Method, electronic device, and storage medium for simulating layered release of interventional consumables

Abstract

This application discloses a method, electronic device, and storage medium for simulating the layered release of interventional consumables. The computer-implemented method for simulating the layered release of interventional consumables includes: acquiring a discrete mesh model of the interventional consumable in a blood vessel, wherein the initial state of the discrete mesh model is a compressed state; constructing a set of constraints based on position dynamics (PBD) for the discrete mesh model, wherein the PBD constraint set includes a layered release range and layered release constraints; and performing layered release on the compressed discrete mesh model based on the layered release range and layered release constraints. This application cleverly introduces position dynamics-based PBD technology to simulate the layered release of interventional consumables, thereby accurately and efficiently simulating the actual release process of interventional consumables in clinical practice.

Description

Technical Field

[0001] This application generally relates to the fields of medical imaging and computer technology. More specifically, this application relates to a method for simulated interventional consumable layer release implemented by a computer, an electronic device, and a computer-readable storage medium. Background Technology

[0002] Currently, interventional vascular surgery has become the mainstream surgical method for treating vascular diseases in clinical practice. For example, endovascular stent implantation is a key means of treating diseases such as vascular stenosis and aneurysms. Precise computer simulation before surgery is of great significance for evaluating stent performance, optimizing surgical plans, and reducing risks. However, existing simulation methods mainly involve directly generating the final shape of the endovascular stent by conforming it to the vessel wall. Although this is efficient, it cannot simulate the actual stent release process in clinical practice. Among related technologies, there are also techniques that simulate the stent release process by generating dynamic stents, but these techniques often consume a lot of time and do not meet the efficiency requirements of clinical practice.

[0003] In view of this, there is an urgent need to provide a computer-implemented simulation scheme for the layered release of interventional consumables, so as to efficiently and accurately simulate the actual release process of interventional consumables such as stents in clinical practice. Summary of the Invention

[0004] In order to at least address one or more of the technical problems mentioned above, this application proposes a method, electronic device, and storage medium for simulating the layered release of interventional consumables in several aspects.

[0005] In a first aspect, this application provides a computer-implemented method for the layered release of simulated interventional consumables, comprising: acquiring a discrete mesh model of the interventional consumable in a blood vessel, wherein the initial state of the discrete mesh model is a compressed state; constructing a position dynamics (PBD) constraint set for the discrete mesh model, wherein the PBD constraint set includes a layered release range and layered release constraints; and performing layered release of the discrete mesh model in the compressed state based on the layered release range and the layered release constraints.

[0006] In some embodiments, constructing a set of constraints based on position dynamics (PBD) for the discrete mesh model includes: determining the hierarchical release range for the discrete mesh model; constructing structural constraints for the discrete mesh model; constructing a first constraint and a second constraint for the released layers in the discrete mesh model; and determining the hierarchical release constraints based on the structural constraints, the first constraint, and the second constraint.

[0007] In some embodiments, the structural constraints include basic distance constraints for maintaining the model topology and environmental interaction constraints for preventing penetration of blood vessels. The first constraints include opposite node distance constraints for maintaining layer compression, circumferential distance constraints for maintaining the layer ring structure, and stability constraints for maintaining layer stability. The second constraints include minimum radius constraints for guiding node release.

[0008] In some embodiments, the discrete mesh model includes a multi-layer structure distributed along the centerline of the blood vessel, and each layer contains uniformly distributed circumferential nodes. The following iterative solution method is used to perform layer release of the discrete mesh model in a compressed state: determine the layer index range of the nodes to be released in the current iteration based on the layer release range; update the attribute identifiers of all nodes in the discrete mesh model based on the layer index range; and execute the constraints on the unreleased layers and released layers in the current iteration based on the attribute identifiers of all nodes and the layer release constraints, until the release of all nodes in the discrete mesh model is completed.

[0009] In some embodiments, updating the attribute identifiers of all nodes in the discrete mesh model according to the layer index range includes: using a first identifier to mark nodes in the discrete mesh model that belong to the layer index range; using a second identifier to mark nodes in the discrete mesh model that do not belong to the layer index range; and updating the first identifier and the second identifier according to the layer index range in response to the end of the current iteration; wherein the first identifier and the second identifier are different identifiers.

[0010] In some embodiments, performing constraints on the unreleased and released layers in this iteration includes: performing the basic distance constraint and the environment interaction constraint on all nodes in the discrete mesh model; performing the minimum radius constraint on nodes with a first identifier; and performing the opposite node distance constraint, the circumferential distance constraint, and the stability constraint on nodes with a second identifier.

[0011] In some embodiments, where all nodes in the discrete mesh model are released layer by layer, the method further includes: obtaining the release result of each release layer; and displaying the release result.

[0012] In some embodiments, obtaining a discrete mesh model of an interventional consumable in a blood vessel includes: obtaining first size information of the blood vessel and second size information of the interventional consumable; and generating the discrete mesh model based on the first size information and the second size information.

[0013] In a second aspect, this application provides an electronic device, comprising: a memory storing computer instructions for tiered release of simulated interventional consumables implemented by a computer; and a processor executing the computer instructions, causing the electronic device to perform the computer-implemented method for tiered release of simulated interventional consumables as described in the preceding and following embodiments.

[0014] In a third aspect, this application provides a computer-readable storage medium including computer-implemented program instructions for the tiered release of simulated interventional consumables, which, when executed by a processor, cause the computer-implemented method for the tiered release of simulated interventional consumables as described in the foregoing and the following embodiments to be implemented.

[0015] Using the computer-implemented method, electronic device, and medium for stratified release of interventional consumables provided above, this application embodiment obtains a discrete mesh model of the interventional consumable in a blood vessel in an initial compressed state, constructs a constraint set based on position dynamics (PBD), and performs stratified release of the compressed discrete mesh model based on the stratified release range and constraints in the constraint set. Therefore, the technical solution of this application cleverly introduces position dynamics (PBD) technology to simulate the stratified release of interventional consumables, thereby accurately and efficiently simulating the actual release process of interventional consumables in clinical practice. Attached Figure Description

[0016] 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:

[0017] Figure 1 A flowchart illustrating a computer-implemented method for the tiered release of interventional consumables, according to an embodiment of this application, is shown. Figure 2 A flowchart illustrating a computer-implemented method for the tiered release of interventional consumables, according to another embodiment of this application, is shown. Figure 3 The diagram illustrates a flowchart of the hierarchical release process of a discrete mesh model in a compressed state, performed in each iteration of an embodiment of this application. Figure 4 A flowchart illustrating a computer-implemented method for the tiered release of simulated interventional consumables, according to another embodiment of this application, is shown. Figure 5 A schematic diagram illustrating the release effect of interventional consumables at different release times according to embodiments of this application; and Figure 6 A schematic block diagram of the structure of an electronic device according to an embodiment of this application is shown. 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] Exemplary application scenarios In related technologies, rapid simulation methods for stent deployment primarily employ the direct generation of intravascular stent morphology. This method mainly uses graphical methods to directly acquire the vascular morphology, directly generating the stent and fitting it to the vessel wall. This method is computationally efficient and suitable for rapidly assessing the final morphology, but it cannot simulate the sequential process of stent deployment through catheters in actual clinical practice. Another method is to simulate the consumable deployment process based on finite element analysis (FEA) technology. This method has very low computational efficiency; generating a dynamic stent often takes tens or even hundreds of hours, failing to meet the clinical need for rapid observation of the dynamic effects of stent deployment.

[0023] To address the problems in the aforementioned scenarios, the inventors discovered that the release process of interventional consumables in clinical practice is gradual. Position-Based Dynamics (PBD) technology, which directly manipulates the position of an object to meet physical constraints, achieves stable and efficient simulation results. This technology can be cleverly and effectively combined with the simulation of interventional consumable release, leveraging the real-time performance and stability of PBD to simulate the release process. Based on this, a computer-implemented scheme for simulating the layered release of interventional consumables is proposed, which can efficiently and accurately simulate the actual release process of interventional consumables such as stents in clinical practice.

[0024] The following combination Figures 1-6 The scheme of this application is described in detail.

[0025] Figure 1 A flowchart illustrating a computer-implemented method 100 for the tiered release of simulated interventional consumables, according to an embodiment of this application, is shown.

[0026] like Figure 1 As shown, in step S101, a discrete mesh model of the interventional consumables in the blood vessel is obtained, wherein the initial state of the discrete mesh model is a compressed state.

[0027] In step S102, a set of constraints based on position dynamics (PBD) is constructed for the aforementioned discrete mesh model. The PBD constraint set includes layered release ranges and layered release constraints.

[0028] In step S103, based on the aforementioned layered release range and layered release constraints, the discrete mesh model in the compressed state is released layer by layer.

[0029] In this application, interventional consumables can be understood as consumables that can be routinely placed in blood vessels to assist in the treatment of diseases, such as flow diversion devices (also known as dense mesh stents). There are no restrictions on the specific type and specifications of these interventional consumables; they can be configured according to application requirements.

[0030] Furthermore, considering that in actual clinical procedures, interventional consumables are first compressed within a catheter and then released into the blood vessel through the catheter, a discrete network model of the consumable in its compressed state is first obtained to realistically simulate the release process. This discrete network model is a network structure composed of nodes and connections, created using a discretization technique, supporting the simulation of the dynamic behavior of the interventional consumable. In specific implementation scenarios, once the discrete mesh model is obtained, the positions of the nodes within it can be determined for effective integration with PBD (Programmable Node Difference) technology in subsequent steps.

[0031] Next, a constraint set for the PBD of the aforementioned discrete mesh model can be constructed. The constraint set can be understood as a set of mathematical conditions used to describe and restrict the behavior of nodes in the discrete mesh model. The constraints in the constraint set can directly act on the positions of nodes in the discrete mesh model to ensure that the discrete mesh model meets the set conditions. In this embodiment, the constraint set specifically includes layered release ranges and layered release constraints. Both the layered release range and the layered release constraints can be set and adjusted according to application requirements. For example, the layered release range can be set to release layer by layer or locally, releasing one layer at a time. Alternatively, it can be set to release multiple layers at once, or even limited to releasing only specified layers, depending on simulation requirements. The layered release constraints can be understood as the specific conditions in the constraint set.

[0032] After creating the constraint set of the PBD, the layered release range and layered release constraints in the PBD constraint set can be used to perform layered release on the discrete mesh model in a compressed state. Specifically, the layered release range can be used to determine the release layers and unreleased layers, and layered release constraints can be applied to these release layers and unreleased layers to achieve the simulation effect of layered release of the discrete mesh model.

[0033] Therefore, unlike traditional force-based dynamics and other technologies used to simulate the release effect of interventional consumables, the technical solution of this application cleverly introduces PBD technology and combines it with the discrete mesh model of interventional consumables. This skips the traditional integration process of "force → acceleration → velocity → position" and can directly act on the nodes in the discrete mesh model so that the discrete mesh model satisfies the conditions in the constraint set, thereby greatly improving the simulation efficiency. At the same time, by performing layered release of the discrete mesh model, the actual release process of interventional consumables in clinical practice can be accurately simulated.

[0034] Figure 2 A flowchart illustrating another embodiment of this application's computer-implemented method 200 for the layered release of simulated interventional consumables is shown. It should be noted that... Figure 2 Method 200 in the middle can be understood as a... Figure 1 Further limitations or extensions of Chinese method 100. Therefore, the preceding text, combined with... Figure 1 The relevant descriptions also apply to the following text.

[0035] like Figure 2 As shown, in step S201, the first size information of the blood vessel and the second size information of the interventional consumable can be obtained. In this embodiment, the size information of the blood vessel can be understood as the size information of the blood vessel to which the interventional consumable is to be implanted. For example, the first size information may specifically include the centerline path or centerline trajectory of the blood vessel. In some specific implementation scenarios, a three-dimensional spatial curve composed of a series of ordered three-dimensional point sets can be used to represent the centerline path or centerline trajectory of the blood vessel. The second size information of the interventional consumable may include parameters such as length, diameter, and radius. In this embodiment, the diameter and radius can be understood as the diameter and radius of the stent in the microcatheter under compression. It should be noted that these descriptions of the first and second size information are merely illustrative, and these size information can be preset according to application requirements.

[0036] In step S202, a discrete mesh model can be generated based on the aforementioned first and second size information.

[0037] As mentioned earlier, the first dimension information may include a three-dimensional spatial curve composed of a series of ordered three-dimensional point sets, which can represent the centerline path or trajectory of the blood vessel. The second dimension information may include the length and radius of the stent. The compressed discrete mesh model may specifically include multiple layers of nodes, with each layer containing uniformly distributed circumferential nodes. In some specific implementation scenarios, the points in the three-dimensional point set can be accumulated to obtain the arc length from the starting point to each point, thus obtaining the total length of the centerline. Next, the average interlayer spacing of the compressed discrete mesh model can be obtained, and the center point of each layer can be determined using the centerline and the average interlayer spacing. For example, starting from the endpoint (starting point) of the centerline, multiple points can be sampled along the arc length at the average interlayer spacing as the center point of each layer, ensuring that the generated mesh is uniformly distributed along the centerline. Then, for each layer center point, a local coordinate system needs to be established to arrange circumferential nodes on its cross-section. Next, the tangent direction of the centerline at each layer center point is determined, and the normal and binormal of the centerline at each layer center point are calculated. The normal vector refers to the direction of the center of curvature at that point, perpendicular to the tangent vector. Then, node coordinates are generated, and the x-axis in the local coordinate system is defined as the normal direction at that point. Next, the node coordinates in the local coordinate system are converted to global coordinates. Finally, the resulting discrete mesh model consists of multiple layers of nodes distributed along the centerline, with each layer containing multiple nodes evenly distributed along the circumference. The global coordinates of each node need to be saved to provide reference geometric information for subsequent layer-by-layer release control.

[0038] In step S203, the layer-by-layer release range for the discrete mesh model is determined. In some embodiments, the layer-by-layer release range can be preset and adjusted according to application requirements. For example, it can be set to release layer by layer, releasing one layer at a time, or releasing multiple layers at once. It can also be set to local release, for example, limiting the release to only specified layers. In specific applications, layer-by-layer release, releasing one layer at a time, is preferred.

[0039] In step S204, structural constraints, first constraints on unreleased layers in the discrete mesh model, and second constraints on released layers can be constructed, and layered release constraints can be determined. After determining the layered release range, structural constraints on the discrete mesh model, first constraints on unreleased layers in the discrete mesh model, and second constraints on released layers can be constructed, and layered release constraints can be determined based on structural constraints, first constraints, and second constraints. In some examples, structural constraints include basic distance constraints for maintaining the model topology and environmental interaction constraints for preventing penetration of blood vessels. The first constraints include opposite node distance constraints for maintaining layer compression, circumferential distance constraints for maintaining the layer ring structure, and stability constraints for maintaining layer stability. The second constraints include minimum radius constraints for guiding node release.

[0040] At step S205, the layered release of the discrete mesh model in the compressed state can be performed by using a cyclic iterative solution method based on the division into release ranges and layered release constraints.

[0041] As an example Figure 3 This illustration shows a flowchart of an embodiment of the present application, illustrating the hierarchical release process 300 of a discrete mesh model in a compressed state during each iteration. Figure 3 In this context, the discrete mesh model specifically includes a multi-layer structure distributed along the centerline of the blood vessel, with each layer containing uniformly distributed circumferential nodes.

[0042] Specifically, the layered release process 300 includes performing the layered release of the discrete mesh model in a compressed state using the following iterative solution method: In step S301, the layer index range of the nodes to be released in this iteration is determined according to the layer release range. For example, each time one layer is released, that is, the layer index range of the layer to be released is [r, r+1), r≥0.

[0043] At step S302, the attribute identifiers of all nodes in the discrete mesh model are updated according to the layer index range. For example, different identifiers can be used to mark the attribute identifiers of these nodes. In some embodiments, a first identifier is used to mark nodes in the discrete mesh model that belong to the layer index range; a second identifier is used to mark nodes in the discrete mesh model that do not belong to the layer index range; in response to the end of this iteration, the first identifier and the second identifier are updated according to the layer index range; wherein the first identifier and the second identifier are different identifiers.

[0044] At step S303, based on the attribute identifiers of all nodes and the layered release constraints, the constraints on the unreleased and released layers in this iteration are executed until all nodes in the discrete mesh model are released. After completing one iteration, steps S301 to S303 are executed again until all nodes in the discrete mesh model are released.

[0045] In some embodiments, the process of constraining the unreleased and released layers in each iteration specifically includes: applying the aforementioned basic distance constraints and environmental interaction constraints to all nodes in the discrete mesh model; applying minimum radius constraints to nodes with a first identifier; and applying opposite node distance constraints, circumferential distance constraints, and stability constraints to nodes with a second identifier. The basic distance constraints are general structural constraints used to maintain the overall topology of the stent mesh and prevent distortion. Environmental interaction constraints are used to handle the contact between nodes and the vessel wall to prevent penetration. For example, a one-sided collision constraint can be used; during iteration, the distance between the node and the vessel arm is not calculated, and if the distance is less than a predetermined value, the node is fixed. The minimum radius constraint is used to guide and restrict the outward expansion of nodes with the first identifier and their eventual attachment to the vessel wall. For example, the minimum radius constraint can be applied to the layer to which the node with the first identifier belongs, i.e., applying a radial force from the center of the layer outward to drive its expansion, so that the layer is eventually released to the target radius value. The target radius value is the radius of the blood vessel.

[0046] The contralateral node distance constraint primarily constrains the distance between two opposite nodes along the diameter within the same layer, ensuring that the distance is the same as the distance between contralateral nodes when the stent is in the microcatheter under compression, thus maintaining the compressed diameter of the layer. The circumferential distance constraint primarily constrains the distance between two adjacent nodes along the circumference within the same layer, ensuring that the distance is the same as the distance between circumferential nodes when the stent is in the microcatheter under compression, thus maintaining the integrity of the layer's annular structure. The stability constraint is primarily designed to enhance the overall stability of the unreleased portion in long stent simulations, preventing overall translational or rotational drift due to uneven stress. This constraint is applied to all unreleased layers (e.g., unreleased layers starting from layer index "r+2"). This constraint calculates the current geometric center point of each unreleased layer and, through projection, ensures that the centerline of the unreleased layer coincides with the initial vascular centerline mentioned earlier, thereby guaranteeing that the unreleased segment remains stable along the predetermined delivery path.

[0047] In some embodiments, a minimum radius constraint may also be applied to nodes with a second identifier. However, this minimum radius constraint is intended to preserve the initial compression radius (i.e., the radius of the scaffold in the microcatheter under compression) of the layer to which the node with the second identifier belongs, preventing the layer from accidentally expanding during simulation and ensuring that it maintains its compression ring shape. In other words, for nodes with a second identifier, the use of "radial forces" that cause them to expand outward is prohibited.

[0048] In this example, during the layered release process of a discrete mesh model in a compressed state, the nodes in the discrete mesh model are divided into released layers and unreleased layers, and different constraints are applied to the released layers and unreleased layers, thereby accurately simulating the layer-by-layer release sequence of interventional consumables.

[0049] Figure 4 This illustration shows a flowchart of a computer-implemented method 400 for the tiered release of simulated interventional consumables, according to another embodiment of this application. It should be noted that... Figure 4 Method 400 in the middle can be understood as... Figure 1 Chinese method 100 and Figure 2 This is a specific implementation of Chinese method 200. Therefore, the preceding text combines... Figure 1 and Figure 2 The relevant descriptions also apply to the following text. This embodiment uses a stent as an interventional consumable.

[0050] In step S401, a stent node in the vascular compression state is constructed. This compressed stent node can be understood as the discrete mesh model in a compressed state mentioned earlier. In some embodiments, a discrete mesh model of the stent in its initial compressed state can be generated based on the centerline path of the blood vessel and preset stent length and diameter parameters. The specific calculation process is as follows: (1) Use a three-dimensional spatial curve to represent the central trajectory of the blood vessel. This is usually represented by an ordered set of three-dimensional points E={e1,e2,e3,...,e...}. M}

[0051] (2) A pre-set compression bracket with a bracket length of L stent The diameter of the compressed microcatheter is D. comp Its radius R comp =D comp / 2.

[0052] (3) The compression support is set to have L layers of nodes, and the circumferential nodes of each layer are C.

[0053] (4) Accumulate the three-dimensional point set to obtain the arc length from the starting point to each point, thus obtaining the total length of the centerline. The accumulation formula is: .

[0054] (5) Calculate the average interlayer spacing Δs=L of the compression stent. stent / (L-1), where l =1,2,3,...,L.

[0055] (6) Starting from the endpoint of the centerline, sample L points along the arc length at intervals Δs, and use them as the center point P of each grid layer. l )={p0,p1,p2,...p L-1 This ensures that the generated mesh is uniformly distributed along the centerline.

[0056] (7) Use the Frenet frame to establish a local coordinate system at the center point P( l To achieve this, a local coordinate system needs to be established so that the circumferential nodes can be arranged on its cross-section.

[0057] (8) The centerline is at point P( l The tangent direction at point () can be calculated and normalized using the centerline difference to obtain the following formula, where k represents the distance. l The nearest sampling point:

[0058] (9) Calculate the normal N and binormal B of the centerline at point P, where the normal N refers to the direction of the center of curvature at that point, perpendicular to the tangent vector:

[0059]

[0060] (10) Calculate the binormal line B: .

[0061] (11) Generate node coordinates. The angle of the c-th node (c=0,1,2,...C-1) on the circumference is... θ c =2πc / C. The x-axis in the local coordinate system is defined as the normal direction of this point. The coordinates of this node in the local coordinate system are:

[0062] (12) Transform the coordinates of the nodes in the local coordinate system into coordinates in the global coordinate system:

[0063] Ultimately, the discrete mesh model consists of L layers of nodes distributed along the centerline, with each layer containing C nodes evenly distributed along the circumference. The steps described above calculated and saved the global coordinates of each node. This step provides reference geometric information for subsequent layered control. Furthermore, after obtaining the global coordinates of each node, the distances to opposite nodes and circumferential nodes under the initial compression state can be further calculated.

[0064] return Figure 4 In step S402, PBD is used to create corresponding constraints for the released and unreleased layers.

[0065] At step S403, iterative release is performed, and the constraints of the released and unreleased layers are gradually applied to the corresponding support nodes.

[0066] At step S404, the result of the PBD loop iteration is output.

[0067] In some embodiments, a sequential, cyclical release strategy can be employed. A released layer counter `r` is set, initially set to 0, indicating that no layers have been released yet. The main loop is then entered, and when `r` is less than the total number of layers `L`, the following sub-steps are executed: First, the release range is determined by setting the range of layer indices to be released in this iteration. In a preferred embodiment, one layer is released at a time, i.e., the range of layers to be released is [r, r+1).

[0068] Next, the layered mechanics switch (radial force mask) is updated: based on the current range of the layers to be released, the mechanical properties of each node are updated. For all nodes within the range of the layers to be released, their "radial force application flag" is set to True (i.e., the first flag mentioned earlier); for all nodes not within this range (i.e., not yet released), their "radial force application flag" is set to False (i.e., the second flag mentioned earlier). This operation achieves a fundamental distinction in mechanical behavior: released layers will be subjected to an outward radial expansion force, while unreleased layers will not be affected by this force, thus maintaining compression.

[0069] Next, the hierarchical constraint system is constructed and solved: based on the current radial force application flag state (i.e., released / unreleased state) of all nodes, the PBD constraint set for this iteration step is dynamically assembled, and one round of PBD iteration is performed. The constraint set includes: General structural constraints: Basic distance constraints applicable to all nodes, used to maintain the overall topology of the support mesh and prevent distortion.

[0070] Layered minimum radius constraint: For nodes with a valid "radial force application flag" (released layer), the target radius value of the minimum radius constraint applied to its layer is set to the radius of the blood vessel, used to guide and restrict the outward expansion of the layer and its eventual attachment to the blood vessel wall. For nodes with an invalid "radial force application flag" (unreleased layer), the target radius value of the minimum radius constraint applied to its layer is set to the initial compression radius (R) saved by the layer in step (1). comp =D comp / 2), used to prevent the layer from accidentally expanding during simulation and to ensure that it maintains the compression ring shape.

[0071] Unreleased layer shape preservation constraint: Geometric constraints specifically applied to nodes (unreleased layers) where the "radial force application flag" is invalid, including: Opposite node distance constraint: constrain the distance between two opposite nodes along the diameter direction in the same layer, so that its target value is maintained as the opposite node distance in the initial compression state calculated in step (12), so as to maintain the compression diameter of the layer.

[0072] Circumferential distance constraint: constrain the distance between two adjacent nodes in the same layer in the circumferential direction, so that its target value is kept as the circumferential node distance in the initial compressed state calculated in step (12), so as to maintain the integrity of the ring structure of the layer.

[0073] Stability constraint of unreleased segment (centerline constraint of layer center point): To enhance the overall stability of the unreleased portion in long stent simulation and prevent overall translational or rotational drift due to uneven stress, this constraint is applied to all unreleased layers starting from index r+2. This constraint calculates the current geometric center point of each unreleased layer and, through projection, ensures that the centerline of the unreleased layer coincides with the initial vascular centerline defined in steps (1) to (12), thereby guaranteeing that the unreleased layer remains stable along the predetermined delivery path. The projection method is as follows: First, for each unreleased layer center point P(l), find its closest point P on the center line. l target ,Right now:

[0074] Next, let the arc length corresponding to P(l) be s. In the arc length sequence {sk}, find the interval [sk, sk+1] such that sk ≤ s ≤ sk+1, then:

[0075]

[0076] Then, enforce constraints: .

[0077] Environmental interaction constraints: One-sided collision constraints are used, meaning that during iteration, the distance between the stent node and the vessel wall is continuously calculated. If the distance is less than a predetermined value (e.g., 0.03), the stent node is fixed. This constraint is used to handle the contact between the stent and the vessel wall and prevent penetration.

[0078] Update state and output: After completing the PBD iterative solution of the above steps, mark the layer to be released as released, that is, update r = r + 1. At this time, the position coordinates of all nodes can be saved.

[0079] In some embodiments, all nodes in the discrete mesh model described above are released layer by layer, and the release result of each released layer can be obtained and displayed. The specific release effect is as follows: Figure 5 As shown, assuming the discrete grid model has a 6-layer structure, and the release time of each layer is t1~t6 as shown in the figure, the release results of the first release layer at the corresponding release time can be obtained and displayed.

[0080] As can be seen, the solution proposed in this application aims to distinguish the behavior of released and unreleased layers within the PBD solution framework through a clear mechanical and constraint layering strategy: applying radial force to the released layers and guiding them to adhere to the vessel wall, while imposing a series of geometric constraints on the unreleased layers to maintain their compressed shape, thereby accurately simulating the layer-by-layer release sequence of the stent and outputting the intermediate state results of each release step. Furthermore, the core of this technical solution lies in: within the PBD framework, clearly distinguishing the mechanical behavior of released and unreleased layers through the combination of layered radial force switching and layered constraints. Specifically, this involves: Initial stent generation: generating a stent mesh model in the initial compressed state based on the vessel centerline, target vessel radius, stent length, and diameter. This model has a fixed number of layers L and the number of circumferential nodes C per layer. A cyclical approach is adopted, releasing one layer (or several configurable layers) at a time, starting from layer 0 and releasing sequentially until all layers are released. After each layer is released, the release of the next layer begins. The mechanical and constraint distinction between released and unreleased layers: For released layers, a radial force pointing outward from the layer center is activated and applied to drive their deployment; simultaneously, a "minimum radius constraint" with a target radius equal to the vessel radius is applied to prevent over-deployment and guide their adhesion to the vessel wall. For unreleased layers, the radial force is disabled. To maintain their compression ring morphology, a set of composite constraints is applied, including "contralateral node distance constraints" (maintaining the compression diameter), "circumferential distance constraints" (maintaining the ring structure), and a "minimum radius constraint" with a target value equal to the initial compression radius of the layer. Furthermore, to enhance the stability of long stent simulations, an additional "layer centerline constraint" is applied to unreleased layers beyond "released layers + 2" to ensure they do not deviate from the original delivery path. All of the above constraints, along with general structural constraints (such as basic distance constraints and collision constraints), are integrated into a unified PBD constraint list for iterative projection solving.

[0081] Therefore, by cleverly introducing PBD technology and combining it with the discrete mesh model of interventional consumables, the traditional integration process of "force → acceleration → velocity → position" is skipped. It can directly act on the nodes in the discrete mesh model so that the discrete mesh model satisfies the conditions in the constraint set, thereby greatly improving the simulation efficiency. At the same time, by releasing the discrete mesh model in layers, the actual release process of interventional consumables in clinical practice can be accurately simulated.

[0082] After introducing the methods of exemplary embodiments of this application, the following references are made. Figure 6 This application describes related products of a computer-implemented method for tiered release of simulated interventional consumables, based on exemplary embodiments of this application.

[0083] Figure 6 A schematic block diagram of an electronic device 600 according to one embodiment of this application is shown. Specifically, as follows... Figure 6As shown, the electronic device 600 may include a processor 601 and a memory 602. The memory 602 stores computer instructions for the simulated layered release of interventional consumables, implemented by a computer. When the computer instructions are executed by the processor 601, the electronic device 600 performs the following actions: acquiring a discrete mesh model of the interventional consumable in the blood vessel, wherein the initial state of the discrete mesh model is a compressed state; constructing a set of constraints based on position dynamics (PBD) for the discrete mesh model, wherein the set of constraints based on position dynamics (PBD) includes a layered release range and layered release constraints; and performing layered release of the compressed discrete mesh model based on the layered release range and the layered release constraints.

[0084] Through the above implementation methods, the electronic device can efficiently and accurately simulate the actual release process of interventional consumables in clinical practice.

[0085] It should be noted that the specific details of the operating method and steps of this electronic device are combined with the foregoing. Figures 1-4 The specific implementation methods described are the same or similar, so they will not be elaborated here.

[0086] Furthermore, this application also provides a computer-readable storage medium storing program instructions configured to execute at runtime. Figures 1-4 The method shown is a computer-implemented simulation-based method for the tiered release of consumables.

[0087] Specifically, in this embodiment, the storage medium may include, but is not limited to, USB flash drives, read-only memory (ROM), random access memory (RAM), portable hard drives, magnetic disks, or optical disks, and other media capable of storing computer programs.

[0088] 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 computer-implemented method for tiered release of consumables through simulation, characterized in that, include: Obtain a discrete mesh model of interventional consumables in blood vessels, wherein the initial state of the discrete mesh model is a compressed state; Construct a set of constraints based on position dynamics (PBD) for the discrete mesh model, wherein the set of constraints based on position dynamics (PBD) includes layered release ranges and layered release constraints; as well as Based on the layered release range and the layered release constraints, the discrete mesh model in the compressed state is released in layers.

2. The method according to claim 1, characterized in that, The set of constraints based on position dynamics (PBD) for the discrete mesh model includes: Determine the hierarchical release range for the discrete mesh model; Construct structural constraints for the discrete mesh model; Construct a first constraint on the unreleased layers and a second constraint on the released layers in the discrete mesh model; and Based on the structural constraints, the first constraint, and the second constraint, the hierarchical release constraint is determined.

3. The method according to claim 2, characterized in that, The structural constraints include basic distance constraints for maintaining the model topology and environmental interaction constraints for preventing penetration of blood vessels. The first constraints include opposite node distance constraints for maintaining layer compression, circumferential distance constraints for maintaining the layer ring structure, and stability constraints for maintaining layer stability. The second constraints include minimum radius constraints for guiding node release.

4. The method according to claim 3, characterized in that, The discrete mesh model comprises a multi-layered structure distributed along the centerline of the blood vessel, with each layer containing uniformly distributed circumferential nodes. The following iterative solution method is used to perform layer-by-layer release of the discrete mesh model in a compressed state: The layer index range of the nodes to be released in this iteration is determined based on the layer release range. Update the attribute identifiers of all nodes in the discrete mesh model according to the layer index range; as well as Based on the attribute identifiers of all nodes and the hierarchical release constraints, the constraints on the unreleased and released layers in this iteration are executed until the release of all nodes in the discrete mesh model is completed.

5. The method according to claim 4, characterized in that, Updating the attribute identifiers of all nodes in the discrete mesh model based on the layer index range includes: The first identifier is used to mark the nodes in the discrete mesh model that belong to the range of the layer index; A second identifier is used to mark nodes in the discrete mesh model that do not belong to the range of the layer index; In response to the end of this iteration, the first identifier and the second identifier are updated according to the layer index range; The first identifier and the second identifier are different identifiers.

6. The method according to claim 5, characterized in that, The constraints on unreleased and released layers in this iteration include: The basic distance constraint and the environmental interaction constraint are applied to all nodes in the discrete mesh model. The minimum radius constraint is applied to the node with the first identifier; and The opposite node distance constraint, the circumferential distance constraint, and the stability constraint are applied to the node with the second identifier.

7. The method according to claim 4, characterized in that, The method further includes the following: all nodes in the discrete mesh model are released layer by layer. Obtain the release result of each release layer; and The release results are then displayed.

8. The method according to any one of claims 1 to 7, characterized in that, Obtaining a discrete mesh model of interventional consumables in blood vessels includes: Obtain the first size information of the blood vessel and the second size information of the interventional consumables; and The discrete mesh model is generated based on the first size information and the second size information.

9. An electronic device, characterized in that, include: The memory stores computer instructions for the simulated release of tiered consumables, implemented by a computer. A processor that executes the computer instructions to cause the electronic device to perform the computer-implemented method for tiered release of simulated interventional consumables according to any one of claims 1 to 8.

10. A computer-readable storage medium, characterized in that, It includes program instructions for computer-implemented tiered release of simulated interventional consumables, which, when executed by a processor, cause the computer-implemented method for tiered release of simulated interventional consumables according to any one of claims 1 to 8 to be implemented.

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