invention provides an electronic device including a processor and a memory, wherein the memory stores at least one instruction or at least one program, the at least one instruction or the at least one program being loaded and executed by the processor to implement the vascular pressure differential analysis method or microcirculation resistance analysis method as described above.

[0044] In another aspect, the present invention provides a computer-readable storage medium storing at least one instruction or at least one program, wherein the at least one instruction or the at least one program is loaded and executed by a processor to implement the vascular pressure differential analysis method or the microcirculation resistance analysis method as described above.

[0045] Due to the above technical solution, the present invention has the following beneficial effects:

[0046] According to the vascular pressure difference analysis method of the present invention, the real-time pressure difference per unit length is calculated by using a pressure difference model based on the change of blood flow velocity at various locations within the vascular segment to be tested over time, and then the pressure difference of the entire vascular segment to be tested is obtained by integrating along the vascular segment, which can improve the accuracy of vascular pressure difference calculation. Attached Figure Description

[0047] To more clearly illustrate the technical solutions of the present invention, the accompanying drawings used in the description of the embodiments or prior art will be briefly introduced below. Obviously, the drawings described below are merely some embodiments of the present invention, and those skilled in the art can obtain other drawings based on these drawings without any creative effort.

[0048] Figure 1 This is a schematic diagram of the implementation environment provided in one embodiment of the present invention;

[0049] Figure 2 This is a flowchart of a method for analyzing vascular pressure differences provided in one embodiment of the present invention;

[0050] Figure 3 This is a flowchart of an OCT imaging method provided in one embodiment of the present invention;

[0051] Figure 4 This is a schematic diagram of an OCT imaging method provided in one embodiment of the present invention;

[0052] Figure 5 This is a flowchart of a microcirculation resistance analysis method provided in one embodiment of the present invention;

[0053] Figure 6 This is a schematic diagram of the structure of a vascular pressure differential analysis device provided in one embodiment of the present invention;

[0054] Figure 7 This is a schematic diagram of the microcirculation resistance analysis device provided in one embodiment of the present invention;

[0055] Figure 8 This is a schematic diagram of the structure of an electronic device provided in one embodiment of the present invention. Detailed Implementation

[0056] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0057] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this invention are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of the invention described herein can be implemented in orders other than those illustrated or described herein. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover a non-exclusive inclusion; for example, a process, method, apparatus, product, or device that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such processes, methods, products, or devices.

[0058] Reference manual attached Figure 1 This illustrates a schematic diagram of an implementation environment provided by an embodiment of the present invention. Figure 1As shown, the implementation environment may include at least one medical scanning device 110 and a computer device 120. The computer device 120 and each medical scanning device 110 may be directly or indirectly connected by wired or wireless communication. This embodiment of the invention does not limit this.

[0059] The computer device 120 may be, but is not limited to, various servers, personal computers, laptops, smartphones, tablets, and portable wearable devices. The server may be an independent server or a server cluster or distributed system composed of multiple servers. It may also be a cloud server that provides basic cloud computing services such as cloud services, cloud databases, cloud computing, cloud functions, cloud storage, network services, cloud communication, middleware services, domain name services, security services, content delivery networks (CDN), and big data and artificial intelligence platforms.

[0060] The medical scanning device 110 can employ imaging technologies such as optical coherence tomography (OCT) or intravascular ultrasound (IVUS). An imaging catheter is inserted deep into the distal end of the blood vessel, and contrast agent is injected through the angiography catheter to flush the vessel. Simultaneously, the imaging catheter rotates and retracts, thereby obtaining an image of the entire vascular structure of the segment under examination. The medical scanning device 110 can also acquire the phase information of the OCT or IVUS signals from each scan.

[0061] The computer device 120 can acquire the vascular structure images collected by the medical scanning device 110, as well as the phase information of each scan, and determine the pressure difference and microcirculation resistance of the vascular segment to be detected through the method provided in this embodiment of the invention, so that doctors can review them and guide timely measures.

[0062] In practical applications, the method provided by this invention can be applied to scenarios involving vascular pressure difference analysis and microcirculation resistance analysis of coronary arteries such as the left circumflex coronary artery, left anterior descending coronary artery, and right coronary artery. It can not only accurately obtain geometric images of vascular lesions during routine imaging surgery, but also simultaneously obtain vascular hemodynamic parameters such as FFR and IMR without introducing additional surgical procedures or increasing the patient's surgical burden.

[0063] It should be noted that, Figure 1 This is merely an example. Those skilled in the art will understand that, although... Figure 1 Only one medical scanning device 110 is shown in the figure, but this does not constitute a limitation on the embodiments of the present invention. It may include more or fewer medical scanning devices 110 than shown in the figure.

[0064] Reference manual attached Figure 2 This illustrates the flowchart of a vascular pressure differential analysis method provided by an embodiment of the present invention, which can be applied to... Figure 1 Among the computer devices 120, specific examples include... Figure 2 As shown, the method may include the following steps:

[0065] S210: Obtain blood flow velocity distribution data for at least one cross section of the blood vessel segment to be detected.

[0066] In this embodiment of the invention, the blood vessel segment to be detected can be a segment of a blood vessel that is abnormal relative to a normal blood vessel. The blood flow velocity distribution data can represent the distribution of blood flow velocity at multiple locations within the cross-section of the blood vessel, and can be regarded as a velocity field formed by the blood flow velocity at multiple locations within the cross-section of the blood vessel. The source of the blood flow velocity distribution data can be directly imported relevant data, or it can be obtained from other resource libraries through real-time configuration and connection, or it can be obtained from a stored database after searching based on information such as the user's name. This embodiment of the invention does not impose any restrictions on this.

[0067] In one possible embodiment, the blood flow velocity distribution data can be obtained by scanning the blood vessel segment to be detected using OCT imaging technology or IVUS imaging technology, and by calculating the phase change of the scanning signal caused by the blood flow velocity.

[0068] Specifically, acquiring blood flow velocity distribution data of at least one cross-section of the blood vessel segment to be detected may include: acquiring phase information of multiple scans at each of the blood vessel cross-sections; determining the phase difference between each two adjacent scans based on the phase information between each two adjacent scans; and calculating the blood flow velocity distribution data of the blood vessel cross-section based on the phase difference between each two adjacent scans. The phase information may be the phase information of an OCT signal or an IVUS signal.

[0069] By way of example, in conjunction with the appendix to the reference specification Figure 3 It illustrates a flowchart of an OCT imaging method provided by a possible embodiment of the present invention, such as... Figure 3 As shown, the OCT imaging method may include the following steps:

[0070] S310: Insert the OCT imaging catheter into a first predetermined position of the blood vessel segment to be detected. Specifically, the OCT imaging catheter can be inserted into the distal end position of the blood vessel segment to be detected.

[0071] S320: Inject a small amount of contrast agent into the blood vessel to partially flush it. Specifically, a mixture of saline and blood, a fat emulsion, or other liquids with weak light scattering can be used for flushing. Adenosine can also be mixed in to achieve maximum blood flow to the vessel.

[0072] S330: The OCT imaging catheter rotates at the first predetermined position while scanning at predetermined time intervals, and retracts at a predetermined speed to acquire OCT data. Specifically, as shown... Figure 4 As shown, the OCT imaging catheter can be retracted in the opposite direction of blood flow. The rotation speed of the OCT imaging catheter, the retraction speed of the OCT imaging catheter, and the predetermined time interval can be set according to actual conditions. This embodiment of the invention does not impose any restrictions on this.

[0073] S340: When the OCT imaging catheter is retracted to the second predetermined position of the blood vessel segment to be detected, the injection of contrast agent is stopped and the acquisition ends.

[0074] Intravascular OCT, as a routine vascular interventional imaging technique, is currently the highest resolution imaging method among interventional imaging methods used in clinical practice. In a standard OCT procedure, the OCT imaging catheter is inserted deep into the distal part of the blood vessel. The physician flushes the vessel by pushing contrast agent through the angiography catheter, while the OCT imaging catheter rotates and retracts to obtain a three-dimensional structural image of the entire vascular segment.

[0075] In this embodiment of the invention, during a conventional OCT procedure, an OCT imaging catheter is inserted into the distal end of the blood vessel segment to be examined. A small amount of contrast agent is injected into the vessel to partially flush it. The OCT imaging catheter then begins rotating and scanning, acquiring three-dimensional structural images of the blood vessel while simultaneously obtaining the phase information of the OCT signal for each scan. This allows for the determination of the phase change of the OCT signal caused by blood flow velocity. Based on this phase change and the principles of Doppler OCT, the blood flow velocity can be calculated.

[0076] Specifically, the phase difference between two adjacent scans can be determined by the phase information of the OCT signals from two adjacent scans, and the blood flow velocity can be calculated based on the following equation (1):

[0077]

[0078] Among them, v z λ represents the velocity of blood flowing along the segment of the blood vessel being tested. c The center wavelength of the OCT light source ΔT is the phase difference between two adjacent scans, ΔT is the time interval between two scans, n is the refractive index of the blood contrast agent mixture, and θ is the angle between the beam emitted from the OCT imaging catheter and the blood flow direction.

[0079] As can be seen from the above calculation formula (1), since the center wavelength, refractive index, and included angle are known, the blood flow velocity can be obtained by determining the time interval between the two scans and the phase change corresponding to the two scans. This can include the phase difference at various positions along the current scanning direction, thus allowing for the calculation of the velocity v. z It can also include the blood flow velocity at each location in the current scanning position and the current scanning direction.

[0080] It should be noted that before calculating blood flow velocity, the OCT signal of each scan can be filtered first, and then the blood flow velocity can be calculated based on the phase information of the OCT signal, thereby reducing the noise of the flow velocity distribution data.

[0081] It should be noted that the actual blood flow velocity can be obtained by subtracting the retraction speed of the OCT imaging catheter from the calculated blood flow velocity.

[0082] In practical applications, the rotation speed and scanning time interval of the OCT imaging catheter can be set to ensure a large overlap of scanning areas between adjacent scan lines. Therefore, the blood flow velocity at the current scanning position and direction can be directly calculated using the phase difference between two adjacent scan lines. Since the retraction speed of the OCT imaging catheter can also be preset, a small retraction speed can be set so that the change in scanning position during one full rotation is negligible. In this case, after one full rotation, phase information from multiple scans at a vessel cross-section can be obtained, allowing for the calculation of the blood flow velocity distribution data for that vessel cross-section.

[0083] In practical applications, since OCT imaging catheters rotate and scan a number of times in one revolution, in order to improve the calculation speed, some or all of the phase information with a high signal-to-noise ratio can be selected to calculate the blood flow velocity distribution data of each blood vessel cross section.

[0084] It is understood that the embodiments of the present invention only need to be performed in conventional OCT imaging surgery, without the need for additional measurement catheters. While obtaining a three-dimensional structural image of the blood vessel through OCT imaging (the three-dimensional structural image can be used to determine the structural information of vascular lesions), the actual blood flow velocity in the blood vessel can be accurately calculated using the imaging principle of Doppler OCT.

[0085] It should be noted that the above method for calculating blood flow velocity based on the principle of Doppler OCT is only an example. In practical applications, methods such as phase variance method or intensity variance method can also be used to calculate blood flow velocity. The specific content of the phase variance method or intensity variance method can be referred to the prior art. The embodiments of the present invention will not be described in detail here.

[0086] It should be noted that the specific method for scanning the blood vessel segment to be detected using IVUS imaging technology and calculating the blood flow velocity distribution data based on the phase change of the scanning signal caused by blood flow velocity can refer to the existing technology, and will not be repeated here in the embodiments of the present invention.

[0087] S220: Based on the preset pressure difference model, calculate the pressure difference per unit length corresponding to each of the blood vessel cross sections according to the blood flow velocity distribution data.

[0088] In this embodiment of the invention, the pressure difference model can be the Navier-Stokes equation. That is, after obtaining the blood flow velocity distribution data of each blood vessel cross-section, the pressure difference per unit length corresponding to each blood vessel cross-section can be directly calculated using the Navier-Stokes equation. The Navier-Stokes equation is as follows:

[0089]

[0090] Where V represents the blood flow velocity distribution data (i.e., the blood velocity vector), t represents time, D / Dt represents the total derivative, and F... b The inertial force acting on the blood is p, where p is the pressure, ρ is the density of the blood, and ν is the kinematic viscosity of the blood, ν = μ / ρ, where μ is the dynamic viscosity of the blood. Since the density and dynamic viscosity of blood are known, the inertial force acting on the blood can be ignored. Therefore, the blood flow velocity distribution data can be directly calculated using equation (2) above. That is, the pressure difference per unit length.

[0091] It should be noted that the specific details of the pressure difference per unit length calculated according to the above formula (2) can be found in the prior art, and will not be repeated here in the embodiments of the present invention.

[0092] In one possible embodiment, the pressure difference model can be a simplified two-dimensional Navier-Stokes equation. That is, after obtaining the blood flow velocity distribution data for each vessel cross-section, the simplified two-dimensional Navier-Stokes equation can be used to calculate the pressure difference per unit length for each vessel cross-section. Specifically, considering only axial flow, the simplified two-dimensional Navier-Stokes equation is as follows:

[0093]

[0094] Among them, v z Let x, y, z be the velocity of blood flowing along the direction of the blood vessel segment to be tested (i.e., along the axial direction of the blood vessel), t be time, p be pressure, ρ be the density of blood, and μ be the dynamic viscosity of blood. For blood, the density and dynamic viscosity are known, so the velocity distribution data can be directly calculated by substituting the above equation (3) with the blood flow velocity distribution data. As the pressure difference per unit length.

[0095] It should be noted that the specific details of the pressure difference per unit length calculated according to the above formula (3) can be found in the prior art, and will not be repeated here in the embodiments of the present invention.

[0096] In one possible embodiment, the pressure difference model can be a simplified one-dimensional Navier-Stokes equation. That is, after obtaining the blood flow velocity distribution data for each vessel cross-section, the two-dimensional region between the imaging catheter and the vessel can be unfolded into a parallel plate, thereby using the simplified one-dimensional Navier-Stokes equation to calculate the pressure difference per unit length for each vessel cross-section. The simplified one-dimensional Navier-Stokes equation is as follows:

[0097]

[0098] Among them, v z Let z be the velocity of blood flowing along the direction of the blood vessel segment to be tested, t be the time, p be the pressure, ρ be the density of blood, μ be the dynamic viscosity of blood, and r be the radial coordinate in polar coordinates. Since the density and dynamic viscosity of blood are known, the velocity distribution data can be directly calculated using equation (4) above. As the pressure difference per unit length.

[0099] It should be noted that the specific details of the pressure difference per unit length calculated according to the above formula (4) can be found in the prior art, and will not be repeated here in the embodiments of the present invention.

[0100] It should be noted that, in one possible embodiment, the two-dimensional region between the imaging catheter and the blood vessel can be unfolded into a parallel plate at different angles to calculate multiple pressure differences per unit length. The multiple pressure differences per unit length are then averaged to obtain the final pressure difference per unit length.

[0101] It is understandable that by averaging data from different perspectives, the accuracy of calculating the pressure difference per unit length can be improved, thereby further improving the accuracy of calculating the pressure difference in the blood vessel segment under test.

[0102] It should be noted that after calculating the pressure difference per unit length for each of the aforementioned blood vessel cross sections, the flow velocity data in the low signal-to-noise ratio region of each blood vessel cross section can be restored based on the Navier-Stokes equation according to the pressure difference per unit length, thereby obtaining more accurate blood flow velocity distribution data.

[0103] Specifically, the pressure difference per unit length can be calculated based on the blood flow velocity in some or all of the high signal-to-noise ratio regions in each blood vessel cross section. Then, based on the calculated pressure difference per unit length and the Navier-Stokes equation, the blood flow velocity in the low signal-to-noise ratio region of the blood vessel cross section can be calculated to obtain the corrected blood flow velocity, thereby obtaining the corrected blood flow velocity distribution data of the blood vessel cross section.

[0104] It is understood that the embodiments of the present invention can improve the accuracy of blood flow velocity distribution data by using the calculated pressure difference per unit length to restore the flow velocity data in the low signal-to-noise ratio region of each blood vessel cross section, thereby improving the accuracy of subsequent microcirculation resistance calculation.

[0105] S230: The pressure difference per unit length is numerically integrated within the range of the blood vessel segment to be detected to obtain the pressure difference of the blood vessel segment to be detected.

[0106] In this embodiment of the invention, the step of numerically integrating the pressure difference per unit length within the range of the blood vessel segment to be detected to obtain the pressure difference of the blood vessel segment to be detected may include:

[0107] The pressure difference per unit length of the blood vessel segment to be tested is obtained by summing the cumulative pressure differences at each cross-section of the blood vessel segment to be tested.

[0108] Specifically, for the entire blood vessel segment to be tested, the pressure difference per unit length can be measured along the retraction direction. Numerical integration is performed to obtain the pressure difference Δp across the entire blood vessel segment being tested.

[0109] In one possible embodiment, the method may further include the following steps: acquiring the distal blood flow of the blood vessel segment to be detected; correcting the pressure difference of the blood vessel segment to be detected based on the distal blood flow to obtain the corrected pressure difference.

[0110] In this embodiment of the invention, since the pressure difference per unit length corresponding to different blood vessel cross-sections calculated in step S220 may correspond to different phases of the cardiac cycle, the calculated pressure difference can be calibrated based on the distal blood flow value of the blood vessel segment to be detected, so as to eliminate the offset caused by changes in blood flow in the pressure calculation.

[0111] Specifically, obtaining the distal blood flow of the blood vessel segment to be detected may include: obtaining blood flow velocity distribution data of the distal cross section of the blood vessel segment to be detected; and calculating the distal blood flow of the blood vessel segment to be detected based on the blood flow velocity distribution data of the distal cross section.

[0112] In this embodiment of the invention, the distal cross-section can be the cross-section corresponding to the distal endpoint of the blood vessel segment to be detected, and the distal blood flow can be the blood flow through the distal cross-section per unit time. The method for obtaining the blood flow velocity distribution data of the distal cross-section can refer to the specific content in step S210, and will not be repeated here.

[0113] Specifically, calculating the distal blood flow of the vessel segment to be detected based on the blood flow velocity distribution data of the distal section may include: acquiring a vascular structure image of the vessel segment to be detected; determining a structural image of the distal section of the vessel segment to be detected based on the vascular structure image; determining a blood flow region of the distal section based on the structural image of the distal section; and numerically integrating the blood flow velocity within the blood flow region of the distal section based on the blood flow region of the distal section and the blood flow velocity distribution data to obtain the distal blood flow.

[0114] In this embodiment of the invention, the vascular structure image can be obtained by scanning the vascular segment to be detected using OCT imaging technology or IVUS imaging technology. From the vascular structure image of the vascular segment to be detected, the structural image of the distal cross-section can be obtained. Based on the structural image of the distal cross-section, the blood flow region between the imaging catheter and the blood vessel in the distal cross-section can be determined. By numerically integrating the blood flow velocity within the blood flow region of the distal cross-section, the blood flow rate of the distal cross-section, i.e., the distal blood flow rate, can be calculated.

[0115] The integral calculation formula is as follows:

[0116] Q=∫∫ (x，y)∈Ω v z (x, y)dxdy (5)

[0117] Where Q represents distal blood flow, Ω represents the blood flow region between the imaging catheter and the blood vessel in the distal section, and x and y are the spatial coordinates of the distal section, which can be obtained from the structural image of the distal section.

[0118] It is understood that the embodiments of the present invention, by numerically integrating the blood flow velocity within the blood flow region, can measure the actual blood flow at the distal end of the blood vessel, thus avoiding the influence of individual differences and having higher accuracy. Furthermore, it can also improve the accuracy of subsequent microcirculation resistance calculation.

[0119] Specifically, after obtaining the distal blood flow of the blood vessel segment to be detected, the pressure difference can be corrected based on the distal blood flow and the corresponding maximum distal blood flow to obtain the corrected pressure difference. For example, the pressure difference can be proportionally amplified using the following formula (6) based on the ratio of the maximum distal blood flow to the distal blood flow to obtain the final pressure difference:

[0120]

[0121] Where Q represents distal blood flow, Q max Δp is the maximum distal blood flow, Δp is the pressure difference of the blood vessel segment to be detected, and Δp' is the corrected pressure difference.

[0122] It is understood that, by calibrating the calculated pressure difference based on the actual blood flow value measured at the distal end of the blood vessel, the embodiments of the present invention can eliminate the offset caused by changes in blood flow in the pressure calculation, thereby further improving the accuracy of the calculation results.

[0123] In summary, the vascular pressure difference analysis method according to the embodiments of the present invention can directly calculate the real-time pressure difference per unit length using the Navier-Stokes equation based on the change of blood flow velocity at various locations within the tested vascular segment over time, and then integrate along the vascular segment to obtain the pressure difference of the entire tested vascular segment, thereby improving the accuracy of vascular pressure difference calculation.

[0124] Reference manual attached Figure 5 This illustrates the flowchart of a microcirculation resistance analysis method provided by an embodiment of the present invention, which can be applied to... Figure 1 Among the computer devices 120, specific examples include... Figure 5 As shown, the method may include the following steps:

[0125] S510: Obtain the pressure difference and proximal pressure value of the blood vessel segment to be tested.

[0126] In embodiments of the present invention, it can be based on, as follows Figures 2-4 The illustrated embodiment provides a vascular pressure difference analysis method to obtain the pressure difference of the vascular segment to be detected. For specific acquisition methods, please refer to [example...]. Figures 2-4 The content of the illustrated embodiment will not be repeated here.

[0127] In this embodiment of the invention, the proximal pressure value can be the pressure value corresponding to the proximal endpoint of the vessel segment to be detected. The absolute pressure value at the proximal endpoint of the vessel segment to be detected can be directly measured using existing measurement methods and used as the proximal pressure value. Specific measurement methods can be found in existing technologies, and will not be elaborated further in this embodiment.

[0128] S520: Obtain the distal blood flow of the blood vessel segment to be detected.

[0129] S530: Determine the distal pressure value of the blood vessel segment to be detected based on the pressure difference and the proximal pressure value.

[0130] In this embodiment of the invention, the absolute pressure value at the distal end of the target blood vessel segment, i.e., the distal pressure value, can be calculated using the following formula (7) based on the pressure difference and the proximal pressure value:

[0131] P d =P a -Δp (7)

[0132] Among them, P a P represents the proximal pressure value. d Δp represents the distal pressure value, and Δp represents the pressure difference of the blood vessel segment to be tested.

[0133] S540: Calculate the microcirculatory resistance of the vascular segment to be tested based on the distal pressure value and the distal blood flow.

[0134] In this embodiment of the invention, the microcirculatory resistance of the downstream blood vessels can be calculated using the following formula (8) based on the distal pressure value and the distal blood flow:

[0135]

[0136] Where IMR is the microcirculation resistance, P d Q represents distal pressure, and Q represents distal blood flow.

[0137] It should be noted that other contents in steps S510-S540 can be referred to as follows: Figures 2-4 The vascular pressure difference analysis method provided in the illustrated embodiment will not be described again here.

[0138] In summary, the microcirculation resistance analysis method according to embodiments of the present invention calculates the magnitude of microcirculation resistance in downstream blood vessels by combining the actual blood flow value measured at the distal end of the blood vessel with the distal pressure value calculated based on the Navier-Stokes equation, thereby improving the accuracy of microcirculation resistance calculation.

[0139] Reference manual attached Figure 6 This illustrates the structure of a vascular pressure differential analysis device 600 provided in one embodiment of the present invention. For example... Figure 6 As shown, the device 600 may include:

[0140] Blood flow velocity acquisition module 610 is used to acquire blood flow velocity distribution data of at least one cross section of the blood vessel segment to be detected;

[0141] The first pressure difference calculation module 620 is used to calculate the unit length pressure difference corresponding to each of the blood vessel cross sections based on the preset pressure difference model and the blood flow velocity distribution data.

[0142] The second pressure difference calculation module 630 is used to perform numerical integration of the pressure difference per unit length within the range of the blood vessel segment to be detected, so as to obtain the pressure difference of the blood vessel segment to be detected.

[0143] In one possible embodiment, the device 600 may further include:

[0144] The distal blood flow acquisition module is used to acquire the distal blood flow of the blood vessel segment to be detected.

[0145] The correction module is used to correct the pressure difference of the blood vessel segment to be detected based on the distal blood flow, so as to obtain the corrected pressure difference.

[0146] Reference manual attached Figure 7 This illustrates the structure of a microcirculation resistance analysis device 700 provided in one embodiment of the present invention. For example... Figure 7 As shown, the device 700 may include:

[0147] The first acquisition module 710 is used to acquire the pressure difference and proximal pressure value of the blood vessel segment to be detected. The pressure difference can be based on, for example... Figures 2-4 The method for analyzing the vascular pressure difference provided in the illustrated embodiment is used to determine this.

[0148] The second acquisition module 720 is used to acquire the distal blood flow of the blood vessel segment to be detected;

[0149] The distal pressure calculation module 730 is used to determine the distal pressure value of the blood vessel segment to be detected based on the pressure difference and the proximal pressure value.

[0150] The microcirculation resistance calculation module 740 is used to calculate the microcirculation resistance of the blood vessel segment to be detected based on the distal pressure value and the distal blood flow.

[0151] It should be noted that the apparatus provided in the above embodiments is only illustrated by the division of the above functional modules when implementing its functions. In actual applications, the above functions can be assigned to different functional modules as needed, that is, the internal structure of the device can be divided into different functional modules to complete all or part of the functions described above. In addition, the apparatus provided in the above embodiments and the corresponding method embodiments belong to the same concept, and the specific implementation process can be found in the corresponding method embodiments, which will not be repeated here.

[0152] One embodiment of the present invention also provides an electronic device, which includes a processor and a memory, wherein the memory stores at least one instruction or at least one program, the at least one instruction or the at least one program being loaded and executed by the processor to implement the vascular pressure difference analysis method or microcirculation resistance analysis method provided in the above method embodiments.

[0153] Memory can be used to store software programs and modules. The processor executes various functional applications and data processing by running the software programs and modules stored in the memory. Memory can primarily include a program storage area and a data storage area. The program storage area can store the operating system, application programs required for the functions, etc.; the data storage area can store data created based on the use of the device, etc. Furthermore, memory can include high-speed random access memory, and can also include non-volatile memory, such as at least one disk storage device, flash memory device, or other volatile solid-state storage device. Accordingly, memory can also include a memory controller to provide the processor with access to the memory.

[0154] In one specific embodiment Figure 8 This diagram illustrates a hardware structure of an electronic device for implementing the vascular pressure differential analysis method or microcirculation resistance analysis method provided in the embodiments of the present invention. The electronic device can be a computer terminal, mobile terminal, or other device. The electronic device can also participate in or include the vascular pressure differential analysis device or microcirculation resistance analysis device provided in the embodiments of the present invention. Figure 8 As shown, the electronic device 800 may include a memory 810 with one or more computer-readable storage media, a processor 820 with one or more processing cores, an input unit 830, a display unit 840, a radio frequency (RF) circuit 850, a wireless fidelity (WiFi) module 860, and a power supply 870, among other components. Those skilled in the art will understand that... Figure 8 The electronic device structure shown does not constitute a limitation on the electronic device 800, and may include more or fewer components than shown, or combine certain components, or have different component arrangements. Wherein:

[0155] The memory 810 can be used to store software programs and modules. The processor 820 performs various functional applications and data processing by running or executing the software programs and modules stored in the memory 810 and by calling data stored in the memory 810. The memory 810 may mainly include a program storage area and a data storage area. The program storage area may store the operating system, at least one application program required for a function, etc.; the data storage area may store data created based on the use of the electronic device, etc. In addition, the memory 810 may include high-speed random access memory, and may also include non-volatile memory, such as hard disk, RAM, plug-in hard disk, smart media card (SMC), secure digital (SD) card, flash card, at least one disk storage device, flash memory device, or other volatile solid-state storage device. Accordingly, the memory 810 may also include a memory controller to provide the processor 820 with access to the memory 810.

[0156] The processor 820 is the control center of the electronic device 800. It connects various parts of the electronic device via various interfaces and lines. By running or executing software programs and / or modules stored in the memory 810, and by calling data stored in the memory 810, it performs various functions and processes data of the electronic device 800, thereby providing overall monitoring of the electronic device 800. The processor 820 can be a central processing unit, or other general-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. A general-purpose processor can be a microprocessor or any conventional processor.

[0157] The input unit 830 can be used to receive input numerical or character information, and to generate keyboard, mouse, joystick, optical, or trackball signal inputs related to user settings and function control. Specifically, the input unit 830 may include a touch-sensitive surface 831 and other input devices 832. Specifically, the touch-sensitive surface 831 may include, but is not limited to, a touchpad or a touch screen, and other input devices 832 may include, but are not limited to, one or more of the following: a physical keyboard, function keys (such as volume control buttons, power buttons, etc.), a trackball, a mouse, and a joystick.

[0158] The display unit 840 can be used to display information input by the user or information provided to the user, as well as various graphical user interfaces of electronic devices. These graphical user interfaces can be composed of graphics, text, icons, videos, and any combination thereof. The display unit 840 may include a display panel 841, which may optionally be configured as a liquid crystal display (LCD), an organic light-emitting diode (OLED), or the like.

[0159] The RF circuit 850 can be used for receiving and transmitting signals during information transmission or calls. Specifically, it receives downlink information from the base station and hands it over to one or more processors 820 for processing; additionally, it transmits uplink data to the base station. Typically, the RF circuit 850 includes, but is not limited to, an antenna, at least one amplifier, a tuner, one or more oscillators, a Subscriber Identity Module (SIM) card, a transceiver, a coupler, a low-noise amplifier (LNA), a duplexer, etc. Furthermore, the RF circuit 850 can also communicate wirelessly with networks and other devices. The wireless communication can use any communication standard or protocol, including but not limited to Global System for Mobile Communications (GSM), General Packet Radio Service (GPRS), Code Division Multiple Access (CDMA), Wideband Code Division Multiple Access (WCDMA), Long Term Evolution (LTE), email, Short Messaging Service (SMS), etc.

[0160] WiFi is a short-range wireless transmission technology. Electronic device 800, through WiFi module 860, can help users send and receive emails, browse web pages, and access streaming media, providing users with wireless broadband internet access. Although Figure 8 WiFi module 860 is shown, but it is understood that it is not a necessary component of electronic device 800 and can be omitted as needed without changing the nature of the invention.

[0161] The electronic device 800 also includes a power supply 870 (such as a battery) to power various components. Preferably, the power supply can be logically connected to the processor 820 through a power management system, thereby enabling functions such as charging, discharging, and power consumption management through the power management system. The power supply 870 may also include one or more DC or AC power supplies, recharging systems, power fault detection circuits, power converters or inverters, power status indicators, and other arbitrary components.

[0162] It should be noted that, although not shown, the electronic device 800 may also include a Bluetooth module, etc., which will not be described in detail here.

[0163] An embodiment of the present invention also provides a computer-readable storage medium, which can be disposed in an electronic device to store at least one instruction or at least one program related to implementing a vascular pressure differential analysis method or a microcirculation resistance analysis method. The at least one instruction or the at least one program is loaded and executed by the processor to implement the vascular pressure differential analysis method or the microcirculation resistance analysis method provided in the above-described method embodiment.

[0164] Optionally, in embodiments of the present invention, the storage medium may include, but is not limited to, various media capable of storing program code, such as USB flash drives, read-only memory (ROM), random access memory (RAM), portable hard drives, magnetic disks, or optical disks.

[0165] One embodiment of the present invention also provides a computer program product or computer program, which includes computer instructions stored in a computer-readable storage medium. A processor of a computer device reads the computer instructions from the computer-readable storage medium and executes the computer instructions, causing the computer device to perform the vascular pressure differential analysis method or microcirculation resistance analysis method provided in the various optional embodiments described above.

[0166] It should be noted that the order of the above embodiments of the present invention is merely for descriptive purposes and does not represent the superiority or inferiority of the embodiments. Furthermore, specific embodiments have been described above. Other embodiments are within the scope of the appended claims. In some cases, the actions or steps described in the claims can be performed in a different order than that shown in the embodiments and still achieve the desired result. Additionally, the processes depicted in the drawings do not necessarily require a specific or sequential order to achieve the desired result. In some embodiments, multitasking and parallel processing are also possible or may be advantageous.

[0167] The various embodiments in this specification are described in a progressive manner. Similar or identical parts between embodiments can be referred to mutually. Each embodiment focuses on describing the differences from other embodiments. In particular, the apparatus embodiments are basically similar to the method embodiments, so the description is relatively simple; relevant parts can be referred to the descriptions of the method embodiments.

[0168] Those skilled in the art will understand that all or part of the steps of the above embodiments can be implemented by hardware or by a program instructing related hardware. The program can be stored in a computer-readable storage medium, such as a read-only memory, a disk, or an optical disk.

[0169] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A method for analyzing differential blood pressure, characterized in that, include: Obtain blood flow velocity distribution data for at least one cross-section of the blood vessel segment to be detected; Based on a preset pressure difference model, the pressure difference per unit length corresponding to each of the blood vessel cross sections is calculated according to the blood flow velocity distribution data. The pressure difference per unit length within the blood vessel segment to be detected is numerically integrated to obtain the pressure difference of the blood vessel segment to be detected. Obtain blood flow velocity distribution data of the distal section of the blood vessel segment to be detected; calculate the distal blood flow rate of the blood vessel segment to be detected based on the blood flow velocity distribution data of the distal section, wherein the distal blood flow rate is the blood flow rate passing through the distal section per unit time; The pressure difference of the blood vessel segment to be detected is corrected based on the distal blood flow to obtain the corrected pressure difference.

2. The method according to claim 1, characterized in that, The acquisition of blood flow velocity distribution data for at least one cross-section of the blood vessel segment to be detected includes: Phase information from multiple scans at each of the aforementioned blood vessel cross sections was obtained; The phase difference between each two adjacent scans is determined based on the phase information of each two adjacent scans; The blood flow velocity distribution data of the blood vessel cross section is calculated based on the phase difference between each two adjacent scans.

3. The method according to claim 2, characterized in that, The phase information refers to the phase information of optical coherence tomography (OCT) signals or intravascular ultrasound signals.

4. The method according to claim 1, characterized in that, The step of numerically integrating the pressure difference per unit length within the tested blood vessel segment to obtain the pressure difference of the tested blood vessel segment includes: The pressure difference per unit length of the blood vessel segment to be tested is obtained by summing the cumulative pressure differences at each cross-section of the blood vessel segment to be tested.

5. The method according to claim 1, characterized in that, The calculation of the distal blood flow rate of the vessel segment to be detected based on the blood flow velocity distribution data of the distal section includes: Obtain an image of the vascular structure of the blood vessel segment to be detected; The structural image of the distal section of the blood vessel segment to be detected is determined based on the vascular structure image; The blood flow region of the distal section is determined based on the structural image of the distal section; Based on the blood flow region of the distal section and the blood flow velocity distribution data, the blood flow velocity is numerically integrated within the blood flow region of the distal section to obtain the distal blood flow rate.

6. A method for analyzing microcirculation resistance, characterized in that, The method includes: The pressure difference and proximal pressure value of the blood vessel segment to be detected are obtained, wherein the pressure difference is determined based on the blood vessel pressure difference analysis method as described in any one of claims 1 to 5; Obtain the distal blood flow of the blood vessel segment to be detected; The distal pressure value of the blood vessel segment to be tested is determined based on the pressure difference and the proximal pressure value. The microcirculatory resistance of the tested vascular segment is calculated based on the distal pressure value and the distal blood flow.

7. A vascular pressure differential analysis device, characterized in that, include: The blood flow velocity acquisition module is used to acquire blood flow velocity distribution data of at least one cross section of the blood vessel segment to be detected. The first pressure difference calculation module is used to calculate the pressure difference per unit length corresponding to each of the blood vessel cross sections based on the preset pressure difference model and the blood flow velocity distribution data. The second pressure difference calculation module is used to perform numerical integration of the pressure difference per unit length within the range of the blood vessel segment to be detected, so as to obtain the pressure difference of the blood vessel segment to be detected. The third pressure difference modification module is used to acquire blood flow velocity distribution data of the distal section of the blood vessel segment to be detected; calculate the distal blood flow rate of the blood vessel segment to be detected based on the blood flow velocity distribution data of the distal section, wherein the distal blood flow rate is the blood flow rate passing through the distal section per unit time; and modify the pressure difference of the blood vessel segment to be detected based on the distal blood flow rate to obtain the modified pressure difference.

8. A microcirculation resistance analysis device, characterized in that, include: The first acquisition module is used to acquire the pressure difference and proximal pressure value of the blood vessel segment to be detected, wherein the pressure difference is determined based on the blood vessel pressure difference analysis method as described in any one of claims 1 to 5. The second acquisition module is used to acquire the distal blood flow of the blood vessel segment to be detected; The distal pressure calculation module is used to determine the distal pressure value of the blood vessel segment to be detected based on the pressure difference and the proximal pressure value. The microcirculation resistance calculation module is used to calculate the microcirculation resistance of the blood vessel segment to be tested based on the distal pressure value and the distal blood flow.

9. An electronic device, characterized in that, The electronic device includes a processor and a memory, wherein the memory stores at least one instruction or at least one program, the at least one instruction or the at least one program being loaded and executed by the processor to implement the vascular pressure differential analysis method as described in any one of claims 1-5 or the microcirculation resistance analysis method as described in claim 6.

10. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores at least one instruction or at least one program, which is loaded and executed by a processor to implement the vascular pressure differential analysis method as described in any one of claims 1-5 or the microcirculation resistance analysis method as described in claim 6.

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