CN111863262A

CN111863262A - Simulation method, device and equipment

Info

Publication number: CN111863262A
Application number: CN202010732399.8A
Authority: CN
Inventors: 姚洋洋; 宋凌; 杨光明; 秦岚; 卢旺盛
Original assignee: Qianglian Zhichuang Beijing Technology Co ltd
Current assignee: Qianglian Zhichuang Beijing Technology Co ltd
Priority date: 2020-07-27
Filing date: 2020-07-27
Publication date: 2020-10-30
Anticipated expiration: 2040-07-27
Also published as: CN111863262B

Abstract

The embodiment of the specification discloses a simulation method, a simulation device and simulation equipment, and belongs to the technical field of medical images and computers. The method comprises the following steps: acquiring aneurysm parameters and parent artery parameters of the craniocerebral image data to be processed, wherein the central line of the parent artery is a uniform central line; modeling according to speed velocity, time delta t and increasing distance position based on the aneurysm parameters and the parent artery parameters to obtain a stent simulation surface of the stent to be intervened, wherein position + velocity delta t is reduced to 0 when a preset constraint condition is met; and simulating the stent to be intervened based on the stent simulation surface to obtain at least one simulation effect of woven mesh display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter.

Description

Simulation method, device and equipment

Technical Field

The present disclosure relates to the field of medical imaging and computer technologies, and in particular, to a simulation method, apparatus, and device.

Background

Intracranial aneurysm, also called cerebral hemangioma, is mostly abnormal bulging on the wall of intracranial arterial vessel, and is the first cause of subarachnoid hemorrhage, and in cerebrovascular accidents, it is second to cerebral thrombosis and hypertensive cerebral hemorrhage, and is located in the third place. Intracranial aneurysms are classified into non-ruptured aneurysms and ruptured aneurysms, wherein most of the intracranial aneurysms are non-ruptured aneurysms, but once ruptured, spontaneous subarachnoid space bleeding is triggered to become ruptured aneurysms, the lethal disability rate of which exceeds 50 percent, and the life of a patient is seriously threatened.

The blood flow guiding device is used as an epoch-making product for treating intracranial aneurysm, and is widely applied to the intracranial aneurysm with large, huge, medium and small size ranges. Currently, the blood flow guiding device, i.e. the dense mesh stent, includes PED (vascular embolization device), sfd (silk flow embolization device), FRED, Surpass, tubbridge, etc., wherein the typical representative is PED, which is a cobalt-chromium-nickel alloy stent system, and is a new intravascular embolization auxiliary device that is on the market in recent years. The occurrence of the method leads the traditional interventional operation treatment in the aneurysm sac to be developed into the reconstruction treatment of the parent artery, changes the blood flow direction entering the aneurysm by increasing the metal coverage rate and the mesh rate, thereby achieving the thorough and lasting aneurysm embolization effect and simultaneously restoring the integrity of the parent artery structure.

Therefore, the type selection of the interventional stent, the weaving effect and the adherence of the interventional stent after being implanted into the aneurysm and the like are important for the reconstruction treatment of the parent artery. However, the current simulation of the intracranial aneurysm interventional stent has the defects of poor simulation effect, low accuracy, long time consumed by simulation calculation and the like, and influences the application of the dense mesh stent in the treatment of the intracranial aneurysm, so a new simulation method is needed.

Disclosure of Invention

The embodiment of the specification provides a simulation method, a simulation device and simulation equipment, which are used for solving the following technical problems: the simulation of the intracranial aneurysm interventional stent has the defects of poor simulation effect, low accuracy, long time consumed by simulation calculation and the like, and influences the application of the dense mesh stent in the treatment of the intracranial aneurysm.

In order to solve the above technical problem, the embodiments of the present specification are implemented as follows:

an embodiment of the present specification provides a simulation method, including:

acquiring aneurysm parameters and parent artery parameters of the craniocerebral image data to be processed, wherein the central line of the parent artery is a uniform central line;

modeling according to speed velocity, time delta t and increasing distance position based on the aneurysm parameters and the parent artery parameters to obtain a stent simulation surface of the stent to be intervened, wherein position + velocity delta t is reduced to 0 when a preset constraint condition is met;

and simulating the stent to be intervened based on the stent simulation surface to obtain at least one simulation effect of woven mesh display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter.

Further, the modeling is performed according to the velocity, the time Δ t and the growth distance position based on the aneurysm parameter and the parent artery parameter to obtain a stent simulation surface of the stent to be inserted, and the method specifically includes:

obtaining parameters of the stent to be intervened;

and simulating the surface of the stent to be intervened by taking a point on the central line of the parent artery as a source point and taking the tangential direction of a normal vector as an initial direction according to the angle extension of an interval (180/number of stent braided wires), wherein the number of the stent braided wires is determined based on the parameters of the stent to be intervened.

Further, the preset constraint condition comprises one or more of expansion detection, growth detection, stretching detection, collision detection and plane detection.

Further, the expansion detection means that the speed is reduced to 0 when the growth distance of the stent to be inserted is greater than the diameter of the stent to be inserted and the maximum expansion coefficient, wherein the maximum expansion coefficient is determined by the performance and the material of the stent to be inserted.

Further, the growth detection means that a proximal end release point on a center line of the parent artery is used as a release starting point, a homogenized point on the center line of the parent artery is used as a scale along an initial direction, a point where any one scale is located is selected as a current point, N points before and after the current point on the center line of the parent artery are used as a group, when a total growth distance of the current point is greater than a first preset multiple of an average distance, the speed is reduced to 0, wherein the value of N is determined by the homogenization of the center line of the parent artery, and the average distance is the average distance of the group where the N points before and after the current point are located.

Further, if the scale value between the current point and the proximal release point is less than N, taking the specific scale of the current point on the centerline of the parent artery as a group;

and if the scale value between the current point and the proximal release point is more than or equal to N, taking N points before and after the current point on the central line of the parent artery as a group.

Further, the stretching detection means that when the total increasing distance of the current point is greater than a second preset multiple of the average distance in the current direction, the speed is decreased to 0, where the current direction is the direction in which the initial direction is located, and the average distance in the current direction is the distance along the current direction of the group in which the current point is located.

Further, the collision detection means that when a point in two directions of the current point touches a blood vessel wall, the speed is reduced to 0, where the two directions are a direction in which the initial direction is located and a direction opposite to the initial direction, respectively.

Further, the plane detection means calculating a distance between the current point and a plane where a front point and a rear point are located, and when the current point reaches the inside of the plane where the front point is located and reaches the outside of the plane where the rear point is located along the initial direction, the speed is reduced to 0, the front point is a point located in front of the current point along the initial direction, and the rear point is a point located behind the current point along the initial direction.

Further, the mesh grid display means that in the release region of the stent to be intervened, the source points respectively extend along the clockwise direction and the counterclockwise direction along the initial direction according to the angle extension of the interval (180/number of stent braided wires), and the intersection points with the stent simulation surface form a mesh grid for mesh grid display.

Further, the adherent display means that the distance between a point of the simulated surface and the blood vessel wall is calculated to be dis, and the pseudo-color display is according to rgb color mode and according to a formula r of 255 dis 2; g? 0.0:255 (1.0-dis) 0.5; b is 0; r > 255? 255: r; g > 255? And 255 g, calculating and displaying adherence.

Further, the length display means that the distance L between the current point and the next point on the central line of the parent artery is calculated from the proximal release point;

taking the radius of the current point and the next point to be added as a diameter D, and taking the current L and the D as parameters to calculate the actual release length of the blood flow guiding device as L_delta；

Cumulative calculation of L_deltaAnd L, when L_deltaWhen the length of the FD is equal, the accumulated L is the length of the FD after the FD is actually released, and the length is displayed.

An embodiment of the present specification further provides a simulation apparatus, including:

the acquisition module is used for acquiring aneurysm parameters and parent artery parameters of the craniocerebral image data to be processed, wherein the central line of the parent artery is a uniform central line;

the stent surface simulation module is used for modeling according to the velocity, the time delta t and the increasing distance position based on the aneurysm parameters and the parent artery parameters to obtain a stent simulation surface of the stent to be intervened, wherein the position + velocity delta t is reduced to 0 when a preset constraint condition is met;

and the support simulation module is used for simulating the support to be intervened based on the support simulation surface to obtain at least one simulation effect of woven mesh display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter.

obtaining parameters of the stent to be intervened;

An embodiment of the present specification further provides an electronic device, including:

at least one processor; and the number of the first and second groups,

a memory communicatively coupled to the at least one processor; wherein,

The method comprises the steps of obtaining aneurysm parameters and parent artery parameters of craniocerebral image data to be processed, wherein the central line of a parent artery is a uniform central line; modeling according to speed velocity, time delta t and increasing distance position based on the aneurysm parameters and the parent artery parameters to obtain a stent simulation surface of the stent to be intervened, wherein position + velocity delta t is reduced to 0 when a preset constraint condition is met; based on the support simulation surface, the support to be intervened is simulated, and at least one simulation effect of mesh grid display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter is obtained, so that the support to be intervened can be simulated, the implantation condition of the support is observed, the optimal intervention support is selected, and reference is provided for clinical application.

Drawings

In order to more clearly illustrate the embodiments of the present specification or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly introduced below, it is obvious that the drawings in the following description are only some embodiments described in the present specification, and for those skilled in the art, other drawings can be obtained according to the drawings without any creative effort.

Fig. 1 is a schematic diagram of a simulation method provided in an embodiment of the present disclosure;

FIG. 2 is a schematic flow chart illustrating the homogenization of the centerline of a parent artery according to an embodiment of the present disclosure;

FIG. 3 is a schematic diagram of a proximal release point and a distal release point provided by an embodiment of the present disclosure;

fig. 4 is a schematic view of a weaving process of a woven mesh provided in an embodiment of the present description;

fig. 5 is a schematic diagram of a simulation apparatus provided in an embodiment of the present disclosure.

Detailed Description

In order to make those skilled in the art better understand the technical solutions in the present specification, the technical solutions in the embodiments of the present specification will be clearly and completely described below with reference to the drawings in the embodiments of the present specification, and it is obvious that the described embodiments are only a part of the embodiments of the present application, and not all of the embodiments. All other embodiments, which can be obtained by a person skilled in the art without making any inventive step based on the embodiments of the present disclosure, shall fall within the scope of protection of the present application.

Fig. 1 is a schematic diagram of a simulation method provided in an embodiment of the present disclosure, where the simulation method includes:

step S101: and acquiring aneurysm parameters and parent artery parameters of the craniocerebral image data to be processed, wherein the central line of the parent artery is a uniform central line.

In the embodiment of the present specification, the craniocerebral image data to be processed is any one of CTA (CT angiography), MRA (magnetic resonance angiography), DSA (digital subtraction angiography); the craniocerebral image data to be processed can be two-dimensional image data or three-dimensional image data; the craniocerebral image data to be processed needs to be converted into a DICOM format so as to be convenient for subsequent processing.

In an embodiment of the present description, the aneurysm parameters comprise: the central point of the aneurysm neck and the length of the aneurysm neck;

the parent artery parameters include: the central line of the parent artery, the radius of a point on the central line of the parent artery, the proximal point of the parent artery and the distal point of the parent artery.

In the embodiment of the present specification, the acquisition of the aneurysm parameters and the parent artery parameters is to extract blood vessel data from image data to be processed by a threshold segmentation method, perform surface reconstruction on the extracted blood vessel data, further segment the aneurysm, and acquire the aneurysm parameters and the parent artery parameters. The specific method for obtaining the parameters of the aneurysm and the parameters of the parent artery does not constitute a limitation to the present application.

It should be noted that the centerline of the parent artery is a uniform centerline, the uniform centerline can be used as a scale for subsequently selecting a release point, and the subsequently selected release point is located on a corresponding scale on the uniform centerline.

To further understand the homogenization of the centerline of the parent artery, fig. 2 is a schematic flow chart of the homogenization of the centerline of the parent artery according to the embodiment of the present disclosure. The homogenization of the central line of the parent artery mainly comprises the following steps:

step S201: and screening out second centerline data from the acquired first centerline data of the parent artery, wherein the second centerline data are abnormal centerline data.

In the embodiment of the present specification, the method for screening the second centerline data is as follows: and screening abnormal central line data from the first central line data as second central line data based on the variance. In a specific implementation process, screening out second centerline data from the acquired first centerline data of the parent artery, specifically comprising: traversing each point on the first central line data, calculating a tangent plane of the blood vessel by taking the advancing direction of the current point as a normal vector, calculating the variance of the radius by taking the point of the central line as the center of a circle and the point of the tangent plane as the radius, and considering the current point as an abnormal point when the variance is greater than a preset value. In a specific implementation, the preset value may be 0.5. It should be noted in particular that the advancement direction is the direction along the direction of the parent artery, i.e. from the proximal release point to the distal release point.

Step S203: and performing interpolation processing on the second centerline data, and correcting the second centerline data to obtain third centerline data.

In an embodiment of this specification, the obtaining of the third centerline data specifically includes: and performing interpolation processing on normal points before and after the abnormal point in the second centerline data along the advancing direction, so as to correct the second centerline data and obtain third centerline data. In the specific implementation process, the positions of the abnormal points and the radii corresponding to the abnormal points in the second centerline data need to be corrected. The radius corresponding to the abnormal point is obtained by interpolation of the radius or diameter of the normal point before and after the abnormal point, and the correction of the position of the abnormal point is obtained by interpolation of the position of the normal point before and after the abnormal point.

Step S205: and carrying out homogenization treatment on the third centerline data to obtain fourth centerline data.

The third centerline data obtained through the calibration process in the foregoing step further needs to be subjected to a homogenization process. Specifically, the data of the fourth center line is obtained by homogenizing every two points on the third center line in steps of fixed values. In practice, the step size for the fixed value is preferably 0.01.

Step S207: and diluting the fourth centerline data to obtain fifth centerline data.

In order to use the centerline data of the parent artery as a scale for the subsequent stent surface simulation during the subsequent treatment process, the fourth centerline data obtained in step S205 needs to be further diluted. In a specific implementation process, the fourth centerline data is diluted by N to obtain fifth centerline data. In one embodiment of the present description, N is preferably 5. It should be noted that N of 5 is merely an example of the present specification, and does not specifically limit the present application.

Step S209: and performing smoothing processing on the fifth central line data to obtain uniform central line data.

In the embodiments of the present disclosure, the smoothing process may use a Sinc smoothing function, or may use other smoothing processes, and the specific manner of the smoothing process does not limit the present disclosure.

By adopting the method for uniformizing the central line of the parent artery, provided by the embodiment of the specification, abnormal points on the central line of the parent artery can be eliminated, and the normalized and diluted central line data can be used as a data scale for subsequent research.

The optimized central line data of the parent artery is further used for correcting the radius/diameter of the parent artery.

Step S211: and acquiring the slope of radius change based on the optimized central line data of the parent artery and the central line data of the parent artery, and correcting the radius of the parent artery to obtain the corrected radius.

In the embodiment of the present specification, the slope of the change in radius is (radius of the current point-radius of the previous point)/radius of the previous point.

In the embodiment of the present specification, the corrected radius is obtained based on the loop judgment. Specifically, the loop ends when the slope of the radius change is >0.1, and the corrected radius is (radius of the current point + radius of the previous point)/2.

In one embodiment of the present disclosure, the radius of each point on the centerline is defined as the selected point P on the centerline and its corresponding maximum radius P1, and the perpendicular line perpendicular to the vector P1P is defined as the diameter of each point on the centerline.

Step S103: and modeling according to the velocity, the time delta t and the increasing distance position based on the aneurysm parameters and the parent artery parameters to obtain a stent simulation surface of the stent to be intervened, wherein the position + velocity delta t is 0 when a preset constraint condition is met.

In an embodiment of the present specification, the obtaining a stent simulation surface of a stent to be inserted based on the aneurysm parameter and the parent artery parameter by modeling according to a velocity, a time Δ t, and a growth distance position specifically includes:

obtaining parameters of the stent to be intervened;

and simulating the surface of the stent to be intervened by taking a point on the central line of the parent artery as a source point and taking the tangential direction of a normal vector as an initial direction according to the angle extension of an interval (180/number of stent braided wires), wherein the number of the stent braided wires is determined based on the parameters of the stent to be intervened. In one embodiment of the present description, the number of stent braided wires is 48.

In the embodiments of the present specification, the tangential direction of the normal vector is determined with the tangential direction of the normal vector taken in the distal direction with the proximal end as a starting point.

It should be noted that the stents to be introduced are all stents that can be used in blood flow guiding devices. The parameters of the stent to be intervened are determined based on the model of the stent to be intervened, the model of the stent to be intervened can be selected manually, and the parameters can be automatically matched from a consumable database based on the aneurysm parameters and the parent artery parameters. In a specific embodiment, the consumable database contains data related to the major stents, and can be updated according to the specific models of stents on the market. The specific configuration of the consumable database does not constitute a limitation of the present application.

In the embodiment of the specification, the stent simulation surface of the stent to be intervened is obtained by taking the proximal release point of the parent artery as the release starting point and releasing along the proximal release point to the distal release point, so as to simulate the release effect of different points.

FIG. 3 is a schematic diagram of a proximal release point and a distal release point provided in an embodiment of the present disclosure, in which one end of the centerline of the parent artery segment that is far from the heart is taken as the distal end, and one end that is near to the heart is taken as the proximal end. And (5) starting from the acquired tumor neck central point, and taking the tumor neck radius as the distance to acquire a tumor neck point. Further, a release point of the stent to be intervened is selected from the tumor neck point. In a specific embodiment, the release point of the stent to be introduced is located 5-12mm, preferably 8mm, from the tumor neck point. Wherein, the release point far away from the far end is a far-end release point, and the release point far away from the near end is a near-end release point.

In the embodiment of the present disclosure, the preset constraint condition includes one or more of inflation detection, growth detection, stretch detection, collision detection, and plane detection.

In the embodiment of the present disclosure, the expansion detection means that the speed is reduced to 0 when the stent to be inserted is increased by a distance greater than the diameter of the stent to be inserted and the maximum expansion coefficient, where the maximum expansion coefficient is determined by the performance and material of the stent to be inserted. In one particular embodiment of the present description, the maximum expansion coefficient is preferably 1.1.

In an embodiment of the present specification, the growth detection means that a proximal end release point on a centerline of the parent artery is used as a release starting point, a uniform point on the centerline of the parent artery is used as a scale along an initial direction, a point where any one scale is located is selected as a current point, N points before and after the current point on the centerline of the parent artery are used as a group, and when a total growth distance of the current point is greater than a first preset multiple of an average distance, the speed is reduced to 0, where a numerical value of N is determined by the uniformity of the centerline of the parent artery, and the average distance is an average distance of the groups where N points before and after the current point are located.

If the scale value between the current point and the proximal release point is less than N, taking the specific scale of the current point on the central line of the parent artery as a group;

Continuing to continue the previous example, in the process of homogenization treatment of the central line of the parent artery, diluting by taking 5 as a unit, in the process of growth detection, N is 5, the growth detection refers to taking a proximal release point on the central line of the parent artery as a release starting point, taking a homogenized point on the central line of the parent artery as a scale along the initial direction, selecting a point where any one scale is located as a current point, taking 5 points in front of and behind the current point on the central line of the parent artery as a group, and when the total distance of growth of the current point is greater than a first preset multiple of the average distance, reducing the speed to 0. In the embodiments of the present specification, the first preset multiple is preferably 1.1.

If the scale value between the current point and the proximal release point is less than 5, for example, 3, taking 3 points before and after the current point on the centerline of the parent artery as a group;

and if the scale value between the current point and the proximal release point is more than or equal to 5, taking 5 points in front of and behind the current point on the central line of the parent artery as a group.

In this embodiment of the present specification, the stretch detection means that when a total distance of an increase of the current point is greater than a second preset multiple of an average distance in a current direction, the speed is decreased to 0, where the current direction is a direction in which the initial direction is located, and the average distance in the current direction is a distance along the current direction of a group in which the current point is located. In the embodiments of the present specification, the second preset multiple is preferably 1.1.

In the embodiment of the present disclosure, the collision detection means that when a point in two directions of the current point touches a blood vessel wall, the speed is reduced to 0, where the two directions are respectively a direction in which the initial direction is located and a direction opposite to the initial direction.

In this embodiment of the present specification, the plane detection means calculating a distance between the current point and a plane where a front point and a rear point are located, where when the current point reaches an inside of the plane where the front point is located and reaches an outside of the plane where the rear point is located along the initial direction, the speed is reduced to 0, the front point is a point located in front of the current point along the initial direction, and the rear point is a point located behind the current point along the initial direction.

In the embodiment of the present specification, the judgment of reaching the inside or the outside of the plane is made by calculating the distance from a point to the plane by a plane equation.

Step S105: and simulating the stent to be intervened based on the stent simulation surface to obtain at least one simulation effect of woven mesh display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter.

In the embodiment of the present specification, the mesh-grid display refers to that in the release region of the stent to be inserted, the source point respectively extends along the clockwise direction and the counterclockwise direction, along the initial direction according to the angle of the interval (180/number of stent-weaving lines), and forms a mesh-grid with the intersection point of the stent simulation surface for mesh-grid display.

To further understand the method for displaying the woven mesh, fig. 4 is a schematic diagram of the weaving process of the woven mesh provided in the embodiments of the present specification. The following description will be made in detail with reference to a drawing process of a specific woven mesh.

And (3) calculating the intersection point of each point on the centerline of the parent artery and the vessel wall by taking the point on the centerline of the parent artery as a source point, as shown in fig. 4a, A, B points and the like, wherein the points are the intersection points of the centerline of the parent artery and the vessel wall.

The points of the cross-section shown in figure 4a on the centerline of the parent artery are spread out to form a rectangular matrix of points as shown in figure 4 b.

Further, connecting matrix points of the matrix shown in fig. 4b in a clockwise direction, connecting the point of the nth column of each M row with the point of N +1 of the M +1 row, and so on to obtain the graph shown in fig. 4 c;

further, in the diagram shown in fig. 4c, the matrix points are connected in the counterclockwise direction, the nth column point of each M row is connected with the nth-1 column point of the M-1 row, and so on, and finally the woven mesh is formed, as shown in fig. 4 d.

It should be particularly noted that, in order to satisfy the simulation of knitting of stents to be inserted of different blood flow guiding devices, the embodiments of the present specification further provide a knitting simulation method, so as to implement the difference of mesh size and coverage rate of the simulation of knitting of stents to be inserted according to the diameters of wires of different stents to be inserted. In the specific implementation process, the diameter of the metal wire of the stent to be intervened is set according to the model of the stent to be intervened, and the mesh grid with different mesh sizes and coverage rates is woven according to the diameter of the metal wire of the stent to be intervened.

Continuing with the previous example, the matrix shown in fig. 4b is obtained, and the woven mesh with different mesh sizes and coverage rates is woven according to the preset diameter of the metal wire of the stent to be inserted. Fig. 4e shows the knitting effect of another mesh-knitting net with different mesh size and coverage. From the comparison between fig. 4d and fig. 4e, it can be seen that the weaving effect of the two woven nets is different, and the mesh size and the coverage rate of the two woven nets are obviously different. The smaller the mesh of fig. 4d, i.e. the denser the mesh, the greater the metal coverage.

In the embodiments of the present specification, the smaller the mesh, or the denser the mesh, the greater the metal coverage. The metal coverage rate is used for simulating the real effect of the stent to be intervened after being implanted, provides objective basis for the selection of the stent to be intervened, also provides reference basis for subsequent clinic, such as the size of a blood sinus and the like, and has important clinical reference significance.

In the embodiment of the present specification, the adherent display means that the distance between the point of the simulated surface and the blood vessel wall is calculated to be dis, and the pseudo-color display is according to rgb color mode and according to the formula r 255 dis 2; g? 0.0:255 (1.0-dis) 0.5; b is 0; r > 255? 255: r; g > 255? And 255 g, calculating and displaying adherence.

It should be particularly noted that, in the calculation of the adherence display, a three-eye operator is used, and for the conditional expression b? And x is y, firstly calculating the condition b, and then judging. If the value of b is true, calculating the value of x, and the operation result is the value of x; otherwise, calculating the value of y, and obtaining the operation result as the value of y. A conditional expression never computes both x and y. Conditional operators are right-binding, that is, grouping computations from right to left. For example, a? b: c? d: e will be pressed as a? b (c.

< expression 1 >? < expression 2> expression 3 >; "? The meaning of the operator is: firstly, the value of the expression 1 is solved, if the value is true, the expression 2 is executed, and the result of the expression 2 is returned; if the value of expression 1 is false, expression 3 is executed and the result of expression 3 is returned.

Can be understood as a condition? Result 1? Number is a format requirement. It can also be understood whether a condition is satisfied, which is result 1, otherwise result 2.

In the embodiment of the specification, the length display means that the distance L between the current point and the next point on the central line of the parent artery is calculated from the proximal release point;

In the embodiment of the specification, the expansion coefficient is the ratio of the section diameter of the simulated surface corresponding to the optimized centerline data of the parent artery to the diameter of the blood flow guiding device. The expansion coefficient is used for reflecting the real effect of the stent to be intervened after being implanted, and objective basis is provided for the selection of the stent to be intervened.

In the embodiment of the specification, the angle change curve displays the change of the corresponding parent artery blood vessel through the angle change of each point on the optimized parent artery central line data. The angle change curve is used for reflecting the real effect of the stent to be intervened after being implanted, and provides objective basis for the selection of the stent to be intervened.

In the embodiments of the present specification, the angle variation curve may be obtained by: the angle (180-angle)/180 of each point is obtained through an inverse cosine function to obtain the angle change of the current point, all angle change curves are firstly subjected to seven-point linear smoothing, and then quadratic function fitting smoothing is carried out to obtain the final curve. In the embodiments of the present specification, the angle change curve may be represented as a histogram.

In the embodiment of the specification, the diameter change curve is used for displaying the change of the diameter corresponding to each point on the central line of the optimized parent artery after the stent to be intervened is implanted. The diameter change curve is used for reflecting the real effect of the stent to be intervened after being implanted, and objective basis is provided for the selection of the stent to be intervened.

In the embodiment of the present specification, the diameter variation curve may be obtained by median filtering through diameters of all points corresponding to optimized centerline data of the parent artery, and the diameter variation curve may be represented as a histogram.

In the present specification embodiment, the wire diameter may be set by parameters to the diameter of the braided mesh wire.

Verification tests show that the simulation method provided by the embodiment of the specification can accurately display the length of the stent to be intervened, the accuracy rate is over 95%, the simulation can be accurately performed, and the requirements of clinical application are met.

By adopting the simulation method provided by the embodiment of the specification, the simulation of the stent to be intervened can be realized, the implantation condition of the stent can be observed, the optimal intervention stent can be selected, and the reference is provided for clinical application.

The simulation method provided in the embodiments of the present specification can determine the effect of the netting display and the adherence display when evaluating the simulation effect.

The above details a simulation method, and accordingly, the present specification also provides a simulation apparatus, as shown in fig. 5. Fig. 5 is a schematic diagram of a simulation apparatus provided in an embodiment of the present disclosure, where the simulation apparatus includes:

the acquiring module 501 is used for acquiring aneurysm parameters and parent artery parameters of the to-be-processed craniocerebral image data, wherein the central line of the parent artery is a uniform central line;

a stent surface simulation module 503, which performs modeling according to a velocity, a time Δ t and a growth distance position based on the aneurysm parameter and the parent artery parameter to obtain a stent simulation surface of a stent to be inserted, wherein the position + velocity Δ t is reduced to 0 when a preset constraint condition is satisfied;

and the support simulation module 505 is used for simulating the support to be intervened based on the support simulation surface to obtain at least one simulation effect of woven mesh display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter.

obtaining parameters of the stent to be intervened;

at least one processor; and the number of the first and second groups,

a memory communicatively coupled to the at least one processor; wherein,

The foregoing description has been directed to specific embodiments of this disclosure. Other embodiments are within the scope of the following claims. In some cases, the actions or steps recited in the claims may be performed in a different order than in the embodiments and still achieve desirable results. In addition, the processes depicted in the accompanying figures do not necessarily require the particular order shown, or sequential order, to achieve desirable results. In some embodiments, multitasking and parallel processing may also be possible or may be advantageous.

The embodiments in the present specification are described in a progressive manner, and the same and similar parts among the embodiments are referred to each other, and each embodiment focuses on the differences from the other embodiments. In particular, for the embodiments of the apparatus, the electronic device, and the nonvolatile computer storage medium, since they are substantially similar to the embodiments of the method, the description is simple, and the relevant points can be referred to the partial description of the embodiments of the method.

The apparatus, the electronic device, the nonvolatile computer storage medium and the method provided in the embodiments of the present description correspond to each other, and therefore, the apparatus, the electronic device, and the nonvolatile computer storage medium also have similar advantageous technical effects to the corresponding method.

In the 90 s of the 20 th century, improvements in a technology could clearly distinguish between improvements in hardware (e.g., improvements in circuit structures such as diodes, transistors, switches, etc.) and improvements in software (improvements in process flow). However, as technology advances, many of today's process flow improvements have been seen as direct improvements in hardware circuit architecture. Designers almost always obtain the corresponding hardware circuit structure by programming an improved method flow into the hardware circuit. Thus, it cannot be said that an improvement in the process flow cannot be realized by hardware physical modules. For example, a Programmable Logic Device (PLD), such as a Field Programmable Gate Array (FPGA), is an integrated circuit whose Logic functions are determined by programming the Device by a user. A digital system is "integrated" on a PLD by the designer's own programming without requiring the chip manufacturer to design and fabricate application-specific integrated circuit chips. Furthermore, nowadays, instead of manually making an integrated Circuit chip, such Programming is often implemented by "logic compiler" software, which is similar to a software compiler used in program development and writing, but the original code before compiling is also written by a specific Programming Language, which is called Hardware Description Language (HDL), and HDL is not only one but many, such as abel (advanced Boolean Expression Language), ahdl (alternate Language Description Language), traffic, pl (core unified Programming Language), HDCal, JHDL (Java Hardware Description Language), langue, Lola, HDL, laspam, hardsradware (Hardware Description Language), vhjhd (Hardware Description Language), and vhigh-Language, which are currently used in most common. It will also be apparent to those skilled in the art that hardware circuitry that implements the logical method flows can be readily obtained by merely slightly programming the method flows into an integrated circuit using the hardware description languages described above.

The controller may be implemented in any suitable manner, for example, the controller may take the form of, for example, a microprocessor or processor and a computer-readable medium storing computer-readable program code (e.g., software or firmware) executable by the (micro) processor, logic gates, switches, an Application Specific Integrated Circuit (ASIC), a programmable logic controller, and an embedded microcontroller, examples of which include, but are not limited to, the following microcontrollers: ARC 625D, Atmel AT91SAM, Microchip PIC18F26K20, and Silicone Labs C8051F320, the memory controller may also be implemented as part of the control logic for the memory. Those skilled in the art will also appreciate that, in addition to implementing the controller as pure computer readable program code, the same functionality can be implemented by logically programming method steps such that the controller is in the form of logic gates, switches, application specific integrated circuits, programmable logic controllers, embedded microcontrollers and the like. Such a controller may thus be considered a hardware component, and the means included therein for performing the various functions may also be considered as a structure within the hardware component. Or even means for performing the functions may be regarded as being both a software module for performing the method and a structure within a hardware component.

The systems, devices, modules or units illustrated in the above embodiments may be implemented by a computer chip or an entity, or by a product with certain functions. One typical implementation device is a computer. In particular, the computer may be, for example, a personal computer, a laptop computer, a cellular telephone, a camera phone, a smartphone, a personal digital assistant, a media player, a navigation device, an email device, a game console, a tablet computer, a wearable device, or a combination of any of these devices.

For convenience of description, the above devices are described as being divided into various units by function, and are described separately. Of course, the functionality of the various elements may be implemented in the same one or more software and/or hardware implementations in implementing one or more embodiments of the present description.

As will be appreciated by one skilled in the art, the present specification embodiments may be provided as a method, system, or computer program product. Accordingly, embodiments of the present description may take the form of an entirely hardware embodiment, an entirely software embodiment or an embodiment combining software and hardware aspects. Furthermore, embodiments of the present description may take the form of a computer program product embodied on one or more computer-usable storage media (including, but not limited to, disk storage, CD-ROM, optical storage, and so forth) having computer-usable program code embodied therein.

The description has been presented with reference to flowchart illustrations and/or block diagrams of methods, apparatus (systems), and computer program products according to embodiments of the description. It will be understood that each flow and/or block of the flow diagrams and/or block diagrams, and combinations of flows and/or blocks in the flow diagrams and/or block diagrams, can be implemented by computer program instructions. These computer program instructions may be provided to a processor of a general purpose computer, special purpose computer, embedded processor, or other programmable data processing apparatus to produce a machine, such that the instructions, which execute via the processor of the computer or other programmable data processing apparatus, create means for implementing the functions specified in the flowchart flow or flows and/or block diagram block or blocks.

These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing apparatus to function in a particular manner, such that the instructions stored in the computer-readable memory produce an article of manufacture including instruction means which implement the function specified in the flowchart flow or flows and/or block diagram block or blocks.

These computer program instructions may also be loaded onto a computer or other programmable data processing apparatus to cause a series of operational steps to be performed on the computer or other programmable apparatus to produce a computer implemented process such that the instructions which execute on the computer or other programmable apparatus provide steps for implementing the functions specified in the flowchart flow or flows and/or block diagram block or blocks.

In a typical configuration, a computing device includes one or more processors (CPUs), input/output interfaces, network interfaces, and memory.

The memory may include forms of volatile memory in a computer readable medium, Random Access Memory (RAM) and/or non-volatile memory, such as Read Only Memory (ROM) or flash memory (flash RAM). Memory is an example of a computer-readable medium.

Computer-readable media, including both non-transitory and non-transitory, removable and non-removable media, may implement information storage by any method or technology. The information may be computer readable instructions, data structures, modules of a program, or other data. Examples of computer storage media include, but are not limited to, phase change memory (PRAM), Static Random Access Memory (SRAM), Dynamic Random Access Memory (DRAM), other types of Random Access Memory (RAM), Read Only Memory (ROM), Electrically Erasable Programmable Read Only Memory (EEPROM), flash memory or other memory technology, compact disc read only memory (CD-ROM), Digital Versatile Discs (DVD) or other optical storage, magnetic cassettes, magnetic tape disk storage or other magnetic storage devices, or any other non-transmission medium which can be used to store information that can be accessed by a computing device. As defined herein, a computer readable medium does not include a transitory computer readable medium such as a modulated data signal and a carrier wave.

It should also be noted that the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising an … …" does not exclude the presence of other like elements in a process, method, article, or apparatus that comprises the element.

This description may be described in the general context of computer-executable instructions, such as program modules, being executed by a computer. Generally, program modules include routines, programs, objects, components, data structures, etc. that perform particular tasks or implement particular abstract data types. The specification may also be practiced in distributed computing environments where tasks are performed by remote processing devices that are linked through a communications network. In a distributed computing environment, program modules may be located in both local and remote computer storage media including memory storage devices.

The embodiments in the present specification are described in a progressive manner, and the same and similar parts among the embodiments are referred to each other, and each embodiment focuses on the differences from the other embodiments. In particular, for the system embodiment, since it is substantially similar to the method embodiment, the description is simple, and for the relevant points, reference may be made to the partial description of the method embodiment.

The above description is only an example of the present specification, and is not intended to limit the present application. Various modifications and changes may occur to those skilled in the art. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application should be included in the scope of the claims of the present application.

Claims

1. A method of simulation, the method comprising:

2. The method according to claim 1, wherein said obtaining a stent simulation surface of a stent to be inserted based on said aneurysm parameters and said parent artery parameters by modeling according to a velocity, a time Δ t, and a growth distance position, comprises:

obtaining parameters of the stent to be intervened;

3. The method of claim 1, wherein the predetermined constraint includes one or more of inflation detection, growth detection, stretch detection, collision detection, and planar detection.

4. The method according to claim 3, wherein the expansion detection means that the speed is reduced to 0 when the stent to be inserted is increased by a distance greater than the diameter of the stent to be inserted by a maximum expansion coefficient determined by the properties and material of the stent to be inserted.

5. The method of claim 3, wherein the growth detection is performed by taking a proximal release point on a centerline of the parent artery as a release starting point, taking a uniform point on the centerline of the parent artery as a scale along an initial direction, selecting a point with any scale as a current point, taking N points before and after the current point on the centerline of the parent artery as a group, and when a total growth distance of the current point is greater than a first preset multiple of an average distance, the speed is decreased to 0, wherein the N value is determined by the uniformity of the centerline of the parent artery, and the average distance is an average distance of the group where N points before and after the current point are located.

6. The method of claim 5, wherein if the scale value between the current point and the proximal release point is < N, then the specific scale at which the current point on the centerline of the parent artery is located is taken as a group;

7. The method of claim 5, wherein the stretch detection indicates that the speed is decreased to 0 when the total distance of the current point increases by more than a second predetermined multiple of an average distance in a current direction, wherein the current direction is a direction in which the initial direction is located, and the average distance in the current direction is a distance in the current direction of a group in which the current point is located.

8. The method according to claim 5, wherein the collision detection means that when the point in two directions of the current point touches the blood vessel wall, the speed is reduced to 0, wherein the two directions are respectively the direction of the initial direction and the opposite direction of the initial direction.

9. The method of claim 5, wherein the plane detection means calculates a distance between the current point and a plane where a front point and a back point are located, and the speed is reduced to 0 when the current point reaches an inside of the plane where the front point is located and reaches an outside of the plane where the back point is located along the initial direction, the front point is a point located in front of the current point along the initial direction, and the back point is a point located behind the current point along the initial direction.

10. The method according to claim 2, wherein said mesh-grid display is a mesh-grid display consisting of the intersections of said source points with said stent simulation surface, extending in said initial direction at said intervals (180/number of stent wires) in the clockwise and counterclockwise direction, respectively, in the release area of said stent to be introduced.

11. The method according to claim 1, wherein said adherent display is calculated as dis distance between the points of the simulated surface and the vessel wall, and the pseudo-color display is calculated according to rgb color model, according to the formula r 255 dis 2; g? 0.0:255 (1.0-dis) 0.5; b is 0; r > 255? 255: r; g > 255? And 255 g, calculating and displaying adherence.

12. The method of claim 1, wherein the length display is calculated from a proximal release point, calculating a distance L between a current point and a next point on a centerline of the parent artery;

13. A simulation apparatus, the apparatus comprising:

and the support model module is used for simulating the support to be intervened based on the support simulation surface to obtain at least one simulation effect of woven mesh display, adherence display, length display, metal coverage rate, expansion coefficient, angle change curve, diameter change curve and metal wire diameter.

14. The apparatus according to claim 13, wherein said obtaining a stent simulation surface of a stent to be inserted based on said aneurysm parameters and said parent artery parameters by modeling according to a velocity, a time Δ t, and a growth distance position, comprises:

obtaining parameters of the stent to be intervened;

15. The apparatus of claim 13, wherein the predetermined constraint condition comprises one or more of a swelling detection, a growth detection, a tension detection, a collision detection, and a plane detection.

16. The apparatus according to claim 15, wherein the expansion detection means that the speed is reduced to 0 when the stent to be inserted is increased by a distance greater than a diameter x a maximum expansion coefficient of the stent to be inserted, wherein the maximum expansion coefficient is determined by properties and materials of the stent to be inserted.

17. The apparatus of claim 15, wherein the growth detection is performed by taking a proximal release point on a centerline of the parent artery as a release starting point, taking a uniform point on the centerline of the parent artery as a scale along an initial direction, selecting a point with any one scale as a current point, taking N points before and after the current point on the centerline of the parent artery as a group, and when a total growth distance of the current point is greater than a first preset multiple of an average distance, the speed is decreased to 0, wherein the value of N is determined by the uniformity of the centerline of the parent artery, and the average distance is an average distance of the group of N points before and after the current point.

18. The device of claim 17, wherein if the scale value between the current point and the proximal release point is < N, the specific scale at which the current point on the centerline of the parent artery is located is taken as a group;

19. The apparatus of claim 17, wherein the stretch detection indicates that the speed is decreased to 0 when the total distance of the current point increases by more than a second predetermined multiple of an average distance in a current direction, wherein the current direction is a direction in which the initial direction is located, and the average distance in the current direction is a distance in the current direction of a group in which the current point is located.

20. The apparatus of claim 17, wherein the collision detection means that the velocity is reduced to 0 when a point touches the blood vessel wall in two directions of the current point, wherein the two directions are respectively a direction in which the initial direction is located and a direction opposite to the initial direction.

21. The apparatus of claim 17, wherein the plane detection means calculates a distance between the current point and a plane where a front point and a back point are located, the speed is reduced to 0 when the current point reaches an inside of the plane where the front point is located and reaches an outside of the plane where the back point is located along the initial direction, the front point is a point located in front of the current point along the initial direction, and the back point is a point located behind the current point along the initial direction.

22. The device according to claim 14, wherein said mesh-grid display means that in the release area of said stent to be inserted, said source points are respectively in clockwise and counterclockwise directions, along said initial direction, according to the angular extension of said interval (180/number of stent wires), and the intersection points with said stent simulation surface constitute mesh-grid display.

23. The device of claim 13 wherein said adherent display is calculated as dis distance between the points of the simulated surface and the vessel wall, and wherein the pseudo-color display is in rgb color mode, according to the formula r 255 dis 2; g? 0.0:255 (1.0-dis) 0.5; b is 0; r > 255? 255: r; g > 255? And 255 g, calculating and displaying adherence.

24. The apparatus of claim 13, wherein the length display is calculated from a proximal release point, calculating a distance L between a current point and a next point on a centerline of the parent artery;

25. An electronic device, comprising:

at least one processor; and the number of the first and second groups,

a memory communicatively coupled to the at least one processor; wherein,