Cardiac ultrasound visualization method

Abstract

A method for visualizing a heart valve and blood flow through the heart valve for the purpose of assessing valve backflow. A visualization is generated based on both the 3D B-mode data and the 3D Doppler data. The visualization includes generating a combined drawing of each of a heart valve structure, an upstream confluence region, and an output jet region. Drawing parameters applied in drawing each of these structures may preferably be independently adjustable to allow tuning of the visualization. The rendering may be performed by a render operable to render both the raster data and the grid data.

Description

Technical Field

[0001] The present invention relates to a method for visualizing cardiac ultrasound data (e.g., cardiac ultrasound data representing the heart valve region). Background Technology

[0002] Cardiac ultrasound imaging is used for a range of different diagnostic purposes.

[0003] One example application is for analyzing blood flow through heart valves (e.g., aortic, mitral, tricuspid, pulmonary valves). For imaging the blood flow itself, the most common mode of ultrasound imaging is color flow Doppler imaging. This is advantageous because it is relatively inexpensive and requires relatively little space (e.g., compared to alternatives such as MRI).

[0004] To image the valves, 3D ultrasound imaging can be used to generate 3D B-mode images. 3D Doppler color images of blood flow can be obtained, thereby creating a holistic image depicting the heart's structure, which is filled with information about the flow within the cavities and through the valves between them. Dedicated flow models exist in the prior art to enable the quantification of leakage through the mitral valve in the presence of backflow during systole.

[0005] However, existing ultrasound visualization techniques have weaknesses in the context of reflux analysis.

[0006] One challenge is to accurately and completely obtain the 3D topology of the heart valves from the acquired 3D B-mode data. This can be due to insufficient image size relative to image resolution, or poor echo return due to the valves being oriented perpendicular to the ultrasound beam.

[0007] Even when there is no loss of valve signal in the B-mode data, tuning the visualization parameters used to draw 2D images from 3D data is not a simple task. If the parameters are too strong, the image may show the presence of phantom pores that are not present in the real anatomy, while if the parameters are too weak, existing pores may be missed.

[0008] Ideal visualization of 3D ultrasound data would include a topological and physical representation of valves, blood flow, and preferably ventricular and atrial structures. Such visualization allows clinicians to accurately assess valves within the complete anatomical context. More specifically, ideal visualization would allow for the representation of several of the following:

[0009] The topology and location of the valves;

[0010] The shape, size, and location of each opening in the valve;

[0011] The interaction between blood flow and valves;

[0012] The convergence of blood flow at the entrance of the valve's orifice;

[0013] Afferent blood flow through the valve openings;

[0014] Outflow jet in the atrium due to reflux.

[0015] Existing visualization tools can enable the visualization of one selected aspect of these aspects, but not multiple aspects, and not all aspects together. Summary of the Invention

[0016] This invention is defined by the claims.

[0017] According to one aspect of the invention, a method for visualizing heart valves using ultrasound data is provided. Another aspect provides a processing apparatus configured to perform said method. Yet another aspect provides a computer program product including computer program code configured to cause the processor to perform said method when run on a processor.

[0018] The method includes receiving 3D B-mode ultrasound data of a cardiac region containing cardiac valve structures.

[0019] The method also includes receiving 3D Doppler ultrasound data of the cardiac region.

[0020] The method also includes generating 2D images based on B-mode data and Doppler data.

[0021] Generating 2D images involves applying image rendering.

[0022] Image rendering can be used to derive combined renderings of: the heart valve structures in the heart region, the output jets emitted from the heart valves, and / or the upstream converging flow region upstream of the valves. This can be, for example, a region containing at least an isokinetic surface of blood flow.

[0023] In a preferred embodiment, the combined drawing may also include visualization of at least a portion of the structure of one or more cardiac chambers (preferably atria and / or ventricles).

[0024] The method may include deriving a 3D raster of the heart valve structure from 3D B-mode image data.

[0025] The method may include exporting a 3D mesh of the output jet using 3D Doppler ultrasound data and / or exporting a 3D raster of the output jet using 3D Doppler ultrasound data. The method may also include exporting a 3D mesh of the upstream confluence region using 3D Doppler ultrasound data and / or exporting a 3D raster of the upstream confluence region using 3D Doppler ultrasound data.

[0026] Image rendering can include applying image rendering to: a 3D grid of the heart valve structure, a 3D mesh or 3D grid of the output jet, and a 3D mesh or 3D grid of the upstream (confluence) region to generate a 2D image.

[0027] Generating 2D images may include identifying heart valve structures in B-mode and / or Doppler data. Generating 2D images may include identifying the output jet region in B-mode and / or Doppler data. Generating 2D images may include identifying the upstream confluence region in B-mode and / or Doppler data.

[0028] For example, generating a 2D image may include: identifying a 3D region of B-mode data occupied by the heart valve structure, thereby producing a 3D raster representation of the heart valve. Generating a 2D image may also include: identifying an output jet region within the heart region containing the fluid jet exiting from the heart valve. This may be based on processing at least Doppler ultrasound data. It may also be based on processing 3D B-mode data. Generating a 2D image may further include identifying an upstream confluence region within the heart region, wherein the upstream confluence region is a region containing at least an isovelocity surface of blood flow. This may be based on processing at least Doppler ultrasound data. It may also be based on processing 3D B-mode data.

[0029] The method may include: performing a rendering process to render a 2D image, the 2D image including visualizations of each of the heart valve structure, the output jet region, and the upstream confluence region.

[0030] The drawing process may include drawing the 3D raster representation applied to the heart valve to achieve 2D visualization of the heart valve structure in the 2D image.

[0031] According to an embodiment of the present invention, a combination of 3D B-mode data and 3D Doppler data is proposed to create a 2D visualization of the valve and surrounding area.

[0032] Furthermore, in at least one set of embodiments, the valve is rendered by applying volumetric rendering to a 3D raster of the B-mode echo data (rather than to a grid segmented from the echo data). This means that the rendering of the heart valve region takes into account internal structural information and, advantageously, allows for additional degrees of freedom in configuring the visual properties of the rendering by adjusting the voxel transparency transfer function in the volumetric rendering of the 3D raster. This is not an option when rendering a grid. This advantageously allows for optimizing the visibility of the most relevant structural elements of the heart valve structure, as well as optimizing the relative visibility of the valve and the flow. For example, this allows for better alignment between the jet and the orifice.

[0033] 3D raster means (3D) voxel dataset. 3D raster (or voxel dataset) is distinguished from other types of 3D image representations, such as 3D vector images, or 3D meshes or other types of 3D segmentation.

[0034] The method may include: independently adjusting one or more drawing parameters applied when drawing each of the heart valve structure, the output jet region, and the upstream confluence region.

[0035] This allows for improved visualization by enabling independently tunable plotting of each element in the valve, refluxing jet, and confluence regions via independently tunable visualization parameters. This allows for optimization of the visibility of different elements of the valve and flow.

[0036] In the existing technology, there is no known simple way to visualize 3D echo and color Doppler data to provide a clear representation of any mitral regurgitation that may be present. This is true for both TTE and TEE imaging. However, distinguishing and identifying these components during the regurgitation process is fundamental to diagnosis.

[0037] In some embodiments, one or more rendering parameters may include at least the relative transparency level of each of the heart valve structures, the output jet region, and the upstream confluence region in the final generated image.

[0038] In some embodiments, the one or more drawing parameters may include one or more of the following: transparency, smoothness, color, and / or fading applied to each of the heart valve structure, the output jet region, and the upstream confluence region.

[0039] The rendering of one or more of the heart valve structure, the output jet region, and the upstream confluence region may include applying a rendering transfer function to the ultrasound data. In some embodiments, one or more rendering parameters may include one or more parameters of the rendering transfer function. For example, it may include parameters of the rendering transfer function used to derive a 3D raster of the heart valve structure.

[0040] In some embodiments, adjusting the one or more drawing parameters may include: receiving user input from a user interface indicating settings for at least one of the one or more drawing parameters, and adjusting the at least one drawing parameter based on the user input. Alternatively, the adjustment may be performed automatically.

[0041] In some embodiments, drawing the heart valve structure may include applying a transfer function to voxels of a raster representation of the heart valve, wherein the transfer function defines one or more visualization properties, such as transparency levels, for each voxel of the raster as a function of voxel values. One or more drawing parameters include one or more parameters of the transfer function. For example, one or more drawing parameters may include a threshold level or value of the transfer function. For example, the threshold level or value may define voxel values ​​above which raster-represented voxels are included in the drawing, and below which raster-represented voxels are not included in the drawing; that is, below which the voxel value, the voxel transparency is 100%, and above which the voxel value, the voxel transparency is less than 100%.

[0042] In some embodiments, identifying the output jet region may include segmenting the output jet region in the Doppler ultrasound data. Mapping the output jet region may include generating a 3D mesh based on the segmentation to create a contour of the output jet region, and applying volumetric rendering to the mesh.

[0043] Instead of generating a 3D mesh, in some embodiments, the rendering of the output jet region includes applying volume rendering to a 3D raster representation of the output jet region within the Doppler data.

[0044] In some embodiments, identifying the upstream confluence region includes segmenting the upstream confluence region in the Doppler data. Drawing the upstream confluence region may include generating a 3D mesh of the upstream confluence region based on the segmentation, and applying volumetric drawing to the mesh.

[0045] Instead of generating a 3D mesh, in some embodiments, drawing the upstream confluence region includes applying volumetric drawing to a 3D raster representation of the upstream confluence region within the Doppler data.

[0046] In some embodiments, identifying a 3D region of B-mode data occupied by heart valve structures includes segmenting the heart valve structures in the B-mode data.

[0047] In some embodiments, identifying a 3D region of B-mode data occupied by a heart valve structure includes calculating a 3D mask based on segmentation, the 3D mask distinguishing the 3D region occupied by the heart valve structure from the background region.

[0048] In some embodiments, the identification of the output jet region and the upstream confluence region includes applying a flow dynamics model to Doppler ultrasound data. The flow dynamics model may be adapted to determine the isokinetic surface of blood flow upstream of the heart valve. The flow dynamics model may be adapted to determine the blood flow path through the valve. The flow dynamics model may be adapted to determine the output jet from the valve.

[0049] The velocity surface can be a near-side isovelocity surface region (PISA).

[0050] An example flow dynamics model suitable for this purpose is described in detail in document WO 2023 / 020920 A1.

[0051] Another aspect of the present invention provides a processing apparatus comprising one or more processors configured to: receive: 3D B-mode ultrasound data of a cardiac region including cardiac valve structures, and receive 3D Doppler ultrasound data of the cardiac region; identify a 3D region of the B-mode data occupied by the cardiac valve structures to generate a 3D raster representation of the cardiac valves; identify an output jet region within the cardiac region containing a fluid jet exiting from the cardiac valves based on processing of at least the Doppler ultrasound data; identify an upstream confluence region within the cardiac region based on processing of at least the Doppler ultrasound data, wherein the upstream confluence region is a region containing at least an isokinetic surface of blood flow; and perform a rendering process to render a 2D image including visualizations of each of the cardiac valve structures, the output jet region, and the upstream confluence region.

[0052] The rendering process may include applying rendering to a 3D raster representation of the heart valve to produce a 2D visualization of the heart valve structure in a 2D image.

[0053] In some embodiments, the processing device may also be configured to independently adjust one or more rendering parameters applied when rendering each of the heart valve structure, the output jet region, and the upstream confluence region. The one or more parameters may include the level of transparency applied to each of the heart valve structure, the output jet region, and the upstream confluence region.

[0054] The processing device may include a receiving module for receiving 3D B-mode ultrasound data and 3D Doppler ultrasound data. The processing device may include a 3D rendering module for performing identification steps and rendering processes. The processing device may include a rendering adjustment module for independently adjusting one or more rendering parameters.

[0055] Another aspect of the present invention is a system comprising: a processing device according to any example or embodiment of this disclosure or according to any claim of this application; and an ultrasonic acquisition device operable to acquire 3D B-mode data and 3D Doppler data.

[0056] These and other aspects of the invention will become apparent from the embodiments described below and will be set forth with reference to the embodiments described below. Attached Figure Description

[0057] To better understand the invention and to more clearly illustrate how the invention can be implemented, reference will now be made to the accompanying drawings by way of example only, in which:

[0058] Figure 1 The steps of an example method according to one or more embodiments of the present invention are summarized;

[0059] Figure 2 This is a block diagram of an example processing device and system according to one or more embodiments of the present invention;

[0060] Figure 3 and Figure 4 The illustration shows a sample drawing of the mitral valve, the upstream confluence region, and the outflow jet region;

[0061] Figure 5 and Figure 6 The illustration shows another example of the mitral valve, the upstream confluence region, and the outflow jet region;

[0062] Figure 7 The illustration shows the processing flow of an example method according to a set of embodiments of the present invention;

[0063] Figure 8 The diagram illustrates the adjustment of the transparency parameter when drawing the valve structure;

[0064] Figure 9 The diagram illustrates the adjustment of the smoothness parameter for drawing the valve structure;

[0065] Figure 10 The diagram illustrates the adjustment of the fade parameters for plotting the valve structure;

[0066] Figure 11 The diagram illustrates the adjustment of thresholding parameters for plotting the valve structure; and

[0067] Figure 12 The illustration shows an example drawing of a cross-sectional plane through the valve structure. Detailed Implementation

[0068] The invention will be described with reference to the accompanying drawings.

[0069] It should be understood that while the detailed description and specific examples indicate exemplary embodiments of the apparatus, system, and method, they are intended for illustrative purposes only and are not intended to limit the scope of the invention. These and other features, aspects, and advantages of the apparatus, system, and method of the present invention will be better understood from the following description, the appended claims, and the accompanying drawings. It should be understood that the drawings are merely schematic and not to scale. It should also be understood that the same reference numerals are used in all the drawings to indicate the same or similar parts.

[0070] This invention provides a method for visualizing a heart valve and blood flow through it for the purpose of evaluating valvular regurgitation. The visualization is generated based on both 3D B-mode data and 3D Doppler data. The visualization includes generating a combined drawing of each of the heart valve structure, the upstream confluence region, and the output jet region. The drawing parameters applied when drawing each of these structures can preferably be adjusted independently to allow for tuning the visualization. The drawing can be performed by a drawer operable to draw both raster and grid data. In some embodiments, drawing the valve structure may include applying the drawing to a raster representation of the valve structure, for example, derived from 3D B-mode data. This allows internal structural information to be considered when generating the visualization.

[0071] At least one embodiment of the present invention can provide a tunable tool that enables a user to perform diagnostic analysis of mitral regurgitation. This is achieved through visualization of the main elements involved in the phenomenon, which may include one or more of the following:

[0072] The 3D volume of the mitral valve, which is derived, for example, from 3D echo data (e.g., B-mode data).

[0073] For example, a portion of the 3D volume of the left atrium and / or left ventricle derived from 3D echo data (e.g., B-mode data).

[0074] Upstream confluence region. This is the blood flow region upstream of the valve where flow paths converge. It is typically characterized by isokinetic surfaces. Visualization of this region can be derived, at least in part, from 3D color Doppler data. The visualization can be derived using flow models or other backflow analyses, which can be configured to compute isokinetic geometry and / or 3D streamlines of the incoming flow. For example, using a flow model, velocity vectors can be generated to represent the flow through the valve.

[0075] Output the jet region. Its visualization can be derived from at least 3D color Doppler data. The visualization can be derived using a flow model or other backflow analysis method, which can be configured to derive a 3D volumetric geometry representing the segmentation and / or 3D streamlines of the jet.

[0076] Visualizing two or more of these components together allows practitioners to better understand where the valve orifice is located and its status relative to, for example, the Carpentier classification.

[0077] Any of the elements listed above can be represented using a 3D plotter, and the visualization of each element can be independently adjusted based on one or more of the following: transparency, data threshold, smoothness, color, and fading factor. Tuning can be configurable via a user interface. The user interface can allow tuning to occur simultaneously with the display of the plotted image. Alternatively, tuning can be performed automatically.

[0078] Figure 1 The steps of an example method according to one or more embodiments are outlined in block diagram form. The steps will be outlined before further explanation in the form of example embodiments.

[0079] A method for visualizing heart valves using ultrasound data is provided 10.

[0080] The method includes receiving three-dimensional B-mode ultrasound data of 12 cardiac regions containing cardiac valve structures. The method also includes receiving three-dimensional Doppler ultrasound data of 14 cardiac regions.

[0081] Method 10 further includes generating images based on B-mode data and Doppler data. Image generation includes applying image rendering. Image rendering can be used to render 2D images. Image rendering can be used to derive a combined rendering of: cardiac valve structures in the cardiac region, and output jet regions emanating from the cardiac valves, and / or upstream confluence regions upstream of the valves, which, for example, contain at least isovelocity surfaces of blood flow. In a preferred embodiment, the combined rendering may also include at least portions of the structures of one or more cardiac chambers (preferably the left atrium and / or left ventricle).

[0082] refer to Figure 1 An example method may include identifying 16a 3D regions of B-mode data occupied by heart valve structures. This can be used to obtain a 3D raster representation of the heart valve. The method may include identifying 20 output jet regions within the heart region containing fluid jets exiting from the heart valve based on processing at least Doppler ultrasound data. The method may include, for example, identifying 18 upstream confluence regions within the heart region based on processing at least Doppler ultrasound data, where the upstream confluence region is a region containing at least an isokinetic surface of blood flow.

[0083] refer to Figure 1 The method includes performing a drawing process 26 to draw an image, such as a 2D image, which includes visualizations of each of the heart valve structures, the output jet region, and the upstream confluence region.

[0084] The rendering process may include applying rendering to a 3D raster representation of the heart valve to achieve 2D visualization of the heart valve structure in a 2D image.

[0085] Optionally, and as Figure 1 As shown, method 10 may include independently adjusting one or more rendering parameters applied by 22 when rendering each of the heart valve structures, the output jet region, and the upstream confluence region. This allows for fine-tuning of the visualization of each of the heart valve structures, the upstream confluence region, and the output jet region in the final image. For example, in some embodiments, one or more rendering parameters may include at least the transparency level of each of the heart valve structures, the output jet region, and the upstream confluence region in the generated 2D image. For example, this may be the relative transparency of the heart valves, the upstream confluence region, and the output jet region in the final image. In some embodiments, one or more rendering parameters include one or more of the following: transparency, smoothness, color, and / or fading applied to each of the heart valve structures, the output jet region, and the upstream confluence region.

[0086] Mapping one or more of the heart valve structures, the outflow jet region, and the upstream confluence region may include applying a mapping transfer function to the ultrasound data. In some embodiments, one or more configurable mapping parameters may include one or more parameters of the mapping transfer function.

[0087] As described above, the method can also be embodied in hardware, such as in a processing device configured to perform the method according to any example or embodiment described in this document or according to any claim of this application.

[0088] To further aid understanding, Figure 2 A schematic representation of an example processing device 32 configured to perform methods according to one or more embodiments of the present invention is presented. The processing device is shown in the context of a system 30 including the processing device. The processing device alone represents an aspect of the invention. System 30 is another aspect of the invention. The provided system does not need to include all the illustrated hardware components; it may include only a subset of them.

[0089] The processing device 32 includes one or more processors 36 configured to perform the methods outlined above, or any embodiments described in this document or any claim of this application. In the illustrated example, the processing device also includes an input / output unit 34 or a communication interface.

[0090] exist Figure 2In the illustrated example, system 30 also includes a user interface 52. In some embodiments, adjusting one or more drawing parameters may include receiving user input from the user interface indicating settings for at least one of the one or more drawing parameters, and adjusting at least one drawing parameter based on the user input. Alternatively, the adjustment may be performed automatically.

[0091] exist Figure 2 In the illustrated example, system 30 also includes an ultrasound acquisition or imaging device 54 for acquiring 3D ultrasound data 44. The ultrasound data 44 includes 3D B-mode data and 3D Doppler data.

[0092] System 30 may also include memory 38 for storing computer program code (i.e., computer executable code) configured to cause one or more processors 36 of processing unit 32 to perform methods as outlined above or described in this disclosure or according to any of the claims.

[0093] As previously stated, the present invention can also be embodied in software form. Therefore, another aspect of the present invention is a computer program product comprising computer program code configured to, when run on a processor, cause the processor to perform any example or embodiment of the invention described herein or any method according to any claim of this patent application.

[0094] Regarding the generation of combined renderings, in at least some embodiments, the process can be understood to include the following basic steps.

[0095] A set of ultrasound data of the patient's cardiac region is received. This can be received, for example, in real time from an ultrasound acquisition device 54, or it can be received from a data repository storing previously acquired ultrasound data. The ultrasound data includes both 3D Doppler data and 3D B-mode data. The aim is to draw a representation of the scanned volume in such a way that an individual configuration of the drawing settings is allowed for each item in the cardiac valve structure and the flow through the cardiac valves (e.g., including the upstream confluence region and the outflow jet region). For this purpose, a first process may involve identifying and / or isolating and / or extracting the relevant volume portions of the received data corresponding to the different elements to be visualized. This can be achieved by applying one or more suitable segmentation algorithms to the B-mode data and / or the Doppler data.

[0096] Regarding the identification of regions corresponding to blood flow, this may include applying flow analysis modules or algorithms, such as reflux analysis modules or algorithms, capable of analyzing Doppler data to identify flow geometry and / or flow paths, and optionally calculating one or more flow-related quantities. Such software modules are known in the art, for example, PhilipsQLAB, which provides advanced Doppler and flow quantification tools. The output of such analysis modules includes, for example, a representation of the geometry and / or flow path or contour of blood flow. They may additionally provide an output representation of the geometry or shape of one or more valve orifices (because the shape of the flow envelope as it flows through the valve will reflect the shape of the orifice).

[0097] For example, document WO 2023 / 020920 A1 outlines an example flow analysis model suitable for performing these functions. In brief, the flow analysis method in WO 2023 / 020920 A1 includes receiving both B-mode ultrasound data 62 and Doppler ultrasound data 64 as input. The method includes generating a model of the mitral valve based on the B-mode data. The method also includes generating a model of the orifice based on the mitral valve model and the Doppler data. The method further includes generating a blood flow model of mitral regurgitation based on the orifice model. The method may also include comparing the blood flow model with the Doppler data and modifying the orifice model such that the blood flow model is altered to match the Doppler data. For example, the orifice model may be modified to have at least one of a different shape, a different location, or a different orientation. Readers can refer to WO 2023 / 020920 A1 for a detailed description of the implementation details of this example method.

[0098] In addition to the heart valve structure, upstream confluence region, and outflow jet region, the method may include identifying and / or isolating and / or extracting volume portions in the received ultrasound data that correspond to at least a portion of one or more heart chambers (such as the left ventricle and / or left atrium).

[0099] Once each of the relevant elements to be visualized has been identified and / or isolated and / or extracted, it is necessary to generate an image containing the elements, which involves applying image rendering.

[0100] As those skilled in the art will understand, there are various possible techniques for plotting extracted elements from ultrasound data. At least two will be briefly discussed. One approach is raster-based plotting. In raster-based plotting, a plotting algorithm is applied to a 3D raster representation of the relevant elements to be visualized, namely one or more of the heart valve structure, upstream confluence region, and outflow jet region. The 3D raster representation can be understood as a 3D voxel representation of the elements. The 3D raster representation of the heart valve region can be obtained, for example, by simply extracting a volumetric region containing the heart valve structure from 3D B-mode data. 3D raster representations of different elements of the flow can also be extracted from 3D Doppler data, B-mode data, or the flow analysis module described above. 3D raster plotting can be performed using various techniques, such as, for example, direct volume plotting, volume slicing, indirect volume plotting, maximum intensity projection (MIP), multiplanar reconstruction (MPR), shading models, etc. Preferably, the plotting is a volumetric plotting method to provide a 2D depiction of the 3D geometry of the different elements (i.e., excluding MPR plotting). Regarding direct volumetric rendering, as will be known to those skilled in the art, this involves performing ray casting of voxels through a 3D raster and applying one or more transfer functions to the voxels encountered by each ray projected through the raster to obtain a set of pixel values ​​for each ray across a 2D image frame before passing through the raster. The transfer functions map the voxel values ​​to color and opacity. In this way, certain features within the volume can be highlighted or made transparent.

[0101] Alternative to raster-based rendering, mesh-based rendering is an alternative. In mesh-based rendering, a mesh is constructed to represent the 3D external shape / morphology of a structure or volume region. Therefore, this typically represents only the external geometry of an element. The mesh is based on a polygon representation, which is typically composed of vertices, edges, and faces. These polygonal models are defined by a set of vertices that form the geometry of the object and can be triangles, quadrilaterals, or other polygonal shapes. The constructed mesh can then be rendered using various techniques such as orthographic or perspective projection, ray tracing, ray casting, scanline rendering, or rasterization. Therefore, mesh-based rendering can involve two processes (after the identification or extraction (e.g., segmentation) of relevant elements from the data): constructing a mesh representing the external geometry of the relevant elements (e.g., a heart valve structure, an upstream confluence region, and / or an outflow jet region), followed by rendering applied to the mesh. A range of techniques can be used to construct the mesh based on the segmented volume region, such as traveling cubes, surface meshes, or dual contours.

[0102] Therefore, either raster-based or mesh-based rendering can be used to render the heart valve structure, the upstream confluence region, and the outflow jet region.

[0103] In any case, the rendering process involves a variety of configurable rendering parameters, and adjusting these parameters will affect how the relevant elements being rendered will appear in the final 2D image.

[0104] In at least some embodiments, the drawing process 26 includes independently configuring or adjusting the drawing parameters applied when drawing each of the heart valve structures, the upstream confluence region, and the output jet region.

[0105] Examples of adjustable drawing parameters common to both raster-based and mesh-based drawing include the following:

[0106] Opacity / Transparency (the degree of perspective or solidity of the drawn element in the image);

[0107] brightness;

[0108] Contrast;

[0109] Color / color mapping (this associates defined colors with defined ranges of values ​​or data);

[0110] Lighting (including parameters related to virtual light sources, such as their position, intensity, and color);

[0111] Clipping planes (this allows you to select a specific portion or slice of the data to be visualized, while omitting other portions or slices);

[0112] Smoothness / shading model (determines how a surface responds to light, thus affecting the perception of smoothness or roughness);

[0113] Sampling rate (especially relevant to volume (raster) plotting, this parameter indicates the frequency at which data is sampled along the observation ray);

[0114] Texture mapping (involves applying a 2D image (texture) to a drawing surface, thereby affecting its appearance);

[0115] Fade (modifies the fade level of objects in the scene)

[0116] Depth cues (modify the appearance of an object based on its depth in the scene, such as fading it relative to distance to enhance depth perception).

[0117] Blending modes (determine how overlapping objects are visually combined, such as additive or average blending);

[0118] Resolution (the level of detail in the drawing).

[0119] Method 10 may include independently adjusting any one or more of the above-described plotting parameters for each of the heart valve structures, the upstream confluence region, and the output jet region.

[0120] Visualizing the flow path through the valvular complex and the regurgitant valve structure enhances the diagnostic analysis of valvular lesions. Furthermore, combining B-mode data plotting (of valvular structure) with another plotting using flow models (discussed above) provides a complementary representation of the lesions and their functional effects. Therefore, a method for combining anatomical valve visualization of flow patterns is proposed, enabling a clear understanding of the interaction between flow and valvular structure.

[0121] In one preferred embodiment, raster-based rendering is used to perform the rendering of the valve structure. This is advantageous because it allows internal structural information to be considered in the visualization.

[0122] In some embodiments, a combination of segmentation and voxel masking can be used to perform the identification / extraction of heart valve regions. For example, identifying a 3D region in B-mode data occupied by heart valve structures may include: segmenting the heart valve structures in the B-mode data, and calculating a 3D mask based on the segmentation, the 3D mask distinguishing the 3D region occupied by the heart valve structures from the background region.

[0123] To further explain, in order to separate the valve from the rest of the echo data volume, a 3D mask can be introduced to select the valve signal within a wider cardiac valve region. Thus, the area inside the 3D mask can be drawn differently from the area outside the 3D mask, meaning the visibility of the valve region can be enhanced (e.g., highlighted) relative to the surrounding area, resulting in better visibility and better highlighting.

[0124] To compute the 3D mask, a segmentation algorithm can first be used to generate a segmentation of the valve structure. Based on the segmentation, the following process can be applied: Extract a set of points uniformly distributed on the valve. For example, in the case of a triangular mesh, take all vertices. Alternatively, voxel region segmentation can be performed, using points sampled from voxels or the entire voxel set. Next, the principal orientation or axis of the valve can be identified, for example, by applying Principal Component Analysis (PCA) to identify the horizontal axis (e.g., the shortest axis). Add two new sets of points to the set of points. These new points are created by translating the original points along the shortest axis identified by PCA. This produces an expanded set of points with additional points on both sides of the original set along the short axis. Next, all points can be expanded along the other two axes. After expansion, the set of points is processed by a convex hull (or convex hull) algorithm, which produces the identification of a minimum convex shape covering all points. The mask is then formed by selecting all voxels inside the convex hull. Thus, this produces a 3D mask fitted around the valve structure.

[0125] The above-described renderings of each of the heart valve structures (mapped from B-mode data), the upstream confluence region (mapped using at least Doppler data), and the output jet region (mapped using at least Doppler data) can be incorporated into a single composite rendering operation to produce a composite rendered 2D image, as follows:

[0126] Figure 3 and Figure 4 An example drawing of mitral regurgitation is shown, which includes a representation of each of the heart valve structure 202, the upstream confluence region 204 facing the orifice, and the outflow jet region 206. Figure 3 and Figure 4 The same reflux is shown from opposite sides. The heart valve structure in this example is drawn from a raster representation of the heart valve structure.

[0127] Figure 5 and Figure 6 Another example drawing of mitral regurgitation is shown, which includes a representation of each of the heart valve structure 202, the upstream confluence region 204 facing the orifice, and the outflow jet region 206. Figure 5 and Figure 6 The same reflux from opposite sides is shown. The visualization also shows portions of the left atrium and left ventricle. The heart valve structures, as well as portions of the left atrium and left ventricle, are drawn from a raster representation of these structures.

[0128] Figure 7 The processing of an example method according to a specific set of embodiments is outlined in the form of a block diagram.

[0129] Source 3D B-mode 62 and 3D Doppler 64 data are shown. In the final stage of the process, plotter 102 processes the input data to plot an image that includes a representation of each of the heart valve structures, the upstream confluence region, and the output jet region.

[0130] Figure 7 An optional masking process previously discussed for deriving a 3D raster representation of the valve is illustrated, comprising segmenting the valve 72, applying a voxel mask 74 to the segmented valve, and extracting the valve signal from the masked data to produce a raster representation of the valve structure. Optionally, when generating the mask, the masking or segmentation process may also identify or isolate regions corresponding to cardiac chambers (such as ventricles or atria). Similar steps can then be applied to extract signals corresponding to these regions. A single combined mask covering both the valve and one or more cardiac chamber regions can be generated, or separate masks can be generated for the valve and(one or more) chamber regions.

[0131] This produces a grid representation of the valves and is optionally used for cardiac chamber regions, such as the ventricles and / or atria.

[0132] Alternatively or additionally, segmentation 78 of the valve structure in the B-mode data 62 can be performed, and rendering can be performed based on the segmentation without masking.

[0133] Optional use of the reflux analysis module 82 is also shown, which is adapted to output the geometry or other representation of the upstream confluence region and the output jet region, as described above. Optionally, the reflux analysis module 82 can also be configured to output a representation of the valve orifice geometry based on the external shape of the detected flow through the orifice.

[0134] Generally, the backflow analysis module can be configured to receive at least Doppler ultrasound data, such as color Doppler data, and optionally also B-mode ultrasound data. The module can be configured to construct 3D models of the orifice and / or upstream confluence region and / or outlet jet region. The module can be configured to perform flow quantification, for example, using techniques such as the proximal isokinetic surface area (PISA) method. This can be used to estimate the severity of backflow by calculating the transvalvular flow rate.

[0135] An example flow analysis method that can be employed by the reflux analysis module 82 is described in detail in document WO 2023 / 020920 A1. The method disclosed therein receives both B-mode ultrasound data 62 and Doppler ultrasound data 64 as input. The method includes generating a model of the mitral valve based on the B-mode data. The method also includes generating a model of the orifice based on the mitral valve model and the Doppler data. The method further includes generating a blood flow model of mitral valve regurgitation based on the orifice model. The method may also include comparing the blood flow model with the Doppler data and modifying the orifice model such that the blood flow model is modified to match the Doppler data. For example, the orifice model may be modified to have at least one of a different shape, a different location, or a different orientation. The reader refers to WO 2023 / 020920 A1 for a detailed description of the implementation details of this example method used by the reflux analysis module 82.

[0136] The output of the reflux analysis module may include at least the segmentation of the output jet, the geometry of the upstream confluence region, and the geometry of the orifice of the optional valve.

[0137] In some embodiments, the depiction of the heart valve structure 202, the upstream confluence region 204, the outlet jet region 206, and / or the orifice can be customized to show a cross-sectional view or sectional perspective. This is achieved by defining a 2D cross-sectional plane that cuts through these structures and drawing a view across that cross-sectional plane. Figure 7In the example, a cross-sectional planar view of the orifice geometry output from the reflux analysis module is shown at box 84, which is an optional feature. However, drawing the cross-sectional view is also an optional feature of any of the heart valve structure 202, the upstream confluence region 204, the output jet region 206, and / or the orifice geometry. Implementation details related to this feature will be described in more detail later.

[0138] It can perform 92 data normalization.

[0139] As mentioned above, the drawing parameters of each element to be drawn can be adjusted or tuned independently.

[0140] The plotter 102 receives a raster and / or mesh representation of the heart valve structure, the output jet region, the upstream confluence region, and optionally the valve orifice, the left ventricle, and / or the left atrium. The plotter is operable to simultaneously plot both the 3D raster and mesh representations.

[0141] The valves, and optionally the left atrium and left ventricle, are drawn by applying the drawing to a 3D raster representation obtained from B-mode data.

[0142] Regarding rendering, as mentioned above, the upstream confluence region and the output jet region can be rendered using a raster representation of the flow or a mesh representation using the flow geometry. For example, for the isotropic region, this can be rendered using a mesh representation. Alternatively, it can be rendered using a 3D raster representation formed from voxels of 3D color Doppler data. The color Doppler data can be thresholded first. Another alternative is to use a streamline representation for rendering.

[0143] By way of example, regarding the output jet region, this can again be plotted using a grid representation or a 3D raster representation formed by voxels of 3D color Doppler data. The color Doppler data can be thresholded first. Another alternative is to use a streamline representation to represent the output jet region.

[0144] In some embodiments, a combination of raster and mesh representation can be used to map the upstream confluence region and / or the output jet region. This can be achieved, for example, by obtaining a segmentation of the external geometry of the relevant flow region and constructing a mesh of the external geometry. The flow volume within the external geometry can be represented using a 3D raster formed by 3D color Doppler voxels within the region. The flow volume can then be drawn as a raster defined by the mesh of the external geometry (i.e., a color Doppler representation of the fluid contained within the glass).

[0145] The plotter 102 generates a combination of different elements to be visualized (i.e., the grid structure, the upstream confluence region, and the output jet region).

[0146] As mentioned above, various drawing parameters can be tuned to optimize the visibility of the visualization. Tuning of these parameters can be performed individually for each element to be included in the final drawn image. This is in... Figure 7 The flowchart is shown at box 94.

[0147] One adjustable parameter is transparency. This can be adjusted for both mesh drawing and raster drawing. Figure 8 The illustration shows the adjustment of the transparency of the depiction of the heart valve structure 202. The heart valve structure 202, the upstream confluence region 204, and the output jet region 206 are all depicted. The transparency of the heart valve structure is adjusted from most transparent to least transparent from left to right (from...). Figure 8 (a)-(c))) It can be seen that when valve structure 202 is drawn with maximum opacity, the upstream confluence region 204 is the least visible, but the geometry of the valve structure, especially its surface morphology, is the clearest. In contrast, in the leftmost image, the external shape of the valve geometry is less clear, but the shapes of the upstream confluence region 204 and the output jet region 206 are more visible. Therefore, by adjusting the relative opacity of the drawing of each item in the upstream confluence region, the heart valve structure, and the output jet region in the composite drawing, the visibility and appearance of the differential components can be configured. For example, the user can select which elements are more clearly visible and which elements are more transparent by adjusting the relative opacity.

[0148] Another possible adjustable parameter is smoothness. This means adjusting the outline of the imaged element to be smoother and less noisy (at the cost of some resolution) or less smooth and more noisy. This parameter can be adjusted for both mesh rendering and raster rendering. Figure 9 The illustration shows the smoothness adjustment of the drawn heart valve structure 202. Heart valve structure 202, upstream confluence region 204, and output jet region 206 are all drawn. The smoothness of heart valve structure 202 is adjusted from least smooth to most smooth from left to right. Figure 9 (a)-(c))).

[0149] Another adjustable parameter is fading. This means making some of the drawn elements more or less faded, i.e., more visible or less visible. For example, the relative fading of each of the heart valve structures, the upstream confluence region, and the outflow jet region (relative to each other) can be adjusted. By adjusting this parameter, this allows the user to control which elements are visible for diagnostic assessment, for example, fading out elements that are less important than others, and then fading them back in when needed. This parameter can be adjusted for both mesh drawing and raster drawing. Figure 10The illustration shows the adjustment of the fading of the heart valve structure 202 in the rendering of the heart valve structure 202, the upstream confluence region 204, and the outflow jet region 206. The fading of the heart valve structure 202 is adjusted from least fading (most visible) to most fading (from least visible) from left to right. Figure 10 (a)-(c))).

[0150] Another adjustable parameter is one or more threshold settings for rendering 3D raster data. Adjusting these threshold settings allows for the expansion / contraction of objects represented by the 3D raster, such as a heart valve structure 202. Specifically, in some embodiments, the threshold settings may refer to a cutoff value for voxels in the 3D raster, above or below which voxels are excluded from rendering.

[0151] In some embodiments, adjusting one or more threshold settings can be implemented by adjusting the threshold setting of a transfer function used when rendering a relevant 3D raster. For example, in some embodiments, rendering a 3D raster representation may include applying a transfer function to voxels of the raster representation, wherein the transfer function defines one or more visual properties, such as transparency levels, for each voxel of the raster as a function of voxel values. One or more adjustable rendering parameters may include one or more parameters of the transfer function. One or more adjustable rendering parameters may include threshold settings of the transfer function.

[0152] For example, rendering a 3D raster may include applying a transfer function to the raster, which defines a transparency level at which each voxel in the raster is rendered. The transparency function can define the transparency of each voxel as a function of its voxel value (e.g., in the case of B-mode ultrasound data, the intensity or density or Hounsfield value of each voxel). Possible transparency values ​​may range, for example, from 0 (invisible) to 1 (opaque / non-transparent). In this context, thresholding may include defining a threshold for voxel values ​​above which the transfer function is greater than zero (i.e., not visible in the rendering). By setting higher or lower thresholds, the rendered structure can appear expanded / contracted as more / fewer voxels are included in the rendering. Thresholding can be used to selectively include one type of imaged material in a rendered image and exclude another type, such as including voxels representing tissue regions and excluding voxels representing fluid regions.

[0153] In some examples, the threshold setting may include an upper threshold and a lower threshold, wherein the lower threshold can determine a voxel value above which the transfer function is greater than zero (i.e., not visible in the drawing), and the upper threshold can define a voxel value above which the transfer function is 1 (i.e., opaque / opacity).

[0154] Figure 11 The illustration shows the adjustment of thresholds used to render the raster representation of the heart valve structure 202 in the rendering of the heart valve structure 202, the upstream confluence region 204, and the output jet region 206. The thresholding values ​​for the heart valve structure 202 are adjusted from highest to lowest from left to right (from...). Figure 11 (a)-(c))).

[0155] In some embodiments, adjustable rendering parameters may include color shading for each of the heart valve structure 202, the upstream confluence region 204, and the output jet region 206. This makes the different elements easier to distinguish in visualization. Therefore, the different elements are parameterized by color. In some embodiments, color shading may be applied only to mesh rendering. This allows for better differentiation from raster rendering.

[0156] In some embodiments, the composite rendering of the heart valve structure 202, the upstream confluence region 204, and the output jet region 206 can also be configured to represent a cross-sectional view through the rendering elements, i.e., wherein a 2D cutting plane is defined by the structure, and a visualization is rendered that represents a volumetric rendering of a virtual cross-section view as if viewed through the cutting plane.

[0157] As described above, in some embodiments, the depiction of the heart valve structure 202, the upstream confluence region 204, and the output jet region 206 can be customized to show a cross-sectional view or sectional view. This is achieved by defining a 2D plane that cuts through these structures. The resulting visualization represents a volumetric drawing image that gives the observer the impression of seeing the interior of these elements as if viewed through a specified cutting plane. This allows showing what is inside and avoids superimposing elements that obscure each other. The cross-sectional position can be adjusted to optimize the view of mitral regurgitation from the viewpoint of a particular diagnostic application.

[0158] This type of cross-sectional view drawing (often called cross-sectional or section drawing) is a visualization technique that exposes the internal details of a structure that might otherwise be hidden from view. This is achieved by virtually "cutting away" or "cutting through" portions of the structure, allowing a clear view of its internal components. The process involves defining a 2D cutting plane through which the structure will be segmented. Once the plane is defined, any material or structure on one side of that plane is virtually removed or made transparent during the drawing process. A volumetric drawing image of the remaining portion of the structure can then be generated.

[0159] The position and angle of the cutting plane can be defined in different ways. One option is to allow the user to adjust the position and orientation of the plane. Another option is to define the orientation and / or position of the cutting plane relative to the major axis and normal axis of the valve (or orifice). Another option is to define the orientation and / or position of the cutting plane relative to the major axis of the valve (or orifice) and the jet direction. Yet another option is to define the orientation and / or position of the cutting plane relative to the orientation axes of all objects (valve, orifice, jet, confluence).

[0160] In some embodiments, the cutting plane can be configured to move with the movement of the anatomical structure. For example, if the pore in the valve is moving and changing its axis, a dynamic cutting plane that follows the center of the pore during acquisition can be defined. Its orientation may be limited by a trade-off between the visibility of the valve, the visibility of the incoming flow, the visibility of the outgoing jet, and the low oscillations from one frame to another.

[0161] In cases where there are several pores in the valve, the location and orientation of the cutting plane can be chosen to represent a trade-off between cutting through all the pores and not moving too much. In the case of two pores, this would be a plane that cuts through both. Typically, for mitral regurgitation, there are rarely more than two pores.

[0162] The camera viewpoint can, for example, be pointed in front of the cross-sectional plane and aligned with the center of the valve.

[0163] Figure 12 The illustration shows a cross-sectional view of the heart valve structure 202, the upstream confluence region 204, and the outflow jet region 206. Figure 12 (a) shows the non-section volume plot of the three elements. Figure 12 (b) shows a cross-sectional view across a cut plane extending through the middle of the heart valve structure. Figure 12 (b) shows a cross-sectional view across the same cutting plane from opposite sides.

[0164] Although the examples discussed above have referenced the application of visualization methods for assessing mitral regurgitation, the same methods can be applied to assess any other type of flow defect.

[0165] The embodiments of the present invention described above employ a processing device. A processing device typically includes a single processor or multiple processors. It may be located in a single containing device, structure, or unit, or it may be distributed among multiple different devices, structures, or units. Therefore, references to a processing device suitable for or configured to perform a specific step or task may correspond to that step or task performed individually or in combination by any one or more of a plurality of processing components. Those skilled in the art will understand how such a distributed processing device can be implemented. The processing device includes a communication module or input / output unit for receiving data and outputting data to other components.

[0166] One or more processors in a processing device can be implemented in various ways, using software and / or hardware, to perform a variety of required functions. A processor typically employs one or more microprocessors that can be programmed using software (e.g., microcode) to perform the desired functions. A processor can be implemented as a combination of dedicated hardware for performing some functions and one or more programmable microprocessors and associated circuitry for performing other functions.

[0167] Examples of circuits that may be employed in various embodiments of this disclosure include, but are not limited to, conventional microprocessors, application-specific integrated circuits (ASICs), and field-programmable gate arrays (FPGAs).

[0168] In various implementations, the processor may be associated with one or more storage media, such as volatile and non-volatile computer memories, such as RAM, PROM, EPROM, and EEPROM. The storage media may be encoded with one or more programs that, when executed on one or more processors and / or controllers, perform the required functions. The various storage media may be fixed within the processor or controller, or may be transportable, such that one or more programs stored thereon can be loaded into the processor.

[0169] By studying the accompanying drawings, the disclosure, and the appended claims, those skilled in the art can understand and implement variations of the disclosed embodiments in practicing the claimed invention. In the claims, the word "comprising" does not exclude other elements or steps, and the words "a" or "an" do not exclude a plurality.

[0170] A single processor or other unit can perform the functions of several items recounted in the claims.

[0171] Although specific measures are described in different dependent claims, this does not imply that combinations of these measures cannot be used advantageously.

[0172] Computer programs can be stored / distributed on suitable media, such as optical storage media or solid-state media provided with or as part of other hardware, but computer programs can also be distributed in other forms, such as via the Internet or other wired or wireless telecommunications systems.

[0173] If the term “suitable” is used in the claims or specification, it should be noted that the term “suitable” is intended to be equivalent to the term “configured as”.

[0174] Any reference numerals in the claims should not be construed as limiting the scope.

Claims

1. A method (10) for visualizing heart valves using ultrasound data, comprising: Receive (12) 3D B-mode ultrasound data of the cardiac region including the cardiac valve structures; Receive 3D Doppler ultrasound data of the cardiac region described in (14); Generating a 2D image, wherein generating the 2D image includes: Identify (16) the 3D region of the B-mode data occupied by the heart valve structure to generate a 3D grid representation of the heart valve; Based on the processing of at least the Doppler ultrasound data, identify (18) the output jet region within the cardiac region containing the fluid jet output from the cardiac valve; The upstream confluence region within the cardiac region is identified (20) based on the processing of at least the Doppler ultrasound data, wherein the upstream confluence region is a region containing at least an isokinetic surface of blood flow; Perform the (26) drawing process to draw a 2D image, the 2D image including visualizations of each of the heart valve structure, the output jet region, and the upstream confluence region. The drawing process includes applying the drawing to the 3D raster representation of the heart valve to achieve 2D visualization of the heart valve structure in the 2D image.

2. The method according to claim 1, wherein, The method includes independently adjusting (22) one or more drawing parameters applied when drawing each of the heart valve structures, the output jet region, and the upstream confluence region.

3. The method according to claim 2, wherein, The one or more parameters include at least the transparency level of each of the heart valve structures, the output jet region, and the upstream confluence region in the generated 2D image.

4. The method according to any one of claims 2-3, wherein, The one or more drawing parameters include one or more of the following: transparency, smoothness, color, and / or fading applied to each of the heart valve structure, the output jet region, and the upstream confluence region.

5. The method according to any one of claims 2-4, wherein, Adjusting the one or more drawing parameters includes: receiving user input from a user interface indicating settings for at least one of the one or more drawing parameters, and adjusting the at least one drawing parameter based on the user input.

6. The method according to any one of claims 1-5, wherein, Drawing the heart valve structure includes: applying a transfer function to voxels of the raster representation of the heart valve, wherein the transfer function defines the transparency level for each voxel of the raster as a function of the voxel value, and wherein the one or more drawing parameters include one or more parameters of the transfer function.

7. The method according to any one of claims 1-6, in, Identifying the output jet region includes: segmenting the output jet region in the Doppler ultrasound data; and The drawing of the output jet region includes: Based on the segmentation, a 3D mesh is generated to define the contour of the output jet region, and Apply volume rendering to the mesh.

8. The method according to any one of claims 1-6, wherein, The rendering of the output jet region includes applying volume rendering to a 3D raster representation of the output jet region within the Doppler data.

9. The method according to any one of claims 1-8, in, Identifying the upstream confluence region includes: segmenting the upstream confluence region in the Doppler data; The drawing of the upstream confluence region includes: The 3D mesh of the upstream confluence region is generated based on the segmentation. Apply volume rendering to the mesh.

10. The method according to any one of claims 1-8, wherein, Drawing the upstream confluence region includes applying volumetric drawing to a 3D raster representation of the upstream confluence region within the Doppler data.

11. The method according to any of the preceding claims, wherein, Identifying the 3D region of the B-mode data occupied by the heart valve structure includes: The heart valve structure in the B-mode data is segmented, and A 3D mask is calculated based on the segmentation, which distinguishes the 3D region occupied by the heart valve structure from the background region.

12. The method according to any of the preceding claims, wherein, The identification of the output jet region and the upstream confluence region includes: applying a flow dynamics model to the Doppler ultrasound data, the flow dynamics model being adapted to: Determine the isovelocity surface of blood flow upstream of the heart valve; Determine the blood flow path through the valve; Determine the output jet from the valve.

13. A processing apparatus (32) comprising one or more processors (36), said one or more processors being configured to: Receive: 3D B-mode ultrasound data of a cardiac region including the cardiac valve structure, and receive 3D Doppler ultrasound data of said cardiac region; Identify the 3D region of the B-mode data occupied by the heart valve structure to generate a 3D raster representation of the heart valve; Based on the processing of at least the Doppler ultrasound data, identify the output jet region within the cardiac region that contains the fluid jet exiting from the cardiac valve; The upstream confluence region within the cardiac region is identified based on the processing of at least the Doppler ultrasound data, wherein the upstream confluence region is a region containing at least an isokinetic surface for blood flow; and A rendering process is performed to create a 2D image, which includes visualizations of each of the heart valve structures, the output jet region, and the upstream confluence region. The drawing process includes applying the drawing to the 3D raster representation of the heart valve to achieve 2D visualization of the heart valve structure in the 2D image.

14. The device according to claim 13, wherein, The one or more processors are also configured to independently adjust one or more rendering parameters applied when rendering each of the heart valve structures, the output jet region, and the upstream confluence region.

15. A system (30) comprising: The processing apparatus (32) according to claim 13 or 14; as well as An ultrasonic acquisition device (54) is available for acquiring 3D B-mode data and 3D Doppler data.

Images