CN111462117A

CN111462117A - Data processing system based on blood vessel image and data processing method thereof

Info

Publication number: CN111462117A
Application number: CN202010424342.1A
Authority: CN
Inventors: 李连波
Original assignee: Insight Lifetech Co Ltd
Current assignee: Insight Lifetech Co Ltd
Priority date: 2020-05-19
Filing date: 2020-05-19
Publication date: 2020-07-28

Abstract

The present disclosure provides a data processing system based on blood vessel images, comprising: the device comprises an image acquisition module, an imaging module, a registration module and a calculation module. The image acquisition module is used for acquiring an image signal of a distance of a target blood vessel; the imaging module receives the image signals and acquires a plurality of blood vessel section images in the target blood vessel; the registration module registers the plurality of blood vessel section images based on the angiography image to obtain a whole blood vessel image; the calculation module obtains a target blood vessel image based on the whole blood vessel image and a preset curve, and calculates intravascular pressure at any position in the target blood vessel image according to a fluid mechanics principle. This enables more accurate intravascular pressure to be obtained.

Description

Data processing system based on blood vessel image and data processing method thereof

Technical Field

The present disclosure relates to a data processing system based on blood vessel images and a data processing method thereof.

Background

Coronary artery disease is currently one of the leading causes of death worldwide. Improving the ability to diagnose, monitor and treat coronary artery disease can reduce the number of coronary artery disease deaths to some extent.

Coronary stenosis, which is a common coronary artery disease, is usually determined morphologically based on angiographic images, and if the result shows that the lesion is severe, it is necessary to perform functional determination by further using Fractional Flow Reserve (FFR) or oscillometric pressure ratio (iFR). FFR or iFR is an index of blood pressure drop when measuring a vascular stenosis, that is, FFR or iFR is determined by the ratio of the pressure (Pd) on the distal side of the stenosis to the pressure (Pa) on the proximal side near the aortic port.

Currently, for FFR or iFR, a pressure guide wire is generally used clinically to measure intravascular pressure so as to obtain fractional flow reserve or a ratio of pressure without waveform phase, but since the pressure guide wire needs to be disposed in a blood vessel during measurement, the pressure guide wire affects blood flow so as to cause inaccurate measurement of intravascular pressure. Therefore, in order to overcome the above problems, in the prior art, an angiographic image is obtained by imaging a blood vessel with an X-ray machine, so that a three-dimensional structural image of the blood vessel is obtained based on the angiographic image, and then intravascular pressure of each part of the blood vessel is calculated using the principle of fluid mechanics and a fractional flow reserve is obtained.

However, the three-dimensional structural image obtained by the X-ray machine cannot obtain the specific conditions inside the blood vessel, so that the pressure of each part in the blood vessel obtained by using the three-dimensional structural image will be inaccurate, thereby affecting the evaluation of the medical staff on the conditions of the blood vessel.

Disclosure of Invention

The present disclosure has been made in view of the above-described state of the art, and an object thereof is to provide a data processing system based on a blood vessel image and a data processing method thereof, which can acquire a blood vessel pressure more accurately.

To this end, a first aspect of the present disclosure provides a blood vessel image-based data processing system, characterized by comprising: the image acquisition module comprises a catheter, a probe, a transmission shaft and a withdrawing mechanism, wherein the catheter, the probe and the transmission shaft are arranged in a target blood vessel, the withdrawing mechanism is arranged outside the body, the probe is connected with the transmission shaft and moves along with the transmission shaft, the probe and the transmission shaft are arranged in the catheter, the withdrawing mechanism is connected with the transmission shaft and controls the transmission shaft to move relative to the catheter, and the image acquisition module acquires an image signal of a distance of the target blood vessel by using the probe; the imaging module is connected with the image acquisition module, receives the image signals from the image acquisition module, and acquires a plurality of blood vessel section images in the target blood vessel based on the image signals; a registration module that registers the plurality of vessel section images based on an angiographic image of the target vessel to obtain a vessel whole-body image; and the calculation module is used for obtaining a target blood vessel image of the target blood vessel based on the whole blood vessel image and a preset curve, and calculating intravascular pressure at any position in the target blood vessel image according to the fluid mechanics principle, wherein the preset curve is a curve of the cross section area of the target blood vessel changing along the cardiac cycle, and the target blood vessel image is a three-dimensional blood vessel image of the target blood vessel at the end diastole of the cardiac cycle and along the distance in the length direction of the blood vessel.

In the disclosure, a plurality of blood vessel section images in a target blood vessel are obtained through an image acquisition module and an imaging module, then a registration module registers the plurality of blood vessel section images based on an angiogram to obtain a whole blood vessel image, a calculation module obtains the target blood vessel image based on the whole blood vessel image and a preset curve, and further calculates the intravascular pressure at any position in the target blood vessel image based on the fluid mechanics principle. More accurate intravascular pressure can thereby be obtained.

In the data processing system according to the first aspect of the present disclosure, optionally, the probe acquires an image signal by emitting an ultrasound signal and/or an optical signal. Thereby, an image signal can be acquired with the ultrasound signal and/or the light signal.

In the data processing system according to the first aspect of the present disclosure, optionally, the image signal acquired by the probe through the ultrasonic signal is transmitted to the imaging module through a connecting wire, the image signal acquired by the probe through the optical signal is transmitted to the imaging module through an optical fiber, and the connecting wire and the optical fiber are arranged along the transmission shaft. Therefore, the image signals acquired by the probe can be transmitted to the imaging module through the matched transmission medium.

In the data processing system according to the first aspect of the present disclosure, optionally, the probe simultaneously emits an ultrasound signal and an optical signal to obtain an ultrasound image signal and an optical image signal of a distance of the target blood vessel, the imaging module generates an ultrasound image in the target blood vessel based on the ultrasound image signal, generates an OCT image based on the optical image signal, and combines the ultrasound image and the OCT image to obtain a plurality of the blood vessel cross-sectional images. More accurate blood vessel sectional images can be obtained thereby.

In the data processing system according to the first aspect of the present disclosure, optionally, the calculation module calculates a hemodynamic index at a predetermined position within the target blood vessel based on an intravascular pressure in the target blood vessel image. This enables a hemodynamic index to be obtained.

In the data processing system according to the first aspect of the present disclosure, optionally, the probe emits an optical signal at a first frequency and receives an optical signal at a second frequency reflected by a blood vessel wall of the target blood vessel, and the data processing system further includes an analysis module that analyzes the first frequency and the second frequency by a brillouin scattering principle to obtain biomechanical information of a corresponding position of the target blood vessel. In this case, biomechanical information of the target vessel can be obtained, thereby enabling assessment of the target vessel and identification of potential lesions of the target vessel.

In the data processing system according to the first aspect of the present disclosure, optionally, the imaging module acquires a size of a cross-sectional area and an acquisition time of each blood vessel cross-sectional image, and the registration module performs registration with the angiography image based on the acquisition time of the blood vessel cross-sectional image. Thereby enabling registration of multiple vessel sectional images.

In the data processing system according to the first aspect of the present disclosure, optionally, the calculation module selects any position from the blood vessel whole image as a target position and obtains a first cross-sectional area of the target blood vessel at the target position and a corresponding target time period, the calculation module obtains a target ratio of a blood vessel cross-sectional area of the target blood vessel at the target time period to a blood vessel cross-sectional area at the end of the diastolic period based on the preset curve, and the calculation module obtains the target cross-sectional area of the target blood vessel at the target position when the target blood vessel is at the end of the diastolic period based on the target ratio and the first cross-sectional area. Thereby, the target cross-sectional area of the target blood vessel at the target position at the end of diastole can be obtained, and the subsequent obtaining of the target blood vessel image can be facilitated.

In the data processing system according to the first aspect of the present disclosure, optionally, the calculation module obtains a target cross-sectional area corresponding to each position in the target blood vessel based on the whole blood vessel image and the preset curve, so as to adjust the whole blood vessel image to obtain the target blood vessel image by using the target cross-sectional area corresponding to each position. Thereby enabling obtaining an image of the target blood vessel.

In the data processing system according to the first aspect of the present disclosure, optionally, the step of calculating the intravascular pressure by the calculation module according to a fluid mechanics principle specifically includes: the calculation module acquires intravascular pressure at any position in the target blood vessel image through a pressure initial value and a preset formula, wherein the pressure initial value is a pressure value when a preset position in the distance of the target blood vessel is located at the end of diastole, and the preset formula satisfies the following conditions:

where Δ P represents the pressure difference between the intravascular pressures at two locations in the target vessel, μ represents the dynamic viscosity coefficient, l represents the length of the vessel between the two locations, r represents the average radius of the cross-section of the vessel between the two locations, and F represents the blood flow rate in the target vessel. Intravascular pressures at various locations in the target vessel can thereby be obtained.

A second aspect of the present disclosure provides a blood vessel image-based data processing method, including: acquiring an angiography image of a target blood vessel and a plurality of blood vessel section images of the target blood vessel at a distance, registering the plurality of blood vessel section images based on the angiography image to acquire a whole blood vessel image, selecting any position as a target position based on the whole blood vessel image, acquiring a first cross-sectional area of the target blood vessel at the target position and a corresponding target period, acquiring a target ratio of the cross-sectional area of the target blood vessel at the target period to the cross-sectional area of the blood vessel at the end of diastole based on a preset curve, acquiring a target cross-sectional area of the target blood vessel at the target position and at the end of diastole based on the target ratio and the first cross-sectional area, acquiring target cross-sectional areas corresponding to all positions in the target blood vessel, and adjusting the whole blood vessel image to acquire the target blood vessel cross-sectional area corresponding to all positions to obtain the target blood vessel integral image And calculating intravascular pressure at any position in the target blood vessel image according to a fluid mechanics principle, wherein the preset curve is a curve of the cross-sectional area of the target blood vessel changing along with a cardiac cycle, and the target blood vessel image is a three-dimensional image of the blood vessel at the distance along the length direction of the blood vessel at the end diastole of the cardiac cycle of the target blood vessel.

In the disclosure, a blood vessel overall image is obtained by obtaining a contrast image of a target blood vessel and a plurality of blood vessel section images at a distance, the target blood vessel image is obtained according to the blood vessel overall image and a preset curve, and intravascular pressure at each position of the target blood vessel image is calculated according to a fluid mechanics principle.

In the data processing method according to the second aspect of the present disclosure, the step of calculating the intravascular pressure based on a fluid dynamics principle may specifically include: acquiring intravascular pressure at any position in the target blood vessel image through a pressure initial value and a preset formula, wherein the pressure initial value is a pressure value when a preset position in the distance of the target blood vessel is located at the end of diastole, and the preset formula satisfies the following conditions:

where Δ P represents the pressure difference between the intravascular pressures at two locations in the target blood vessel, μ represents the dynamic viscosity coefficient, and l representsFor the length of the vessel between the two locations, r is the average radius of the vessel cross-section between the two locations, and F is the blood flow in the target vessel. Intravascular pressure at any location in the target vessel can thereby be obtained.

In the data processing method according to the second aspect of the present disclosure, optionally, the preset position is a port at which blood flows into the target blood vessel. The preset position can be determined, and the intravascular pressure can be conveniently obtained subsequently.

In the data processing method according to the second aspect of the present disclosure, optionally, the data processing method further includes calculating a hemodynamic index at a predetermined position within the target blood vessel based on an intravascular pressure in the target blood vessel image. This enables a hemodynamic index to be obtained.

According to the present disclosure, a data processing system based on a blood vessel image and a data processing method thereof capable of acquiring intravascular pressure more accurately can be provided.

Drawings

Embodiments of the present disclosure will now be explained in further detail, by way of example only, with reference to the accompanying drawings, in which:

fig. 1 is a block diagram showing a configuration of a data processing system according to an embodiment of the present disclosure.

Fig. 2 is a schematic configuration diagram showing a data processing system according to an embodiment of the present disclosure.

Fig. 3 is a schematic view of an interventional body showing a catheter according to an embodiment of the present disclosure.

Fig. 4 is a sectional view showing the application of the data processing system according to the embodiment of the present disclosure to a blood vessel.

Fig. 5 is a schematic diagram illustrating a three-dimensional structure acquisition of a blood vessel according to an embodiment of the present disclosure.

Fig. 6 is a schematic view showing a blood vessel whole image acquisition according to the embodiment of the present disclosure.

Fig. 7 shows a flowchart of a blood vessel image-based data processing method according to an embodiment of the present disclosure.

Detailed Description

The present disclosure will be described in further detail below with reference to the accompanying drawings and specific embodiments. In the drawings, the same components or components having the same functions are denoted by the same reference numerals, and redundant description thereof will be omitted.

The present disclosure provides a data processing system based on blood vessel images and a data processing method thereof. According to the blood vessel monitoring method and the blood vessel monitoring device, more accurate intravascular pressure can be obtained, a hemodynamic index can be obtained based on the intravascular pressure, and the condition of the blood vessel (such as whether a stenosis exists or not) can be evaluated by the hemodynamic index.

The data processing system according to the embodiment of the present disclosure may acquire blood vessel information in a target blood vessel by using an interventional catheter technology (e.g., vascular ultrasound imaging, optical interference tomography, ultrasound and optical two-in-one catheter, etc.), so that a blood vessel image may be obtained, and then perform data processing based on the blood vessel image to obtain intravascular pressure. Wherein the target blood vessel may be a blood vessel selected for measurement by a medical practitioner.

Fig. 1 is a block diagram showing a configuration of a data processing system 10 according to an embodiment of the present disclosure. Fig. 2 is a schematic diagram showing the structure of data processing system 10 according to the embodiment of the present disclosure.

In some examples, as shown in fig. 1, data processing system 10 may include an image acquisition module 110, an imaging module 120, a registration module 130, and a calculation module 140.

In the example related to the present embodiment, the image acquisition module 110 may be an acquisition device for acquiring blood vessel information. The imaging module 120, the registration module 130, and the calculation module 140 may be configured in the host 20 so as to perform processing with the host 20 (see fig. 2). In some examples, host 20 may be connected to image acquisition module 110. For example, as shown in fig. 2, the host 20 may be connected to a retraction mechanism 114 (described later) in the image acquisition module 110.

In the data processing system 10 according to the example of the present embodiment, as shown in fig. 2, the image acquisition module 110 may be an acquisition device for acquiring blood vessel information.

In some examples, the image acquisition module 110 may include a catheter 111, a probe 112, a drive shaft 113, and a retraction mechanism 114. The image acquisition module 110 may acquire an image signal of a distance within a target vessel using the probe. In some examples, the imaging module 120 may be connected to the image acquisition module 110, may receive image signals from the image acquisition module 110, and may obtain a plurality of cross-sectional images of the blood vessel in the target blood vessel based on the image signals. In some examples, the registration module 130 may register the plurality of vessel cross-sectional images based on the angiographic image, and may obtain a vessel whole-body image. In some examples, the calculation module 140 may obtain a target blood vessel image based on the blood vessel whole image and a preset curve, and may calculate intravascular pressure at any position in the target blood vessel image according to a fluid mechanics principle, that is, intravascular pressure at any position in the target blood vessel may be obtained.

In the present disclosure, a plurality of blood vessel cross-sectional images in a target blood vessel may be obtained through the image acquisition module 110 and the imaging module 120, then the registration module 130 may perform registration on the plurality of blood vessel cross-sectional images based on an angiogram image to obtain a whole blood vessel image, the calculation module 140 may obtain the target blood vessel image based on the whole blood vessel image and a preset curve, and further may calculate intravascular pressure at any position in the target blood vessel image based on a fluid mechanics principle. More accurate intravascular pressure can thereby be obtained.

In some examples, as described above, data processing system 10 may include image acquisition module 110, as shown in fig. 1 and 2. The image acquisition module 110 may include a catheter 111, a probe 112, a drive shaft 113, and a retraction mechanism 114. However, the examples of the present disclosure are not limited thereto, and the image acquisition module 110 may be other acquisition devices capable of acquiring blood vessel information.

In some examples, the catheter 111 may have a proximal side 111a proximal to the retraction mechanism 114 and a distal side 111b distal to the retraction mechanism 114.

Fig. 3 is a schematic view showing an interventional human body of a catheter 111 according to an embodiment of the present disclosure. Fig. 4 is a cross-sectional view illustrating application of data processing system 10 to blood vessel 300 according to an embodiment of the present disclosure.

In some examples, the catheter 111, probe 112, and drive shaft 113 may be disposed within a target vessel when the data processing system 10 is in operation (see fig. 3 and 4). For example, as shown in fig. 3, during an interventional procedure, a medical professional may first puncture a patient (or patient) from a site (e.g., radial artery or femoral artery) and advance the guidewire 116 along the blood vessel to a location (e.g., a first preset location a) within the target blood vessel, and then advance the catheter 111 along the guidewire 116 such that the probe 112 in the catheter 111 is positioned at the location within the target blood vessel. Thereby enabling the image acquisition module 110 to measure and obtain blood vessel information (e.g., image signals) containing the location.

In some examples, as shown in fig. 2, the conduit 111 may be in the form of an elongated tube. The catheter 111 may have a lumen 1111. The inner diameter of the lumen 1111 may be no smaller than the outer diameter of the probe 112 and drive shaft 113. In this case, the probe 112 and the drive shaft 113 may be disposed in the lumen 1111 of the catheter 111.

In some examples, the cross-section of the conduit 111 may be circular in shape. Thereby, friction between the catheter 111 and the blood vessel can be minimized, thereby reducing the risk of injury to the blood vessel.

In some examples, the catheter 111 may be made of a material that has good biocompatibility, reliable flexibility, good corrosion resistance, and anti-thrombus properties. For example, it may be a polymer or composite material. In this case, the catheter 111 can be placed more safely in the blood vessel, and the occurrence of other adverse symptoms can be reduced. In some examples, the catheter 111 may be fabricated from a material that is transparent to ultrasound and/or light signals (described later) and has little effect. For example, if the probe 112 can emit an ultrasound signal to acquire vascular information, the catheter 111 can be made of a material with acoustic impedance and acoustic impedance of blood; if the probe 112 can emit optical signals to collect blood vessel information, the catheter 111 can be made of a material having optical impedance and optical impedance of blood.

In some examples, as shown in fig. 2 and 4, drive shaft 113 may be coupled to probe 112, and probe 112 may move (rotate or slide) with drive shaft 113. In some examples, the drive shaft 113 and the probe 112 may be disposed in the conduit 111 and may be movable relative to the conduit 111.

In some examples, as shown in fig. 2, an end of the drive shaft 113 distal to the probe 112 may be connected to a retraction mechanism 114 (described later). In this case, the retracting mechanism 114 can control the driving shaft 113 to retract and rotate, and the probe 112 can move along with the driving shaft 113, thereby obtaining blood vessel information (e.g., image signals) at a distance in the target blood vessel.

In some examples, the drive shaft 113 may be provided with an interface 1131 that connects with the retraction mechanism 114. In some examples, the interface 1131 coupled to the retraction mechanism 114 may be mechanically configured. For example, the mechanical structural interface may be snap-fit, screw-fit, socket-and-spigot, groove-and-socket, and the like.

In some examples, the drive shaft 113 may have an internal cavity. In some examples, a connection pathway 115 for transmitting vascular information acquired by the probe 112 may be disposed in the internal cavity.

In some examples, as described above, the image acquisition module 110 may include the probe 112 (see fig. 2 and 4). In some examples, the probe 112 may be used to acquire vessel information of a target vessel.

In some examples, the blood vessel information may be an image signal of image data of the target blood vessel. In other examples, the blood vessel information may also be a signal containing relevant data information of the target blood vessel, for example, a signal containing a blood vessel parameter of cross-sectional areas of a plurality of positions in a distance of the target blood vessel, and a corresponding acquisition time when the blood vessel parameter is acquired.

In some examples, the probe 112 may acquire image signals by emitting ultrasound signals and/or light signals. Thereby enabling acquisition of image signals using ultrasound signals and/or light signals. Examples of the present disclosure are not limited thereto, and in some examples, the probe 112 may acquire vessel information of the target vessel by other means.

In some examples, the probe 112 may include a first probe. In some examples, the first probe may acquire vessel information by transmitting ultrasound signals. Specifically, the first probe may transmit an ultrasound signal that passes through the catheter 111 to the vessel wall and is reflected by the vessel wall, and the first probe may receive the reflected ultrasound signal and convert it into an electrical signal (i.e., an ultrasound image signal) that may be transmitted to an extracorporeal device via the connection path 115. In some examples, the ultrasound image signal obtained by the first probe may be an image signal containing image data of the target blood vessel.

In some examples, the probe 112 may include a second probe. In some examples, the first probe may acquire vessel information by emitting an optical signal (e.g., light in the near-infrared). Specifically, the second probe may emit an optical signal that is transmitted through the catheter 111 to the vessel wall and reflected by the vessel wall, and the second probe may receive the reflected optical signal (i.e., an optical image signal) and transmit it to a device outside the body through the connection path 115. In some examples, the light image signal obtained by the second probe may be an image signal containing image data of the target blood vessel.

In some examples, the probe 112 may include a first probe and a second probe. In this case, the probe 112 may emit an ultrasound signal and/or an optical signal to obtain an ultrasound image signal and an optical image signal, respectively, of a distance of the target blood vessel. In some examples, the first probe and the second probe may be located in the same component. In other examples, a second probe may be disposed in the first probe, the first probe may be provided with a window that mates with the second probe, and the second probe may emit optical signals from the window to acquire vascular information.

In some examples, the probe 112 may record acquisition times at which vessel information for corresponding locations of the target vessel is acquired. Thereby facilitating subsequent registration of data (e.g., vessel parameters or image data) included in the vessel information.

In some examples, the vascular information acquired by the probe 112 may be transmitted to a device outside the body (e.g., the retraction mechanism 114 or the imaging module 120) via the connection pathway 115. In some examples, the connection pathway 115 may include a connecting wire and/or an optical fiber. Specifically, the blood vessel information acquired by the probe 112 through the ultrasonic signal may be transmitted to an external device through a connecting wire, and the blood vessel information acquired by the probe 112 through the optical signal may be transmitted to the external device through an optical fiber. The vessel information acquired by the probe 112 can thus be transmitted to an extracorporeal device via a suitable transmission medium.

In some examples, the connection passage 115 may be disposed along the drive shaft 113. In some examples, the connection passage 115 may be disposed in an internal cavity of the drive shaft 113. But examples of the present disclosure are not limited thereto, and the connection passage 115 may be disposed on the outer wall along the length direction of the drive shaft 113.

In some examples, as described above, the image acquisition module 110 may include the retraction mechanism 114 (see fig. 2). In some examples, the retraction mechanism 114 may be disposed outside of the body.

In some examples, the retraction mechanism 114 may be coupled to the drive shaft 113. Specifically, the retraction mechanism 114 may have a port that mates with the interface 1131 of the drive shaft 113. The retraction mechanism 114 may be connected to the drive shaft 113 through a port. In this case, the withdrawal mechanism 114 may control the movement of the drive shaft relative to the target vessel.

In some examples, the retraction mechanism 114 may be provided with a signal receiving module (not shown). In some examples, the signal receiving module may be connected with the connection path 115. The signal receiving module may receive a signal containing blood vessel information.

In some examples, the signal receiving module may pre-process the received signal and transmit to the imaging module 120, for example, may de-noise the received electrical signal or convert the received optical image signal into a second electrical signal. In other examples, the signal receiving module may transmit the received signal to the imaging module 120.

In some examples, while data processing system 10 is in operation, image acquisition module 110 may acquire vessel information for a distance within a target vessel. Specifically, as shown in fig. 4, the target vessel may be a vessel 300. A first preset position a and a second preset position B may be provided in the blood vessel 300. In operation of the data processing system 10, the probe 112 may be disposed at a first predetermined position a, and the probe 112 may be retracted and stopped at a second predetermined position B by the retraction mechanism 114 controlling the retraction and rotation of the drive shaft 113 relative to the blood vessel 300. In this case, the image acquisition module 110 can be caused to acquire blood vessel information at a distance (e.g., a first preset position a to a second preset position B) in the target blood vessel. In some examples, the first preset position a and the second preset position B may be any position of the target blood vessel. Wherein the second preset position B may be closer to the port where blood flow flows into the target vessel than the first preset position a.

In some examples, the distal side 111b of the catheter 111 may be provided with a visualization ring, or a visualization ring may be provided on the probe 112 or on the drive shaft 113 near the probe 112. In this case, the position of the catheter 111 or the probe 112 in the blood vessel can be determined using X-ray radiography.

In some examples, data processing system 10 may include a control module (not shown). In some examples, the control module may be connected with the retraction mechanism 114. In some examples, the control module may be used to adjust the retraction mechanism 114 to control the retraction speed and rotational speed of the drive shaft 113. For example, the control module may reduce the withdrawal speed of the drive shaft 113, thereby enabling more detailed vessel information to be obtained.

In some examples, if the probe 112 acquires an image signal by emitting an ultrasound signal, the control module may control the frequency of the ultrasound signal emitted by the probe 112. In some examples, if the probe 112 acquires image signals by emitting optical signals, the control module may control the frequency of the optical signals emitted by the probe 112.

In some examples, the control module may be disposed in the host 20. As described above, the control module may be coupled to the retraction mechanism 114. In this case, the host 20 may be connected to the retraction mechanism 114.

In some examples, as described above, data processing system 10 may include imaging module 120 (see fig. 1).

In some examples, the imaging module 120 may be connected with the image acquisition module 110. For example, the imaging module 120 may be coupled to the retraction mechanism 114.

In some examples, the imaging module 120 may receive the vessel information from the image acquisition module 110, and the imaging module 120 may process the obtained vessel information.

In some examples, if the blood vessel information is an image signal containing image data, the imaging module 120 may obtain a plurality of blood vessel cross-sectional images within the target blood vessel based on the blood vessel information (see fig. 6(a) and 6 (b)). That is, the imaging module 120 may receive the image signal from the image acquisition module 110 and obtain a plurality of cross-sectional images of the blood vessel in the target blood vessel based on the image signal.

In some examples, the imaging module 120 may obtain information such as the size of the cross-sectional area and the acquisition time of each blood vessel cross-sectional image. In some examples, the registration module 130 may register the plurality of vessel section images using acquisition times of the angiographic image and the respective vessel section images (described in detail later). Thereby enabling registration of multiple vessel sectional images.

In some examples, the vessel section image may be a cross-sectional image along a vessel width direction (or a radial direction). In some examples, the vessel section image may be an oblique section image located between a width direction (or radial direction) and a length direction (or axial direction). In some examples, the angle between the cross-sectional direction and the length direction of the blood vessel cross-section in the blood vessel cross-sectional image may be adjusted by adjusting the retraction speed of the drive shaft 113 or the frequency at which the probe 112 transmits the ultrasonic signal or the optical signal. In the example according to the present embodiment, the blood vessel sectional image obtained can be a cross-sectional image by reducing the retraction speed of the drive shaft 113.

Examples of the present disclosure are not limited thereto, and in some examples, the imaging module 120 may obtain blood vessel parameters of the target blood vessel using blood vessel information, for example, information such as a cross-sectional area of the blood vessel at each position of the measured target blood vessel may be obtained. In some examples, the imaging module 120 may also obtain information such as acquisition time corresponding to each blood vessel parameter. The subsequent acquisition of the positions of the target vessels respectively corresponding to the individual vessel parameters can thereby be facilitated.

In some examples, if the probe 112 simultaneously emits the ultrasound signal and the optical signal to obtain the ultrasound image signal and the optical image signal, the imaging module 120 may generate ultrasound images in a plurality of target vessels based on the ultrasound image signal, and the imaging module 120 may generate OCT images in a plurality of target vessels based on the optical image signal.

In some examples, the imaging module 120 may synthesize the ultrasound image with a corresponding OCT image to obtain a plurality of vessel cross-sectional images (not shown). Specifically, the imaging module 120 may sequentially use each OCT image as a reference image, and then combine the ultrasound image acquired at the same time as the reference image with the reference image, for example, to add effective information in the ultrasound image to the reference image. More effective and accurate blood vessel section images can be obtained.

Generally, optical signal imaging may have a higher resolution than ultrasound signal imaging, i.e., the optical signal may identify finer intravascular structural features; while the ultrasound image may have a deeper imaging depth in the width direction (radial direction) of the target blood vessel, the ultrasound signal imaging may have more effective information in the width direction (radial direction). For example, the valid information may be side branch information of the target vessel, or the like. In this case, by adding effective information contained in the ultrasound image to the OCT image, a more effective blood vessel sectional image can be obtained.

However, the examples of the present disclosure are not limited thereto, in other examples, if the probe 112 simultaneously transmits the ultrasound signal and the optical signal to obtain the ultrasound image signal and the optical image signal, the imaging module 120 or the image acquisition module 110 may fuse the acquired ultrasound image signal and the optical image signal to obtain a fusion signal, and the imaging module 120 may obtain a plurality of blood vessel section images according to the fusion signal.

Fig. 5 is a schematic diagram illustrating a three-dimensional structure acquisition of a blood vessel according to an embodiment of the present disclosure. Fig. 6 is a schematic view showing a blood vessel whole image acquisition according to the embodiment of the present disclosure. Fig. 5(a) and 5(b) may be angiographic images of the blood vessel 300 in fig. 4 at different angles, respectively, and fig. 5(c) is a schematic diagram of the three-dimensional structure of the blood vessel 300 in fig. 4 obtained based on fig. 5(a) and 5 (b). Fig. 6(a) and 6(b) are sectional images of the blood vessel 300 at two different positions, respectively, and fig. 6(c) is an overall image of the blood vessel 300 obtained based on a plurality of sectional images of the blood vessel.

In some examples, as described above, data processing system 10 may include registration module 130 (see fig. 1). In some examples, the registration module 130 may register the plurality of vessel cross-sectional images based on the angiographic image, and may obtain a vessel whole-body image (see fig. 6(c), which is described in detail later).

In some examples, the whole blood vessel image may be an image of the blood vessel from the location in the target blood vessel where the probe 112 started to be retracted to the location where the probe 112 was located when the retraction stopped. For example, as shown in fig. 6(c), the blood vessel whole image may be a blood vessel image of a first preset position a to a second preset position B in the blood vessel 300.

In some examples, if the imaging module 120 obtains a plurality of vessel cross-sectional images of the target vessel, the registration module 130 may register the plurality of vessel cross-sectional images based on the angiographic image of the target vessel and the acquisition time of each vessel cross-sectional image to obtain a vessel whole image of the target vessel.

In some examples, a cross-sectional image of the blood vessel corresponding to each position can be obtained from the whole image of the blood vessel. For example, as shown in fig. 6, the blood vessel sectional image at C in fig. 6(C) may correspond to fig. 6(a), and the blood vessel sectional image at D in fig. 6(C) may correspond to fig. 6 (b).

In some examples, a contrast agent contrast may be performed on a patient, two angiographic images of a target blood vessel at different angles are obtained by using an X-ray machine (see FIG. 5(a) and FIG. 5(b)), the registration module 130 may three-dimensionally model the target blood vessel by using the two angiographic images to obtain a three-dimensional structure of the target blood vessel (see FIG. 5(c)), the registration module 130 may determine a starting position of the retraction of the probe 112 in the three-dimensional structure (e.g., a corresponding first preset position A in FIG. 5(c)) and a retraction direction L, the registration module 130 may obtain a retraction speed of the retraction mechanism 113 and may obtain an acquisition time of each blood vessel section image.

In other examples, in operation of the data processing system 10, the X-ray machine may be used to obtain an initial path of the drive shaft 113 and the probe 112 in the target blood vessel, and then perform a contrast agent imaging on the patient, and adjust the angle of the X-ray machine to obtain an angiographic image of the target blood vessel, and the registration module 130 may obtain the three-dimensional structure of the target blood vessel by performing three-dimensional modeling based on the initial path of the drive shaft 113 and the probe 112 in the target blood vessel and the angiographic image. The registration module 130 may match the plurality of vessel cross-sectional images to the three-dimensional structure using the initial path of the drive shaft 113 and the probe 112 in the target vessel. In this case, the corresponding positions of the respective blood vessel sectional images in the three-dimensional structure can be obtained, whereby the three-dimensional structure can be adjusted to obtain the blood vessel overall image.

In some examples, the vessel ensemble image may be a three-dimensional acquired image obtained using a three-dimensional structure and a plurality of vessel section images. For example, the registration module 130 may adjust the three-dimensional structure of the target blood vessel based on the blood vessel parameters (e.g., cross-sectional area, etc.) included in the plurality of blood vessel section images, so as to obtain a blood vessel overall image. That is, the blood vessel overall image may be a three-dimensional image including blood vessel parameters of respective positions of a distance of the target blood vessel.

In some examples, the vessel ensemble image may also be a discrete image including an angiographic image and a vessel cross-sectional image matched to the angiographic image. Specifically, the patient may be subjected to contrast agent imaging, an angiographic image of the target blood vessel is obtained by using the X-ray machine, the registration module 130 may obtain the angiographic image of the target blood vessel, and may determine a corresponding position of a starting position (or "starting position") of retraction of the probe 112 in the angiographic image and a retraction direction of the probe 112 when the data processing system 10 is in operation, and then the registration module 130 may determine a position of each blood vessel section image in the angiographic image by obtaining a retraction speed of the retraction mechanism 114 and an acquisition time of each blood vessel section image, so that the position of each blood vessel section image in the angiographic image may be determined, and the angiographic image may be matched with each blood vessel section image. Thereby, a blood vessel whole image including an angiographic image and a blood vessel cross-sectional image matched with the angiographic image can be obtained. In other examples, the vessel ensemble image may also be a target contrast image obtained based on the angiographic image and the plurality of vessel parameters. In particular, the registration module 130 may obtain an angiographic image of the target vessel and may then determine the location of the respective vessel parameters in the angiographic image match, thereby matching the respective vessel parameters to the angiographic image. Thereby, an entire image of the blood vessel can be obtained.

Examples of the present disclosure are not limited thereto, and in some examples, the registration module 130 may match the plurality of vessel parameters or the plurality of vessel section images obtained by the imaging module 120 with the angiographic image, and may obtain vessel global information. The blood vessel overall information may include information such as a plurality of blood vessel parameters in a distance of the target blood vessel and blood vessel positions corresponding to the respective blood vessel parameters, for example, the blood vessel overall information may include information such as cross-sectional areas corresponding to respective positions in a distance of the target blood vessel. In some examples, the registration module 130 may match the plurality of vessel parameters or the plurality of vessel section images with the angiographic image using acquisition times of the angiographic image and the plurality of vessel parameters or the plurality of vessel section images to obtain vessel ensemble information. The specific matching process can be analogous to the above-mentioned acquisition process of the whole blood vessel image.

In some examples, data processing system 10 may include an analysis module (not shown). In some examples, the analysis module may be disposed in the host 20.

In some examples, the probe 112 may acquire the image signal by emitting an optical signal, and the probe 112 may emit an optical signal having a first frequency and receive an optical signal having a second frequency reflected off the vessel wall. The analysis module can analyze the first frequency and the second frequency through the Brillouin scattering principle to obtain biomechanical information of the corresponding position of the target blood vessel.

Specifically, the analysis module may obtain the first frequency, the second frequency, and obtain time information corresponding to the second frequency based on the image signal received by the imaging module 120. The analysis module may analyze the first frequency and the second frequency by the brillouin scattering principle to obtain biomechanical information, such as stiffness of the blood vessel. The analysis module may determine a corresponding position of the biomechanical information in the target blood vessel through the corresponding time information and the whole blood vessel information or the whole blood vessel image of the registration module 130, so as to determine a blood vessel state of the corresponding position, for example, whether plaque exists in the corresponding position or not through the biomechanical information. In this case, biomechanical information of the target vessel can be obtained, thereby enabling assessment of the target vessel, identification of potential lesions of the target vessel, and identification of potential lesions of the target vessel.

In some examples, as described above, data processing system 10 may include a calculation module 140 (see fig. 1). In some examples, the calculation module 140 may obtain a target blood vessel image based on the blood vessel whole image or the blood vessel whole information and a preset curve, and calculate intravascular pressure at any position in the target blood vessel image according to the fluid mechanics principle, that is, intravascular pressure at any position in the target blood vessel may be obtained.

In some examples, the preset curve may be a curve of the cross-sectional area of the target blood vessel as a function of the cardiac cycle. The cardiac cycle may include, among other things, systolic phases of systole and diastolic phases of diastole.

In other examples, the preset curve may also be a curve in which the ratio of the cross-sectional area of the target blood vessel at each phase of the cardiac cycle to the cross-sectional area of the target blood vessel at the end of the diastolic phase varies with the cardiac cycle.

In some examples, the preset curve may be obtained based on measurement experience and preset in the calculation module 140. In some examples, a common ratio (simply "ratio") of the cross-sectional area at each phase to the cross-sectional area at the end of diastole can be obtained by counting and analyzing the cross-sectional areas of the same blood vessel (e.g., a target blood vessel) corresponding to a plurality of patients and normal persons at each phase of the cardiac cycle, so that a curve of the cross-sectional area of the blood vessel as a function of the cardiac cycle can be obtained, or a curve of the cross-sectional area of the blood vessel as a function of the cross-sectional area at each phase to the cross-sectional area at the end of diastole can be obtained. In this case, a preset curve can be obtained, and the preset curve can reflect the change of the cross-sectional area of the corresponding target blood vessel. In some examples, the preset curves may be obtained with one or more factors defined, for example, preset curves corresponding to persons of different age groups, or preset curves corresponding to persons of different genders, respectively, may be obtained.

In some examples, as described above, the calculation module 140 may obtain the target blood vessel image based on the whole blood vessel image or the whole blood vessel information and the preset curve. In some examples, the target vessel image may be a three-dimensional image of the vessel at a distance along the length of the vessel at the end-diastolic phase of the cardiac cycle.

In some examples, the calculation module 140 may select any one of the positions from the blood vessel whole image or the blood vessel whole information as the target position, and may acquire a corresponding first cross-sectional area of the target blood vessel at the target position and a corresponding target period. In some examples, the target time period for which the target blood vessel corresponds at the target location may refer to a certain time period in the cardiac cycle in which the target location was located when the blood vessel information at the target location was acquired.

In some examples, the calculation module 140 may confirm the blood vessel whole image or the target period in the blood vessel whole information at the target position according to the acquisition time corresponding to the blood vessel information at the target position acquired by the image acquisition module 110 and an electrocardiogram. Specifically, when the image acquisition module 110 acquires the blood vessel information, the electrocardiograph of the patient may be measured at the same time by the electrocardiograph recorder, and the calculation module 140 may acquire the electrocardiograph and the acquisition time corresponding to the blood vessel information at the acquisition target position. In this case, a certain period of the acquisition time in the corresponding cardiac cycle in the electrocardiogram may be determined, thereby enabling confirmation of the target period at the target position in the whole blood vessel image or the whole blood vessel information.

In some examples, the calculation module 140 may obtain a target ratio of the cross-sectional area of the target blood vessel at the target time period to the cross-sectional area of the target blood vessel at the end-diastole based on the target time period corresponding to the target position and the preset curve, and may obtain the target cross-sectional area of the target blood vessel at the target position when at the end-diastole based on the target ratio and the first cross-sectional area. Thereby, the target cross-sectional area of the target blood vessel at the target position at the end of diastole can be obtained, and the subsequent obtaining of the target blood vessel image can be facilitated.

In some examples, the calculation module 140 may sequentially obtain the target cross-sectional areas corresponding to the respective positions in the blood vessel overall image based on the blood vessel overall image or the blood vessel overall information and a preset curve. In some examples, the calculation module 140 may adjust the blood vessel whole image to obtain the target blood vessel image by using the target cross-sectional area corresponding to each position. Thereby enabling obtaining an image of the target blood vessel.

In some examples, the calculation module 140 may calculate intravascular pressure corresponding to any location in the target vessel image based on fluid mechanics principles.

Specifically, the calculation module 140 may obtain the intravascular pressure at any position in the target blood vessel image through the initial pressure value and a preset formula. In some examples, the initial value of pressure may be a value of pressure at which a preset position in a distance of the target blood vessel is at end diastole. For example, the preset position may be a port where blood flow is flowing into the target blood vessel. In some examples, the preset formula may satisfy:

where Δ P is the pressure difference between the intravascular pressures at two locations in the target vessel, μ is the dynamic viscosity coefficient, l is the length of the vessel between the two locations, and r is the two locationsThe average radius of the vessel cross-section in between, F, is expressed as the blood flow in the target vessel. Intravascular pressure at any location in the target vessel can thereby be obtained.

However, the examples of the present disclosure are not limited to this, in some examples, the calculation module 140 may also sequentially obtain predetermined target cross-sectional areas (which may be similar to the above-mentioned target cross-sectional areas) corresponding to the respective positions based on the blood vessel whole image or the blood vessel whole information, and the preset curve, and the calculation module 140 may obtain intravascular pressures at the respective positions within a distance of the target blood vessel based on the flow dynamics principle and the predetermined target cross-sectional areas corresponding to the respective positions.

Generally speaking, the diagnosis and treatment of vascular lesions in the prior art requires multiple interventional procedures in a patient. For example, the functional judgment is usually performed by measuring the intravascular pressure by using a pressure guide wire to obtain the fractional flow reserve or the pressure ratio of the non-waveform phase, and if the functional judgment result is positive, an intraluminal imaging tool (such as vascular ultrasound imaging or optical interference tomography imaging) is used to image a portion with vascular lesions to determine the specific conditions of the vascular lesions, so as to guide and establish the treatment strategy before operation, guide the treatment during operation and evaluate the treatment effect after operation. In this case, diagnosis and treatment of vascular lesions require multiple interventional catheters, and effective integration of the results of the respective interventional diagnostic procedures is difficult to achieve. In contrast, in the example according to the present embodiment, the calculation module 140 may calculate the hemodynamic index at the predetermined position within the target blood vessel based on the intravascular pressure in the target blood vessel image. This enables a hemodynamic index to be obtained. For example, the calculation module 140 may calculate a pressure ratio between two locations in the target blood vessel based on the intravascular pressure in the target blood vessel image, and the pressure ratio may be used as a non-waveform pressure ratio corresponding to a blood vessel portion of the target blood vessel between the two locations. In this case, the calculation module 140 or the medical staff may compare the obtained pressure ratio with a preset threshold, so as to evaluate the blood vessel condition corresponding to the target blood vessel between the two positions, for example, as shown in fig. 4, a non-waveform pressure ratio corresponding to a blood vessel portion between two positions (a first preset position a to a second preset position B) in the blood vessel 300 may be obtained, a functional judgment may be performed on the portion, and if the functional judgment result is positive, a blood vessel lesion (e.g., stenosis 301) may be determined between the two positions of the blood vessel 300, and then a blood vessel section image corresponding to the blood vessel lesion portion may be obtained. In this case, it is possible to facilitate medical staff to confirm the details of the vascular disorder, thereby facilitating the subsequent treatment.

In some examples, the preset threshold may be obtained by collecting and processing pressure within the blood vessel of a person who is not suffering from a disease. In some examples, the preset threshold may be derived from past experience and set by the healthcare worker.

Hereinafter, a blood vessel image-based data processing method according to an example of the present embodiment will be described in detail with reference to fig. 7. Fig. 7 shows a flowchart of a blood vessel image-based data processing method according to an embodiment of the present disclosure.

The data processing method according to the example of the present embodiment may include: acquiring an angiographic image of a target blood vessel and a plurality of blood vessel sectional images of a distance of the target blood vessel (step S10); registering the plurality of blood vessel section images based on the angiography image to obtain a blood vessel whole image (step S20); selecting any position as a target position based on the blood vessel whole image, acquiring a first cross-sectional area of a target blood vessel at the target position and a corresponding target period, acquiring a target ratio of the blood vessel cross-sectional area of the target blood vessel at the target period to the blood vessel cross-sectional area at the end of diastole based on a preset curve, acquiring a target cross-sectional area of the target blood vessel at the target position and at the end of diastole based on the target ratio and the first cross-sectional area, thereby acquiring the target cross-sectional area corresponding to each position in the target blood vessel, and further adjusting the blood vessel whole image by using the target cross-sectional area corresponding to each position to acquire the target blood vessel image (step S30); the intravascular pressure at any position in the target blood vessel image is calculated based on the principle of fluid dynamics (step S40).

In the data processing method according to the present embodiment, the blood vessel whole image may be obtained by obtaining a contrast image of the target blood vessel and a plurality of blood vessel cross-sectional images at a distance, the target blood vessel image may be obtained from the blood vessel whole image and a preset curve, and the intravascular pressure at each position of the target blood vessel image may be calculated based on the principle of fluid mechanics.

In the present embodiment, the target blood vessel, the blood vessel section image, the angiographic image, the whole blood vessel image, the target cross-sectional area, the target blood vessel image, and the intravascular pressure may be acquired and processed in the data processing method by referring to the target blood vessel, the blood vessel section image, the angiographic image, the whole blood vessel image, the preset curve, the target cross-sectional area, the target blood vessel image, and the intravascular pressure.

In step S10, an angiographic image of the target blood vessel and a plurality of blood vessel cross-sectional images of the target blood vessel at a distance may be acquired as described above.

In some examples, a plurality of vessel cross-sectional images of a distance of a target vessel may be obtained using interventional catheter techniques. For example, multiple vessel cross-sectional images of the target vessel can be acquired using vascular ultrasound imaging (i.e., IVUS imaging) and/or optical interference tomography (i.e., OCT imaging). See in particular image acquisition module 110 and imaging module 120 described above.

In some examples, an angiographic image of the target vessel may be obtained using an X-ray machine and a contrast agent.

In step S20, the plurality of vessel cross-sectional images may be registered based on the angiographic image to obtain a vessel whole-body image, as described above. For example, a contrast agent contrast may be performed on a patient, two angiographic images of a target blood vessel at different angles may be obtained using an X-ray machine, a three-dimensional structure of the target blood vessel may be obtained by three-dimensionally modeling the target blood vessel using the two angiographic images, a start position (e.g., the first preset position a) of retraction of the probe 112 and a retraction direction may be determined in the three-dimensional structure, a retraction speed of the retraction mechanism 113 may be obtained, and an acquisition time of each blood vessel sectional image may be obtained. In this case, the corresponding positions of the respective blood vessel sectional images in the three-dimensional structure can be obtained, whereby a blood vessel whole image can be obtained. The specific process can be seen in the registration module 130 described above.

In step S30, as described above, any position may be selected as the target position based on the blood vessel whole image and the first cross-sectional area of the target blood vessel at the target position and the corresponding target period may be obtained, the target ratio of the blood vessel cross-sectional area of the target blood vessel at the target period to the blood vessel cross-sectional area at the end of the diastolic period may be obtained based on the preset curve, the target cross-sectional area of the target blood vessel at the target position at the end of the diastolic period may be obtained based on the target ratio and the first cross-sectional area, so that the target cross-sectional area corresponding to each position in the target blood vessel may be obtained, and the blood vessel whole image may be adjusted by using the target cross-sectional area corresponding to each position to. The specific process can be seen in the above calculation module 140.

In some examples, the preset curve may be a curve of the cross-sectional area of the target blood vessel as a function of the cardiac cycle. In other examples, the preset curve may also be a curve in which the ratio of the cross-sectional area of the target blood vessel at each phase of the cardiac cycle to the cross-sectional area of the target blood vessel at the end of the diastolic phase varies with the cardiac cycle.

In some examples, the target vessel image may be a three-dimensional image of the vessel at a distance along the length of the vessel at the end-diastolic phase of the cardiac cycle.

In step S40, as described above, the intravascular pressure at any position in the target blood vessel image can be calculated based on the principle of fluid mechanics. The specific process can be seen in the above calculation module 140.

In some examples, the intravascular pressure at any position in the target blood vessel image may be obtained by the initial pressure value and a preset formula. In some examples, the initial value of pressure may be a value of pressure at which a preset position in a distance of the target blood vessel is at end diastole. For example, the preset position may be a port where blood flow is flowing into the target blood vessel. In some examples, the target vessel may be a crownThe arteriole. The preset position may be an aortic port where blood flow from the aorta into the coronary arteries. The preset position can be determined, and the intravascular pressure can be conveniently obtained subsequently. In some examples, the preset formula may satisfy:

where Δ P represents the pressure difference between the intravascular pressures at two locations in the target vessel, μ represents the dynamic viscosity coefficient, l represents the length of the vessel between the two locations, r represents the average radius of the cross-section of the vessel between the two locations, and F represents the blood flow rate in the target vessel. Intravascular pressure at any location in the target vessel can thereby be obtained.

In some examples, a data processing method may include calculating a hemodynamic index for a predetermined location within the target vessel based on an intravascular pressure in the target vessel image. This enables a hemodynamic index to be obtained. For example, a pressure ratio between two locations in the target blood vessel may be calculated based on the intravascular pressure in the target blood vessel image, and the pressure ratio may be used as a waveform-free pressure ratio corresponding to a blood vessel portion of the target blood vessel between the two locations. In this case, the medical staff may compare the obtained pressure ratio with a preset threshold value, thereby being able to evaluate the condition of the target vessel corresponding to the location between the two locations (e.g., whether a stenotic lesion exists).

While the present disclosure has been described in detail in connection with the drawings and examples, it should be understood that the above description is not intended to limit the disclosure in any way. Those skilled in the art can make modifications and variations to the present disclosure as needed without departing from the true spirit and scope of the disclosure, which fall within the scope of the invention.

Claims

1. A data processing system based on blood vessel images is characterized in that,

the method comprises the following steps:

the image acquisition module comprises a catheter, a probe, a transmission shaft and a withdrawing mechanism, wherein the catheter, the probe and the transmission shaft are arranged in a target blood vessel, the withdrawing mechanism is arranged outside the body, the probe is connected with the transmission shaft and moves along with the transmission shaft, the probe and the transmission shaft are arranged in the catheter, the withdrawing mechanism is connected with the transmission shaft and controls the transmission shaft to move relative to the catheter, and the image acquisition module acquires an image signal of a distance of the target blood vessel by using the probe;

the imaging module is connected with the image acquisition module, receives the image signals from the image acquisition module, and acquires a plurality of blood vessel section images in the target blood vessel based on the image signals;

a registration module that registers the plurality of vessel section images based on an angiographic image of the target vessel to obtain a vessel whole-body image;

and the calculation module is used for obtaining a target blood vessel image of the target blood vessel based on the whole blood vessel image and a preset curve, and calculating intravascular pressure at any position in the target blood vessel image according to the fluid mechanics principle, wherein the preset curve is a curve of the cross section area of the target blood vessel changing along the cardiac cycle, and the target blood vessel image is a three-dimensional blood vessel image of the target blood vessel at the end diastole of the cardiac cycle and along the distance in the length direction of the blood vessel.

2. The data processing system of claim 1, wherein:

the probe acquires image signals by emitting ultrasound signals and/or light signals.

3. The data processing system of claim 2, wherein:

the image signal that the probe was gathered through ultrasonic signal transmits through connecting wire for imaging module, the image signal that the probe was gathered through optical signal transmits through optic fibre for imaging module, connecting wire with optic fibre is along the transmission shaft arranges.

4. The data processing system of claim 2, wherein:

the probe simultaneously emits an ultrasonic signal and an optical signal to obtain an ultrasonic image signal and an optical image signal of a distance of the target blood vessel, the imaging module generates an ultrasonic image in the target blood vessel based on the ultrasonic image signal, generates an OCT image based on the optical image signal, and synthesizes the ultrasonic image and the OCT image to obtain a plurality of blood vessel section images.

5. The data processing system of claim 1, wherein:

the calculation module calculates a hemodynamic index for a predetermined location within the target vessel based on the intravascular pressure in the target vessel image.

6. The data processing system of any of claims 1 to 5, wherein:

the probe emits an optical signal at a first frequency and receives an optical signal at a second frequency reflected by a vessel wall of the target vessel,

the data processing system further comprises an analysis module, and the analysis module analyzes the first frequency and the second frequency through the Brillouin scattering principle to obtain biomechanical information of the corresponding position of the target blood vessel.

7. The data processing system of claim 1, wherein:

the imaging module acquires the size of the cross section area and the acquisition time of each blood vessel section image, and the registration module performs registration with the angiography image based on the acquisition time of the blood vessel section image.

8. The data processing system of claim 1, wherein:

the calculation module selects any position from the whole blood vessel image as a target position and obtains a first cross-sectional area of the target blood vessel at the target position and a corresponding target period, the calculation module obtains a target ratio of the cross-sectional area of the target blood vessel at the target period to the cross-sectional area of the blood vessel at the end of the diastolic period based on the preset curve, and the calculation module obtains the target cross-sectional area of the target blood vessel at the target position when the target blood vessel is at the end of the diastolic period based on the target ratio and the first cross-sectional area.

9. The data processing system of claim 8, wherein:

the calculation module obtains target cross-sectional areas corresponding to all positions in the target blood vessel based on the whole blood vessel image and the preset curve, so that the whole blood vessel image is adjusted by using the target cross-sectional areas corresponding to all the positions to obtain the target blood vessel image.

10. The data processing system of claim 1, wherein:

the step of calculating the intravascular pressure by the calculation module according to the fluid mechanics principle specifically comprises: the calculation module acquires intravascular pressure at any position in the target blood vessel image through a pressure initial value and a preset formula, wherein the pressure initial value is a pressure value when a preset position in the distance of the target blood vessel is located at the end of diastole, and the preset formula satisfies the following conditions:

where Δ P is the pressure difference between the intravascular pressures at two locations in the target vessel, μ is the dynamic viscosity coefficient, l is the length of the vessel between the two locations, r is the average radius of the cross-section of the vessel between the two locations, and F is the average radius of the vessel within the target vesselThe blood flow rate.

11. A data processing method based on blood vessel images is characterized in that,

the method comprises the following steps:

acquiring an angiographic image of a target blood vessel and a plurality of blood vessel section images of a distance of the target blood vessel,

registering the plurality of vessel section images based on the angiographic image to obtain a vessel ensemble image,

selecting any position as a target position based on the blood vessel whole image, acquiring a first cross-sectional area of the target blood vessel at the target position and a corresponding target period, acquiring a target ratio of the blood vessel cross-sectional area of the target blood vessel in the target period to the blood vessel cross-sectional area at the end of the diastolic period based on a preset curve, acquiring a target cross-sectional area of the target blood vessel at the target position and at the end of the diastolic period based on the target ratio and the first cross-sectional area, thereby acquiring target cross-sectional areas corresponding to various positions in the target blood vessel, further adjusting the blood vessel whole image by using the target cross-sectional areas corresponding to the various positions to acquire a target blood vessel image, and calculating the intravascular pressure at any position in the target blood vessel image according to the fluid mechanics principle, wherein, the preset curve is a curve that the cross-sectional area of the target blood vessel changes along with the cardiac cycle, and the target blood vessel image is a three-dimensional image of the blood vessel at the end diastole of the cardiac cycle of the target blood vessel along the distance in the length direction of the blood vessel.

12. The data processing method of claim 11, wherein:

the step of calculating the intravascular pressure according to the fluid mechanics principle specifically comprises: acquiring intravascular pressure at any position in the target blood vessel image through a pressure initial value and a preset formula, wherein the pressure initial value is a pressure value when a preset position in the distance of the target blood vessel is located at the end of diastole, and the preset formula meets the requirement：

Where Δ P represents the pressure difference between the intravascular pressures at two locations in the target vessel, μ represents the dynamic viscosity coefficient, l represents the length of the vessel between the two locations, r represents the average radius of the cross-section of the vessel between the two locations, and F represents the blood flow rate in the target vessel.

13. The data processing method of claim 12, wherein:

the preset position is a port where blood flows into the target blood vessel.

14. The data processing method of claim 11, wherein:

the data processing method further includes calculating a hemodynamic index for a predetermined location within the target vessel based on the intravascular pressure in the target vessel image.