Method for obtaining a support compression model and electronic device

Abstract

The application discloses a method for obtaining a stent compression model and an electronic device, and relates to the technical field of surgical planning. The disclosed method comprises the following steps: obtaining a diastolic model of a stent; setting the stent diameter in the diastolic model as a target diameter; adjusting the stent length in the diastolic model according to the target helix length to obtain an adjusted stent length; and generating a compression model based on the adjusted stent length. The application sets the stent diameter in the diastolic model as the target diameter, and adjusts the stent length in the diastolic model so that the helix length of the stent model after the stent length is adjusted is equal to (or approximately equal to) the target helix length, thereby ensuring that the compression model constructed conforms to the helix length conservation law, and further improving the geometric precision of the compression model, and providing reliable size selection and performance selection basis for clinical surgical planning.

Description

Technical Field

[0001] This application generally relates to the field of surgical planning technology. More specifically, this application relates to a method for obtaining a stent compression model and an electronic device. Background Technology

[0002] Flow diverters (FDs) can promote neck healing of aneurysms by altering the direction of blood flow within a blood vessel, and have become an important tool for treating vascular diseases such as intracranial aneurysms. In clinical surgical planning, surgeons need to simulate the deployment pattern of the FD within the parent artery in advance to assess key properties such as FD adherence and metal coverage, thereby selecting the optimal FD size.

[0003] In existing technologies, virtual FDs are typically generated based on geometric modeling or physical simulation. For example, Chinese patent application number 202010623464.3 proposes a simulation method based on "shell" constraints. This method constructs a cylindrical shell that matches the inner diameter of the artery carrying the tumor, constrains the FD model within the shell, and then releases it to simulate the process of the FD adhering to the vessel wall. However, existing virtual FD generation methods do not fully consider the physical conservation laws followed by the FD braided structure during compression, resulting in a deviation in the microstructure between the simulated FD geometry and the actual compressed geometry.

[0004] In view of this, this application proposes a method and electronic device for obtaining a stent compression model, so as to improve the geometric accuracy of the virtual FD model and provide a reliable basis for size and performance selection for clinical surgical planning. Summary of the Invention

[0005] In order to at least solve one or more of the technical problems mentioned above, this application proposes methods and electronic devices for obtaining a stent compression model in several aspects.

[0006] In a first aspect, this application provides a method for obtaining a stent compression model, comprising: obtaining a diastolic model of the stent; setting the stent diameter in the diastolic model as a target diameter; adjusting the stent length in the diastolic model according to a target helix length to obtain an adjusted stent length; and generating a compression model based on the adjusted stent length.

[0007] In a second aspect, this application provides an electronic device, including: a processor; and a memory having program code stored thereon for acquiring a scaffold compression model, wherein when the program code is executed by the processor, the electronic device performs the method as described in the first aspect.

[0008] This application sets the stent diameter in the diastolic model as the target diameter, and adjusts the stent length in the diastolic model so that the helix length of the stent model after adjusting the stent length is equal to (or approximately equal to) the target helix length; thereby ensuring that the constructed compression model conforms to the law of conservation of helix length, thereby improving the geometric accuracy of the compression model and providing a reliable basis for size and performance selection for clinical surgical planning. Attached Figure Description

[0009] The above and other objects, features, and advantages of exemplary embodiments of this application will become readily understood by reading the following detailed description with reference to the accompanying drawings. In the drawings, several embodiments of this application are illustrated by way of example and not limitation, and the same or corresponding reference numerals denote the same or corresponding parts, wherein:

[0010] Figure 1 Exemplary schematic diagrams of treating aneurysms via FD in some embodiments of this application are shown.

[0011] Figure 2 An exemplary flowchart of a method for obtaining a stent compression model according to some embodiments of this application is shown.

[0012] Figure 3a An exemplary schematic diagram of a compression bracket in some embodiments of this application is shown.

[0013] Figure 3b An exemplary schematic diagram of the support spiral in some embodiments of this application is shown.

[0014] Figure 4 An exemplary schematic diagram of a diamond-shaped hole in some embodiments of this application is shown.

[0015] Figure 5 An exemplary schematic diagram of a spiral in some embodiments of this application is shown.

[0016] Figure 6 A schematic diagram of a three-dimensional geometric model of a dense mesh support in a relaxed state is shown in some embodiments of this application.

[0017] Figure 7 A schematic diagram showing the relationship between the support compression diameter and the support length in some embodiments of this application is illustrated. Detailed Implementation

[0018] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this application. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0019] It should be understood that the terms "comprising" and "including" used in the specification and claims of this application indicate the presence of the described features, integrals, steps, operations, elements and / or components, but do not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components and / or collections thereof.

[0020] It should also be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the application. As used in this specification and claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the term “and / or” as used in this specification and claims refers to any combination and all possible combinations of one or more of the associated listed items, and includes such combinations.

[0021] As used in this specification and claims, the term "if" may be interpreted, depending on the context, as "when," "once," "in response to determination," or "in response to detection." Similarly, the phrase "if determined" or "if [described condition or event] is detected" may be interpreted, depending on the context, as "once determined," "in response to determination," "once [described condition or event] is detected," or "in response to detection of [described condition or event]."

[0022] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "multiple" means two or more, unless otherwise expressly specified. "Several" means one or more, unless otherwise expressly specified.

[0023] The specific embodiments of this application will now be described in detail with reference to the accompanying drawings.

[0024] FD is woven from multiple metal wires and has a mesh-like cylindrical shape; therefore, FD can also be called a dense mesh support.

[0025] Figure 1 Exemplary schematic diagrams of treating aneurysms via FD in some embodiments of this application are shown. Figure 1As shown, the raised area within the parent artery is the aneurysm, and the reticular structure is the fibrous ductus arteriosus (FD). When the FD is placed within the parent artery and covers the aneurysm neck, the fine mesh creates resistance, resulting in very little blood entering the aneurysm cavity and flowing extremely slowly. The blood inside the aneurysm gradually coagulates, forming a thrombus that eventually organizes. Furthermore, over time, vascular endothelial cells grow along the FD at the aneurysm neck, thus promoting neck healing.

[0026] The diameter of the parent artery is typically smaller than the natural dilatation diameter of the fibroadenoma (FD). Before FD implantation, the surgeon first compresses the FD using physical compression and inserts the compressed FD into a microcatheter. During the implantation procedure, the surgeon pushes the microcatheter to the parent artery. Once the tip of the microcatheter reaches the predetermined position, it is slowly pulled back, allowing the FD to cover the aneurysm neck and prevent blood from entering the aneurysm cavity. In clinical surgical planning, the surgeon needs to simulate the deployment pattern of the FD within the parent artery to assess key properties such as apposition and metal coverage, thereby selecting the optimal FD size.

[0027] However, existing virtual FD generation methods do not fully consider the physical conservation laws followed by the FD braided structure during compression, resulting in microstructural deviations between the simulated FD geometry and the actual compressed morphology. Therefore, this application proposes a method and electronic device for obtaining a stent compression model to improve the geometric accuracy of the virtual FD model and provide reliable basis for size and performance selection in clinical surgical planning.

[0028] Figure 2 An exemplary flowchart of a method 200 for obtaining a stent compression model according to some embodiments of this application is shown. Figure 2 As shown, in some embodiments, method 200 includes: S201, obtaining a diastolic model of the stent; S202, setting the stent diameter in the diastolic model to a target diameter; S203, adjusting the stent length in the diastolic model according to the target spiral length to obtain an adjusted stent length; and S204, generating a compression model based on the adjusted stent length.

[0029] Method 200 is used to obtain a stent compression model, wherein: the stent may be a dense mesh stent; the model may be a three-dimensional model, such as a three-dimensional model constructed based on geometric modeling or physical simulation. In some embodiments, the stent diastolic model refers to a standard three-dimensional model of the stent in a completely free, unconstrained, diastolic state. In some embodiments, the stent compression model refers to a three-dimensional model of the stent in a compressed state, such as a three-dimensional model of the stent when compressed in the simulated aneurysm-bearing artery.

[0030] In some embodiments, the diastolic model can be a pre-built three-dimensional model, which is extracted from the pre-built three-dimensional model file during the execution of method 200. In other embodiments, the diastolic model is constructed in real time based on relevant parameters of the stent in the diastolic state.

[0031] Figure 3a Exemplary schematic diagrams of compression supports in some embodiments of this application are shown. For example... Figure 3a As shown, after being compressed, the diameter of the support decreased (from 5mm to 3mm) and the length of the support increased.

[0032] Figure 3b Exemplary schematic diagrams of the helical lines of the support structure in some embodiments of this application are shown. The support structure is woven from multiple metal wires, which extend spirally from one end of the support structure to the other; thus, each physically existing metal wire presents a spiral line in spatial geometry. Figure 3b As shown, spiral wire-1 and spiral wire-2 are extracted from support-1. The points where the two metal wires intersect form nodes, as shown... Figure 3b As further illustrated, helix-1 and helix-2 each include multiple nodes; each physically existing intersection of metal wires is geometrically represented as a node. The length of the support helix follows a conservation law, meaning that the length of the support helix remains unchanged before and after compression.

[0033] Method 200 first obtains a diastolic model of the stent, then sets the stent diameter in the diastolic model as the target diameter. The target diameter can be smaller than the stent diameter in the diastolic model, thus simulating the stent compression process. The target helix length can be the length of any helix extracted from the diastolic model, or it can be the average length obtained by averaging the lengths of multiple helixes. Method 200 sets the stent diameter in the diastolic model as the target diameter and adjusts the stent length in the diastolic model so that the helix length of the stent model after adjusting the stent length is equal to (or approximately equal to) the target helix length. This ensures that the constructed compression model conforms to the helix length conservation law, thereby improving the geometric accuracy of the compression model and providing a reliable basis for size and performance selection in clinical surgical planning.

[0034] In some embodiments, method 200 employs a model generation algorithm to generate a compression model based on a stent parameter tuple in a compressed state, wherein the parameter tuple includes multiple stent parameters, such as stent length. In these embodiments, the stent length in the diastolic model is adjusted according to the target spiral length to obtain an adjusted stent length; further, the compression model is generated based on the parameter tuple whose stent length value is the adjusted stent length.

[0035] In some embodiments, adjusting the stent length in the diastolic model according to the target spiral length includes: adjusting the stent length in the diastolic model according to the target spiral length and the target spiral coil number.

[0036] Similar to the metal wire, the helix extends from one end of the support to the other. With a rotation of 360° around the circumference constituting one revolution, the helix rotates multiple times during its extension, thus forming multiple helical coils. The number of helical coils follows a conservation law, meaning that the number of helical coils remains constant before and after compression.

[0037] In some embodiments, method 200 first obtains a relaxation model of the stent, and then sets the stent diameter in the relaxation model as a target diameter. The target number of spiral coils can be the number of spiral coils of any spiral extracted from the relaxation model, or it can be the average number of spiral coils obtained by averaging the number of spiral coils of multiple spirals. In these embodiments, method 200 sets the stent diameter in the relaxation model as the target diameter by adjusting the stent length in the relaxation model so that, after adjusting the stent length, the stent model has: a spiral length equal to (or approximately equal to) the target spiral length, and a number of spiral coils equal to (or approximately equal to) the target number of spiral coils; thereby ensuring that the constructed compression model conforms to the laws of conservation of spiral length and conservation of the number of spiral coils.

[0038] In some embodiments, obtaining the diastolic model of the stent includes: obtaining the diastolic diameter, diastolic length, number of circumferential nodes, and diastolic node angle of the stent; calculating the stent node coordinates based on the diastolic diameter, diastolic length, number of circumferential nodes, and diastolic node angle; and generating the diastolic model based on the stent node coordinates.

[0039] In some embodiments, the model generation algorithm generates a diastolic model based on a tuple of stent parameters in the diastolic state. This tuple includes multiple stent parameters, such as diastolic diameter, diastolic length, number of circumferential nodes, and diastolic node angle. The number of circumferential nodes refers to the number of nodes distributed across a cross-section of the stent; the node angle refers to the angle formed between two intersecting wires. It is understood that the stent's diameter, length, and node angle change as the stent is compressed, while the number of circumferential nodes does not change with stent compression. The diastolic diameter, diastolic length, and diastolic node angle refer to the stent's diameter, length, and node angle in the diastolic state.

[0040] In some embodiments, during the process of generating a diastolic model based on the stent parameter tuple in the diastolic state, the model generation algorithm first calculates the coordinates of all nodes of the stent based on the stent parameter tuple, and then generates the diastolic model based on the stent node coordinates. In these embodiments, after determining the coordinates of all nodes, the model generation algorithm connects nodes belonging to the same wire according to the stent's weaving pattern to generate a helix, thereby facilitating the generation of the diastolic model.

[0041] In some embodiments, calculating the stent node coordinates based on the diastolic diameter, diastolic length, number of circumferential nodes, and diastolic node angle includes: calculating the diastolic axial interlayer spacing based on the diastolic diameter, number of circumferential nodes, and diastolic node angle; calculating the number of stent layers based on the diastolic length and diastolic axial interlayer spacing; and calculating the stent node coordinates based on the diastolic axial interlayer spacing and the number of stent layers.

[0042] The support is made of multiple interwoven metal wires, which form diamond-shaped holes. Figure 4 Exemplary schematic diagrams of diamond-shaped holes in some embodiments of this application are shown. Figure 4 As shown, the direction extending along the central axis of the support is defined as the axial direction, and the direction extending perpendicularly from the central axis of the support towards the outer perimeter of the support is defined as the radial direction. The diagonal length of the rhomboid mesh in the axial direction is the axial layer spacing of the support. In the axial direction, each ring of the rhomboid mesh of the support constitutes one layer of the support. The number of support layers can be understood as the number of rhomboid holes formed in the axial direction of the support.

[0043] Distensional axial interlayer spacing refers to the axial interlayer spacing of the stent in the distension state. In some embodiments, this is determined by the formula... Based on the diastolic diameter (D) e ), number of circumferential nodes (NC) e and the angle between the diastolic nodes (θ) e ), calculate the diastolic axial interlayer spacing (H) e In other embodiments, based on the diastolic diameter (D) e ), number of circumferential nodes (NC) e and the angle between the diastolic nodes (θ) e ), calculate the diastolic axial interlayer spacing (H) e )include: Calculate the radius of relaxation (R) e ):R e =D e / 2; Calculate the circumferential angle (α) between adjacent circular nodes: α = 2π / NC e ;as well as Calculate the diastolic axial interlayer spacing: .

[0044] In some embodiments, by formula Based on diastolic length (L) e ), diastolic axial interlayer spacing, and calculate the number of stent layers N1; where, diastolic length refers to the length of the stent in the diastolic state. This indicates rounding down to the nearest integer. The addition of 1 is to ensure that there is a layer of diamond-shaped holes at both ends.

[0045] In some embodiments, calculating the stent node coordinates based on the diastolic axial interlayer spacing and the number of stent layers includes: adjusting the diastolic axial interlayer spacing according to the number of stent layers to obtain the adjusted diastolic axial interlayer spacing (AH). e ); Calculate the coordinates of the stent nodes based on the adjusted axial spacing between the layers and the number of stent layers.

[0046] In some embodiments, based on formula The diastolic axial interlayer spacing is adjusted according to the number of stent layers to obtain the adjusted diastolic axial interlayer spacing.

[0047] In some embodiments, the layers of the support are numbered, with variable i serving as the layer index to represent the N1 layers of the support, and the value of i ranging from 0 to N1-1; the nodes of the support in the same circumferential direction are numbered, with variable j serving as the circumferential index to represent the NC nodes of the support in the same circumferential direction. e There are nodes, and the value of j ranges from 0 to NC. e -1. In these embodiments, the support nodes are indexed by ordered pairs (i,j), where the node coordinates (x,j) of node P(i,j) in the spatial Cartesian coordinate system are... ij ,y ij ,z ij It can be calculated using the following formula: , , .

[0048] In some embodiments, the target diameter is set based on the vessel diameter. For example, the target diameter can be set to the diameter of the carrier artery to simulate the compression of the stent by the carrier artery.

[0049] In some embodiments, method 200 includes: obtaining the node coordinates of multiple nodes on a helix of the stent; calculating the distance between adjacent nodes based on the node coordinates of two adjacent nodes; and summing the distances between adjacent nodes to obtain a target helix length. In these embodiments, the target helix length can be the length of any helix extracted from the relaxation model, and the length of the helix is ​​obtained by summing the distances between adjacent nodes.

[0050] Figure 5Exemplary schematic diagrams of spirals in some embodiments of this application are shown. Figure 5 As shown, in some embodiments, the leftmost node of the helix L in the axial direction is P0, its corresponding layer index is 0, and its circumferential index is a. There are two adjacent nodes P on L. m P m+1 Assume P m The layer index is i m The circumferential index is j m P m+1 The layer index is i m+1 The circumferential index is j m+1 Then we have: i m+1 =i m +1, j m+1 =(j m +1) mod (NC) e Assume P m The coordinates are (x m ,y m ,z m ), P m+1 The coordinates are (x m+1 ,y m+1 ,z m+1 ), then P m With P m+1 The distance is: The total length of the spiral L can be obtained by summing the distances between all its adjacent nodes, i.e. .

[0051] In some embodiments, method 200 includes: calculating a target number of spiral coils based on the number of stent layers and the number of circumferential nodes. In these embodiments, the target number of spiral coils can be the number of spiral coils of any spiral extracted from the relaxation model. The number of spiral coils is determined by the total angle of rotation of the spiral around the central axis of the stent during its travel; since the spiral rotates by a basic angle in the circumferential direction with each advancement of a layer, it can be calculated based on... To calculate the total number of spiral turns (CN).

[0052] In some embodiments, adjusting the stent length in the diastolic model based on the target spiral length and the target number of spiral coils includes: initializing the stent length to the diastolic length; adjusting the stent length in the diastolic model based on the target spiral length and the target number of spiral coils through iterative iteration; wherein each iteration includes: calculating the current spiral length and the current number of spiral coils based on the current stent length; in response to the current spiral length and the current number of spiral coils satisfying a preset condition: updating the axial interlayer spacing in the diastolic model based on the current spiral length and the target spiral length to obtain an updated axial interlayer spacing; and adjusting the stent length in the diastolic model based on the updated axial interlayer spacing.

[0053] In some embodiments, the stent diameter in the diastolic model is set to the target diameter, while keeping the number of circumferential nodes and the number of stent layers unchanged. The stent length in the diastolic model is adjusted through iterative loops based on the target spiral length and the target number of spiral coils until, after adjusting the stent length, the spiral length of the stent model is equal to (or approximately equal to) the target spiral length, and the number of spiral coils is equal to (or approximately equal to) the target number of spiral coils.

[0054] In some embodiments, each cycle includes the following steps a, b, c, d.

[0055] a. Calculate the current helix length and the current number of helix coils based on the current support length. The calculation methods for helix length and the number of helix coils have been introduced earlier, so they will not be repeated here. It should be noted that the current helix length is calculated under the condition that the support length is the current support length, and the current number of helix coils is calculated under the condition that the support length is the current support length.

[0056] b. If the current spiral coil length and the current spiral coil number meet preset conditions, update the axial interlayer spacing in the relaxation model based on the current spiral length and the target spiral length to obtain the updated axial interlayer spacing. In some embodiments, if the current spiral length and the current spiral coil number meet preset conditions, it is considered that iterative optimization needs to continue; in these embodiments, based on the current spiral length (length... cur ), Target spiral length tar The ratio of ) Calculate a new axial interlayer spacing to obtain the updated axial interlayer spacing AH. e .

[0057] c. Adjust the stent length in the relaxation model according to the updated axial interlayer spacing. In some embodiments, according to AH e To adjust the length of the stent in the diastolic model to obtain In these embodiments, based on Regenerate the model nodes and proceed to step a.

[0058] d. If the current spiral coil length and the current number of spiral coils do not meet the preset conditions, it is considered unnecessary to continue iterative optimization, and the iteration process is stopped. In this case, the optimized compression model is output, which includes the three-dimensional node coordinates, connection relationships, and the calculated axial interlayer spacing.

[0059] In some embodiments, the preset conditions include: the difference between the current helix length and the target helix length is within a first preset range; or, the difference between the current number of helix coils and the target number of helix coils is within a second preset range.

[0060] In some embodiments, the first preset range is (-∞,-ε]∪[ε,+∞), and the second preset range is (-∞,-δ]∪[δ,+∞), where ε and δ are preset tolerances; in these embodiments, the difference between the current helix length and the target helix length is calculated as length. cur -length tar Calculate the current number of spiral coils and the target number of spiral coils (CN). tar The difference CN cur -CN tar If length cur -length tar Falling within the first preset range, or CN cur -CN tar If the current spiral length and the current number of spiral coils fall within the second preset range, then the preset conditions are considered met. Further, if |length cur -length tar |<εand|CN cur -CN tar If |<δ, it is considered that the current spiral length and the current spiral coil number do not meet the preset conditions, and the iteration process is stopped.

[0061] In some embodiments, an optimization algorithm is used to adjust and optimize based on the diastolic model to obtain a compression model. In these embodiments, the diameter D of the tumor-bearing artery is input to the optimization algorithm. c The optimization algorithm initializes a compression stent model with a stent diameter of D. c The length of the support is L e Maintaining the number of circumferential nodes NC e Assuming the number of support layers N1 remains constant, with min|length cur -length tar |and min|CN cur -CN tar To optimize the objective, the axial interlayer spacing of the compression stent is changed iteratively by adjusting the stent length. cur -length tar |and|CN cur -CN tar The iteration terminates when all values ​​are less than their respective set thresholds. The iteration steps are as follows: Input steps. Input constraint diameter D cAnd the length obtained from the relaxation model tar CN tar NC e 、N1.

[0062] Initialization steps. (Based on D) c Where is the diameter and the dilation length L e An initial compression support model is established based on the initial length.

[0063] Calculation steps. Calculate the length of the current model. cur CN cur .

[0064] Determine the convergence step. If |length cur -length tar |<εand|CN cur -CN tar If | < δ, the iteration terminates and the current model is output.

[0065] Adjust the steps. If the convergence condition is not met, then adjust according to the length. cur With length tar The ratio of the two values ​​is used to calculate a new axial interlayer spacing AH. e And based on AH e Update the support length of the model to obtain .

[0066] Model update steps. Based on Regenerate the model nodes and proceed to the calculation step.

[0067] This application also discloses an electronic device, including: a processor; and a memory storing program code for acquiring a scaffold compression model. When the program code is executed by the processor, the electronic device performs the method described in any of the preceding embodiments. The specific functions implemented by the electronic device provided in the embodiments of this specification can be explained in comparison with the foregoing embodiments in this specification, and can achieve the technical effects of the foregoing embodiments, and will not be repeated here.

[0068] To facilitate readers' understanding of the technical solution of this application, Embodiment 1 is provided here to clarify the technical solution of this application.

[0069] Example 1 1. Parameter input and baseline model construction.

[0070] Figure 6 A schematic diagram of a three-dimensional geometric model of a dense mesh support in a relaxed state, as shown in some embodiments of this application, is illustrated. Figure 6As shown, the expansion diameters of these dense mesh supports are 5mm, 4.9mm, 4.8mm, 3.0mm and 2.0mm, respectively.

[0071] Taking the lattice-AF5004FB stent from Eike as an example, the diastolic diameter D of this stent... e It is 5mm, and the diastolic length L e It is 22mm, and the number of circumferential nodes is NC. e =24, diastolic node angle θ e ≈122°. The diastolic radius R of the stent in the diastolic state. e The thickness is 2.5 mm, the circumferential angle α is 0.2618 rad, and the diastolic axial interlayer spacing H is... e The thickness is 0.363mm, and the calculated number of support layers N1 is 61 layers.

[0072] 2. Calculate the target spiral length on the relaxation model. tar The diameter is 44.91 mm, and the target number of spiral coils is CN. tar It is 2.5 laps.

[0073] 3. Iterative optimization of the compression process, setting the target diameter D. c =4.9mm, maintaining the number of circumferential nodes NC e =24. The number of scaffold layers N1 remains unchanged at 61 layers. The first iteration process is as follows: (1) Calculate the initial parameters and ratio of the compression diameter. Initialize the axial interlayer spacing H. e =0.366667mm, initial helix length length=44.233671mm, length ratio .

[0074] (2) Update the axial interlayer spacing according to the ratio. New support length .

[0075] (3) Calculate the updated model parameters. The updated current helix length is... cur ≈44.403127mm, current number of spiral coils CN cur =2,500,000 cycles, updating axial interlayer spacing .

[0076] (4) Calculate the convergence error: |length cur -length tar |≈0.511657mm,|CN cur -CN tar |=0.000000 cycles.

[0077] If the current spiral length and the current number of spiral coils do not meet the convergence criteria, the new length ratio is recalculated based on the updated model parameters.

[0078] Figure 7 A schematic diagram showing the relationship between the compression diameter and length of the stent in some embodiments of this application is illustrated, wherein the stent is a lattice-AF5004FB model stent. Figure 7 As shown, the method for obtaining a stent compression model disclosed in this application was used to simulate various cases with target diameters ranging from 0.5 to 4.9 mm, at 0.1 mm intervals. Figure 7 The support length of the compression model corresponding to each target diameter is shown.

[0079] While numerous embodiments of this application have been shown and described herein, it will be apparent to those skilled in the art that such embodiments are provided by way of example only. Many modifications, alterations, and alternatives will arise for those skilled in the art without departing from the spirit and intent of this application. It should be understood that various alternatives to the embodiments of this application described herein may be employed in the practice of this application. The appended claims are intended to define the scope of protection of this application and therefore cover equivalents or alternatives within the scope of these claims.

Claims

1. A method for obtaining a scaffold compression model, characterized in that, include: Obtain the relaxation model of the stent; Set the stent diameter in the diastolic model to the target diameter; Based on the target spiral length and the target spiral coil number, adjust the stent length in the relaxation model to obtain the adjusted stent length; as well as A compression model is generated based on the adjusted stent length; The adjustment of the stent length in the relaxation model, based on the target spiral length and the target number of spiral coils, includes: Initialize the stent length to the diastolic length; The length of the stent in the diastolic model is adjusted by iterative loops based on the target spiral length and the target number of spiral coils. Each cycle includes: Calculate the current spiral length and the current number of spiral coils based on the current support length; In response to the current helix length and the current number of helix coils meeting preset conditions: The axial interlayer spacing in the relaxation model is updated based on the ratio of the current helix length to the target helix length to obtain the updated axial interlayer spacing. Adjust the stent length in the relaxation model based on the updated axial interlayer spacing.

2. The method according to claim 1, characterized in that, Obtaining the diastolic model of the stent includes: Obtain the diastolic diameter, diastolic length, number of circumferential nodes, and included angle of the diastolic nodes of the stent; Calculate the coordinates of the stent nodes based on the diastolic diameter, diastolic length, number of circumferential nodes, and the included angle between the diastolic nodes; and A relaxation model is generated based on the coordinates of the stent nodes.

3. The method according to claim 2, characterized in that, The coordinates of the stent nodes are calculated based on the diastolic diameter, diastolic length, number of circumferential nodes, and the included angle between the diastolic nodes. The axial interlayer spacing of the diastolic axis is calculated based on the diastolic diameter, the number of circumferential nodes, and the included angle of the diastolic nodes. Calculate the number of stent layers based on diastolic length and diastolic axial interlayer spacing; and Calculate the coordinates of the stent nodes based on the diastolic axial interlayer spacing and the number of stent layers.

4. The method according to claim 1, characterized in that, The target diameter is set based on the diameter of the blood vessel.

5. The method according to claim 1, characterized in that, include: Obtain the node coordinates of multiple nodes on the spiral line of the bracket; The distance between adjacent nodes is calculated based on the node coordinates of two adjacent nodes. The distances between adjacent nodes are summed to obtain the target spiral length.

6. The method according to claim 1, characterized in that, include: Calculate the target number of spiral coils based on the number of support layers and the number of circumferential nodes.

7. The method according to claim 1, characterized in that, The preset conditions include: The difference between the current helix length and the target helix length is within a first preset range; or, the difference between the current number of helix coils and the target number of helix coils is within a second preset range.

8. An electronic device, characterized in that, include: processor; as well as A memory storing program code for acquiring a scaffold compression model, wherein when the program code is executed by the processor, the electronic device implements the method as described in any one of claims 1-7.

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