CN114010216A - Airway morphological parameter quantitative acquisition method and device and airway stent design method - Google Patents
Airway morphological parameter quantitative acquisition method and device and airway stent design method Download PDFInfo
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Abstract
The invention discloses a method and a device for quantitatively acquiring morphological parameters of an airway and a method for designing an airway stent, which comprises the following steps: performing section cutting on a chest CT image, dividing a bronchial tree into a plurality of cross sections, performing centerline fitting on the plurality of cross sections, determining a three-dimensional centerline of each bronchus, establishing a bronchial tree model according to the three-dimensional centerline and the cross sections, selecting a measuring point on the three-dimensional centerline, acquiring a morphological parameter value at the measuring point, determining a far end point and a near end point on the bronchial tree, determining lumen internal diameters and lumen area values of orthogonal sections corresponding to the plurality of measuring points between the far end point and the near end point, determining a branch included angle and a lumen volume value of the bronchial tree, and calculating a stenosis rate corresponding to the measuring points; according to the invention, the chest CT is segmented, a bronchial tree model is established, quantitative parameters of the model are measured, and quantitative parameters such as lumen internal diameter, lumen area, branch included angle, length and lumen volume value are obtained.
Description
Technical Field
The invention relates to the field of respiratory tract morphological parameter measurement, in particular to a method and a device for quantitatively acquiring airway morphological parameters and a method for designing an airway stent.
Background
The airway stenosis is caused by the reduction of the inner diameter of the airway due to some reasons, which leads to different degrees of dyspnea, atelectasis, obstructive pulmonary inflammation, even suffocation and death in clinic. The treatment means comprises surgical treatment, drug treatment and bronchoscopic intervention treatment, wherein the airway stent placement technology is important for maintaining stable and smooth airway of the patient.
The airway stent implantation has good short-term curative effect on patients with central airway stenosis, but various complications such as granulation tissue hyperplasia, sputum retention, infection, stent fracture, stent displacement and the like are easy to occur after long-term placement. In order to reduce the occurrence of complications, individualized stent design is particularly important, and the design of the airway morphological parameter measurement auxiliary stent is less researched at present.
At present, quantitative analysis before stent design is mostly evaluated by analyzing CT images of patients and combining the CT images with bronchoscopy findings. The inner diameter of a lumen, the thickness of the tube wall and the like of a focus part are artificially measured through the CT image.
The bronchoscope is adopted to measure the lesion length so as to assist the design of the bracket, and the lesion length obtained by measuring under the bronchoscope can be supplemented to the lesion length obtained by the CT post-processing technology (MPR, VE) because the visual observation under the bronchoscope can more accurately judge the boundary compared with the CT image, and the measuring method is as follows:
the method is simple to operate, but errors exist in judgment of lesion boundary and measurement of the length of the withdrawn bronchoscope.
Disclosure of Invention
The invention aims to solve the technical problems that the measurement of the morphological parameters of the airway is inaccurate at the present stage, and the measurement of the parameters required by the design of the airway stent is not standard. The method and the device for quantitatively acquiring the morphological parameters of the airway and the method for designing the airway stent solve the problems of inaccurate quantitative measurement of the morphological parameters of the bronchial tree and irregular measurement of the parameters required by the design of the airway stent.
The invention is realized by the following technical scheme:
a quantitative acquisition method for airway morphological parameters comprises the following steps:
performing section cutting on the chest CT image, and segmenting the bronchial tree into a plurality of cross sections;
performing centerline fitting on the plurality of cross sections to determine a three-dimensional centerline of each bronchus;
establishing a bronchial tree model according to the three-dimensional central line and the cross section;
determining branch angles of a plurality of trachea branches on the bronchial tree;
determining a far-end point and a near-end point on the bronchial tree, selecting a bronchus between the far-end point and the near-end point, and setting the bronchus as a measurement section;
selecting a measuring point on a three-dimensional central line of the measuring section, and acquiring morphological parameter values at the measuring point, wherein the morphological parameter values comprise: the multiple measuring points correspond to the inner diameter and the area of the lumen of the orthogonal section; the length of the segment and the lumen volume are measured.
Further, the method further comprises calculating the stenosis rate of the corresponding measurement point by the following formula:
wherein A is stenosis rate;
n is a reference normal inner diameter value/area value/volume value;
n is the true inside diameter value/area value/volume value.
Specifically, in the process of cutting the section of the chest CT image, the sub-pixel level segmentation precision is adopted in the segmentation method;
and in the measurement points selected on the three-dimensional central line, the measurement points are distributed in a sub-pixel level.
Specifically, the method for measuring the inner diameter of the lumen of the orthogonal cross section comprises the following steps:
selecting a measuring point;
constructing a minimum inscribed sphere at a measuring point to obtain an inner diameter value;
and sequentially measuring along the three-dimensional central line to obtain the inner diameter value of each measuring point in the bronchial tree.
Specifically, the distal point is any point on the bronchial tree, and the proximal point is any point between the distal point and the main opening of the trachea.
As an embodiment, the lumen area of the orthogonal cross section is obtained by obtaining the size of the connected domain of the current tracheal branch and calculating pixel points; alternatively, the first and second electrodes may be,
the trachea area is defined by drawing a closed curve at multiple points on the orthogonal section, and the area is calculated through the closed curve.
Specifically, the method for measuring the branch included angle comprises the following steps:
sequentially determining a starting point, a turning point and an end point on the three-dimensional central line;
connecting the starting point with the turning point, the turning point with the end point;
acquiring the included angle degree of the two straight lines;
the lumen volume of the measurement section is obtained by solving the pixel sums of the plurality of cross sections.
An auxiliary airway stent design method based on airway morphological parameters is based on the airway morphological parameter quantitative acquisition method, and the design method comprises the following steps:
determining the inner diameter of a lumen, the area of the lumen, the length of a lesion, the volume of the lumen and the included angle of branches corresponding to the lesion part;
making the inner diameter of a bracket of the airway bracket correspond to the inner diameter of a lumen, the area of the bracket corresponds to the area of the lumen, the length of the bracket corresponds to the length of a focus, the volume of the bracket corresponds to the volume of the lumen, and the included angle of the bracket corresponds to the included angle of a branch;
and designing the airway stent according to various morphological parameter values and pathological change states.
An apparatus for obtaining quantitative parameters of bronchial airways comprises:
the cutting module is used for cutting the section of the chest CT image and dividing the bronchial tree into a plurality of cross sections;
the fitting module is used for performing centerline fitting on the plurality of cross sections and determining the three-dimensional centerline of each bronchus;
the modeling module is used for building a bronchial tree model according to the three-dimensional central line and the cross section;
the measurement module is used for determining branch included angles of a plurality of trachea branches on the bronchial tree;
the study region selection module is used for determining a far-end point and a near-end point on the bronchial tree, selecting a bronchus between the far-end point and the near-end point, and setting the bronchus as a measurement section;
the first calculation module is used for selecting a measuring point on a three-dimensional central line of the measuring section and acquiring morphological parameter values at a plurality of measuring points, wherein the morphological parameter values comprise: the multiple measuring points correspond to the inner diameter and the area of the lumen of the orthogonal section; measuring the length of the segment and the lumen volume;
the second calculation module is used for calculating the stenosis rate of the corresponding measurement point, and the calculation formula is as follows:
wherein A is stenosis rate;
n is a reference normal inner diameter value/area value/volume value;
n is the true inside diameter value/area value/volume value.
An acquisition terminal of airway quantitative parameters comprises a memory, a processor and a computer program stored in the memory and capable of running on the processor, wherein the processor implements the steps of the airway morphological parameter quantitative acquisition method when executing the computer program.
A computer-readable storage medium, in which a computer program is stored, which, when being executed by a processor, implements the steps of a method for obtaining a quantitative airway parameter as described above.
Compared with the prior art, the invention has the following advantages and beneficial effects:
according to the invention, the chest CT is segmented and the bronchial tree is established, the morphological parameters of the bronchial tree are measured, and quantitative parameters such as the lumen inner diameter, the lumen area, the branch included angle, the length and the lumen volume are obtained, so that the quantitative parameters can be more accurate, simple and homogeneous, and therefore, the quantitative parameters obtained by the method can be applied to parameter formulation of the airway stent design to be more suitable for the focus of a patient, and the complication after the airway stent implantation operation is reduced.
Drawings
The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate exemplary embodiments of the invention and together with the description serve to explain the principles of the invention.
Fig. 1 is a schematic flow chart of a method for quantitatively acquiring airway morphological parameters according to the invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention will be further described in detail with reference to the accompanying drawings and embodiments. It is to be understood that the specific embodiments described herein are for purposes of illustration only and are not to be construed as limitations of the invention.
It should be noted that, for convenience of description, only the portions related to the present invention are shown in the drawings.
In the present invention, the embodiments and features of the embodiments may be combined with each other without conflict. The present invention will be described in detail below with reference to the accompanying drawings in conjunction with embodiments.
At present, quantitative analysis before stent design is mostly evaluated by analyzing CT images of patients and combining the CT images with bronchoscopy findings.
The analysis of CT images mainly adopts multi-planar reconstruction (MPR), which can perform transverse, coronal, sagittal, or oblique plane reconstruction according to the moving direction of the bronchus, and then measure the lumen inner diameter, wall thickness, etc. of the lesion site.
First, the inner diameter (average inner diameter ═ the (longest diameter + short diameter perpendicular to the longest diameter) ÷ 2) of the lesion is measured, as follows: the MPR layer is judged to be a section (the cross section of a bronchus) vertical to the long axis of a bronchus to be measured through experience, then a starting point and an end point of the longest diameter are manually selected, a line is pulled between the starting point and the end point by a computer, the length of the section of the line is displayed, the length is the longest diameter of a lumen, the short diameter vertical to the longest diameter is obtained through the same method, the operation is repeated once when each section is measured, the measurement is purely manual, the measurement vertical to the lumen can not be guaranteed completely, the time and the labor are consumed, and the homogenization of the measurement result can not be guaranteed;
then, the length of the focus is measured, the MPR layer is judged to be a section (the coronal plane of the bronchus) parallel to the long axis of the (bronchus) to be measured through experience, then the starting point and the end point of the narrow part are manually selected, a line is pulled between the starting point and the end point by a computer, the length of the line is displayed, the length is the length of the focus, the process also has the problems, and meanwhile, the bending and running characteristics of the (bronchus) enable the MPR imaging to be incapable of enclosing the whole section of the (bronchus) on the same layer, so that the length of the focus cannot be accurately obtained;
and finally, measuring the included angle of the branch, namely judging that the MPR layer is a layer parallel to the included angle required to be measured through experience, selecting a starting point, a turning point and an end point on the layer, and automatically displaying the included angle degree, wherein the process cannot ensure that the selected measuring point is on the middle line of the air passage, so that the measured angle is biased.
In conclusion, although the CT post-processing technology is widely applied and can help researchers and clinicians to know the focus condition to a certain extent, the operation is complicated, time and labor are wasted, and the consistency of the measurement result cannot be guaranteed.
The method for realizing the quantitative measurement of the lesion part under the bronchoscope comprises the following steps
The reference scale such as a steel wire marked with scales is placed, the area of a focus part is measured after the picture is taken under the bronchoscope, and some methods can realize accurate measurement of the narrow state of the focus part, but generally, the inner diameter/area measurement result is easy to have errors due to distance distortion and radial distortion caused by a fish-eye lens of the bronchoscope, or a special bronchoscope needs to be specially configured, and the bronchoscope belongs to invasive operation and the like, so that the clinical application of the bronchoscope is limited.
At present, bronchoscopes are mainly adopted to measure lesion lengths so as to assist in stent design, and as the visual observation under bronchoscopes can more accurately determine the boundary compared with CT images, the lesion lengths obtained by measuring under bronchoscopes can supplement the lesion lengths obtained by CT post-processing technologies (MPR, VE), and the measuring method is as follows:
the method is simple to operate, but errors exist in judgment of lesion boundary and measurement of the length of the withdrawn bronchoscope.
Example one
In view of the above drawbacks, the present embodiment provides a method for quantitatively obtaining airway morphological parameters, including the following steps:
firstly, performing section cutting on a chest CT image, and segmenting a bronchial tree into a plurality of cross sections; in the process of cutting the cross section of the chest CT image, the segmentation method adopts sub-pixel level segmentation precision, so that the precision of trachea segmentation can be ensured.
And secondly, performing centerline fitting on the plurality of cross sections to determine a three-dimensional centerline of each bronchus, namely determining the central point of each cross section, and sequentially connecting the central points to form the centerline of the bronchus tree.
And thirdly, establishing a bronchial tree model according to the three-dimensional center line and the cross section, and establishing the bronchial tree model in modeling software according to the structure of the cross section and the path of the three-dimensional center line, wherein the modeling can be realized by the technical personnel in the field through the prior art.
And fourthly, determining the branch angle of the bronchial tree.
The method for measuring the branch included angle comprises the following steps: sequentially determining a starting point, a turning point and an end point on the three-dimensional central line; connecting the starting point with the turning point, the turning point with the end point; acquiring the included angle degree of the two straight lines;
the branch included angle and the measurement section are calculated according to the three-dimensional coordinate relation between the point and the point on the selected airway central line on the bronchial tree three-dimensional model.
Fifthly, determining a far-end point and a near-end point on the bronchial tree; the far-end point is any point on the trachea branch, the near-end point is any point between the far-end point and the main opening of the trachea, the selected part between the near-end point and the far-end point is a research area, and the bronchus between the far-end point and the near-end point is selected and set as a measurement section;
sixthly, selecting a measuring point on a three-dimensional central line of the measuring section, and acquiring a morphological parameter value at the measuring point; and selecting measurement points on the three-dimensional central line, wherein the measurement points are distributed in a sub-pixel level.
The morphological parameter values include: the multiple measuring points correspond to the inner diameter and area of the lumen of the orthogonal section, the length of the measuring section and the volume of the lumen,
The method for measuring the inner diameter value of the tube cavity comprises the following steps:
selecting a measuring point;
constructing a minimum inscribed sphere at a measuring point to obtain an inner diameter value; the average inner diameter of the tube cavity is obtained in an 'inscribed sphere' mode, the average error of the inner diameter is 0.03mm, the 95% consistency boundary line is (-0.67,0.60), and accurate measurement in the true sense is realized;
and sequentially measuring along the three-dimensional central line to obtain the inner diameter value of each measuring point in the bronchial tree, and performing one-to-one matching recording on the three-dimensional central line and the inner diameter value, wherein the three-dimensional central line and the inner diameter value can be inquired when needed.
The cross section area is obtained by obtaining the size of a connected domain of the current trachea branch and calculating pixel points; or a trachea area is defined by drawing a closed curve at multiple points on the cross section, and the area is calculated through the closed curve.
The cross-sectional area of the trachea is automatically obtained by calculating the number of pixel points by obtaining the size of a connected domain of the current trachea model. The area is calculated through pixels, and errors of human eyes in identifying the pipe wall interface are greatly reduced.
In addition, the method can also be used for manually measuring, defining the trachea area by drawing a closed curve at multiple points on the trachea of the current section, and calculating the area, length and diameter through the closed curve.
The lumen volume is derived by solving the pixel sum of the plurality of cross sections. The method is based on the picture identification technology and can be realized by adopting the prior art.
In order to facilitate communication with the patient, the stenosis rate of the corresponding measurement point is further calculated according to the following formula:
wherein A is stenosis rate;
and N is a reference normal inner diameter value/area value/volume value.
n is the true inside diameter value/area value/volume value.
After the research area is determined, extracting data of corresponding positions on the model and displaying the data according to sequential linear arrangement, performing detailed far-end point and near-end point selection on the basis of the points on the recorded three-dimensional center line, obtaining the maximum value and the minimum value of the inner diameter according to the selected data line segments, calculating and displaying relevant information such as the cross section area and the change rate, and calculating the stenosis rate of the current point position according to the tracheal linear change rate of the far-end point and the near-end point.
The reference normal values are known by linear prediction of known values ("proximal reference", "distal reference"), the stenosis rate facilitates communication between physicians, and a simple judgment of the amount of stress that the stent may cause (theoretically, the greater the stenosis rate, the greater the stress, and the more likely post-operative complications) to aid in stent design.
The stenosis rate proposed in the present embodiment can be calculated by the inner diameter, the area, and the volume, and at the present stage, a method of calculating by the inner diameter, but not by the volume, is adopted.
Using the inner diameter calculation, the inner diameter of the lesion (average inner diameter ═ (longest diameter + short diameter perpendicular to longest diameter) ÷ 2) measurement is explained as follows:
the multi-plane reconstruction (a CT image post-processing technology) layer is judged to be a section (the cross section of a bronchus) vertical to the long axis of a trachea or a bronchus to be measured through experience, then a line is drawn between a starting point and an end point and the length of the section of the line is displayed by manually selecting the starting point and the end point of the longest diameter, the length is the longest diameter of a lumen, and the short diameter vertical to the longest diameter is obtained through the same method.
The method is the most adopted mode in clinical at present, because the method is easy to obtain, the method can be obtained only by CT data, and the data can be obtained by drawing two lines, but the method has the following problems: manual measurement, the error is big, and the main source of error is: the orthogonal cross section is not accurately selected; the limit of the tube cavity and the tube wall is difficult to judge; and the repeatability is poor, which is equivalent to that the measurement result of the same person is not time measurement or the measurement results of different persons at the same time are possibly different, the homogeneity is poor, and the like.
In addition, only two lines of the longest diameter and the short diameter perpendicular to the longest diameter are measured to obtain the average inner diameter, the measurement result is not the average inner diameter in the true sense by the calculation mode, and only one section is measured and cannot represent the whole focus, the focus has a certain length, a plurality of parts may need to be measured, and the complexity is increased. Also, the inner diameter can represent a limited content, only one-dimensional data, and when the cross section is an irregular circle or ellipse, the result of the measurement can represent a more limited content. Rather than simply designing through an inner diameter auxiliary stent, this stent is not known for patient compliance.
The area calculation is equivalent to the area of the tube cavity, the area of the tube cavity is obtained by drawing the edge of the tube cavity to form a closed curve, or the pixel sum is solved, namely all pixel points of a section which meet the standard (in the tube cavity) are added, each pixel point has a certain area, and the area of the tube cavity is the sum of the areas of all the pixel points. Area is a two-dimensional concept, and it is better to use area to assist in stent design than to use inner diameter.
By adopting volume calculation, the volume of the tube cavity of the test section can be understood as the volume of the gas contained in the air passage, and if one air passage is regarded as a regular circular truncated cone, the calculation formula of the volume of the tube cavity is as follows:
wherein V is the lumen volume;
h is the length of the airway of the test section;
r is the lumen radius of the orthogonal cross section of the proximal point airway;
r is the lumen radius of the orthogonal cross section of the airway at the distal point.
However, the air passage is not a regular truncated cone, and if the formula is adopted for calculation, only an approximate value of the volume of the air passage can be obtained, and if the air passage has a large change degree and an irregular and obvious shape, the formula is adopted for calculation, so that the error is larger. The current ideal method is pixel summation, that is, the volumes of all pixel points in the airway of the test segment are added and summed to obtain the true volume value.
The advantages of the volume are adopted: the volume of the focus section of a patient can be directly obtained, the data of the three-dimensional layer is considered equivalently that all points, lines and planes are considered, the state of the focus can be more accurately described, and meanwhile, the accuracy, repeatability and homogeneity are ensured by adopting a pixel sum mode instead of manual measurement.
Example two
After quantitative parameters such as various lumen internal diameters, lumen areas, lesion lengths, branch included angles and the like of a bronchial tree are measured, an auxiliary airway stent is designed according to the data, and the airway morphological parameter-based auxiliary airway design method provided by the embodiment comprises the following steps:
determining lumen inner diameter, lumen area, lesion length, lumen volume and branch angle corresponding to the lesion site by the methods described herein;
the inner diameter of a bracket of the airway bracket corresponds to the inner diameter of a lumen, the area of the bracket corresponds to the area of the lumen, the length of the bracket corresponds to the length of a focus, the volume of the bracket corresponds to the volume of the lumen, and the included angle of the bracket corresponds to the included angle of a branch.
The design of the airway stent is performed according to various morphological parameter values and pathological states, and the person skilled in the art can understand and implement, for example:
the type of stent is selected according to the nature of the lesion, such as malignant airway stenosis, the first choice of covered stent is recommended for those with longer life expectancy, and the naked stent can be placed for those with shorter life expectancy. A metal bare stent is used with caution for benign airway stenosis, and a covered stent is required for plugging various airway fistulas. The shape of the stent is selected according to the lesion part, for example, a straight cylindrical stent is mainly used for the lesion of the upper middle trachea or one side bronchus (more than 2cm away from the carina). The bifurcated stent (Y or L shaped) can be used for lesions of the mid-lower trachea, 1cm from the carina, or the carina itself, and the right and left main bronchi at approximately 1/2. The specification of the stent is selected according to the radial line measurement result of a diseased region, if the diameter of the stent placed in a patient with airway stenosis is predicted to be less than 10%, the length of the stent is greater than about 10-20 mm of a diseased region, and the diameter of the stent is greater than 10% of the diameter of a normal airway when the airway fistula is closed, the stent can be properly lengthened.
Morphological parameter values of the focus part can assist the design of the final radial line of the airway stent.
Adopt the supplementary support of volume to set up the timing, also can make the design of support more laminate the air flue, but can not only rely on the volume, the same focus length that needs combine, narrow position's diameter isoparametric designs, and the individuation air flue support that accords with different patients can only be made to omnidirectional consideration like this.
EXAMPLE III
The embodiment provides a device for quantitatively acquiring airway morphological parameters, which comprises a cutting module, a fitting module, a modeling module, a measuring module, a research area selecting module, a first calculating module and a second calculating module.
The cutting module is used for cutting the section of the chest CT image and dividing the bronchial tree into a plurality of cross sections;
the fitting module is used for performing centerline fitting on the plurality of cross sections and determining the three-dimensional centerline of each bronchus;
the measurement module is used for determining branch included angles of a plurality of trachea branches on the bronchial tree;
the study region selection module is used for determining a far-end point and a near-end point on the bronchial tree, selecting a bronchus between the far-end point and the near-end point, and setting the bronchus as a measurement section;
the first calculation module is used for selecting a measuring point on a three-dimensional central line of the measuring section and acquiring morphological parameter values at a plurality of measuring points, wherein the morphological parameter values comprise: the multiple measuring points correspond to the inner diameter and the area of the lumen of the orthogonal section; measuring the length of the segment and the lumen volume;
the second calculation module is used for calculating the stenosis rate of the corresponding measurement point, and the calculation formula is as follows:
wherein A is stenosis rate;
n is a reference normal inner diameter value/area value/volume value;
n is the true inside diameter value/area value/volume value.
All the modules can be integrated in one processor, that is, the functions of all the modules are directly realized in one processor; the method according to the first embodiment may be implemented by connecting a plurality of processors to each other via a data cable, thereby integrating the processors into one unit.
Example four
A terminal for quantitatively acquiring airway morphological parameters comprises a memory, a processor and a computer program which is stored in the memory and can run on the processor, and is characterized in that the processor realizes the steps of the method for quantitatively acquiring airway morphological parameters when executing the computer program.
The memory may be used to store software programs and modules, and the processor may execute various functional applications of the terminal and data processing by operating the software programs and modules stored in the memory. The memory may mainly include a program storage area and a data storage area, wherein the program storage area may store an operating system, an execution program required for at least one function, and the like.
The storage data area may store data created according to the use of the terminal, and the like. Further, the memory may include high speed random access memory, and may also include non-volatile memory, such as at least one magnetic disk storage device, flash memory device, or other volatile solid state storage device.
A computer-readable storage medium, in which a computer program is stored, wherein the computer program, when being executed by a processor, implements the steps of a method for quantitative acquisition of airway morphological parameters as described above.
Without loss of generality, computer readable media may comprise computer storage media and communication media. Computer storage media includes volatile and nonvolatile, removable and non-removable media implemented in any method or technology for storage of information such as computer readable instruction data structures, program modules or other data. Computer storage media includes RAM, ROM, EPROM, EEPROM, flash memory or other solid state storage technology, CD-ROM, DVD, or other optical storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices. Of course, those skilled in the art will appreciate that computer storage media is not limited to the foregoing. The system memory and mass storage devices described above may be collectively referred to as memory.
In the description herein, reference to the description of the terms "one embodiment/mode," "some embodiments/modes," "example," "specific example," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment/mode or example is included in at least one embodiment/mode or example of the application. In this specification, the schematic representations of the terms used above are not necessarily intended to be the same embodiment/mode or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments/modes or examples. Furthermore, the various embodiments/aspects or examples and features of the various embodiments/aspects or examples described in this specification can be combined and combined by one skilled in the art without conflicting therewith.
Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present application, "plurality" means at least two, e.g., two, three, etc., unless specifically limited otherwise.
It will be understood by those skilled in the art that the foregoing embodiments are merely for clarity of description and are not intended to limit the scope of the invention. It will be apparent to those skilled in the art that other variations or modifications may be made on the above invention and still be within the scope of the invention.
Claims (10)
1. A quantitative acquisition method for airway morphological parameters is characterized by comprising the following steps:
performing section cutting on the chest CT image, and segmenting the bronchial tree into a plurality of cross sections;
performing centerline fitting on the plurality of cross sections to determine a three-dimensional centerline of each bronchus;
establishing a bronchial tree model according to the three-dimensional central line and the cross section;
determining branch angles of a plurality of trachea branches on the bronchial tree;
determining a far-end point and a near-end point on the bronchial tree, selecting a bronchus between the far-end point and the near-end point, and setting the bronchus as a measurement section;
selecting a measuring point on a three-dimensional central line of the measuring section, and acquiring morphological parameter values at a plurality of measuring points, wherein the morphological parameter values comprise: the plurality of measurement points correspond to the lumen inner diameter, the lumen area, the length of the measurement section, and the lumen volume of the orthogonal cross section.
2. The method for quantitatively acquiring the morphological parameters of the airways according to claim 1, further comprising calculating the stenosis rate of the corresponding measurement points by the following formula:
wherein A is stenosis rate;
n is a reference normal inner diameter value/area value/volume value;
n is the true inside diameter value/area value/volume value.
3. The method for quantitatively acquiring the morphological parameters of the airways according to claim 2, wherein the method for measuring the inner diameter of the lumen of the orthogonal section comprises the following steps:
selecting a measuring point;
constructing a minimum inscribed sphere at a measuring point to obtain an inner diameter value;
and sequentially measuring along the three-dimensional central line to obtain the inner diameter value of each measuring point in the bronchial tree.
4. The quantitative acquisition method of airway morphological parameters according to claim 3, characterized in that in the cross-section cutting of the chest CT image, the segmentation method adopts sub-pixel level segmentation precision;
and in the measurement points selected on the three-dimensional central line, the measurement points are distributed in a sub-pixel level.
The far-end point is any point on the bronchial tree, and the near-end point is any point between the far-end point and the main opening of the trachea.
5. The quantitative acquisition method of airway morphological parameters according to claim 4, characterized in that the lumen area of the orthogonal cross section is obtained by acquiring the size of the connected domain of the current tracheal branch and calculating pixel points; alternatively, the first and second electrodes may be,
the trachea area is defined by drawing a closed curve at multiple points on the orthogonal section, and the area is calculated through the closed curve.
6. The method for quantitatively acquiring the morphological parameters of the airways according to claim 1, wherein the method for measuring the included angle of the branches comprises:
sequentially determining a starting point, a turning point and an end point on the three-dimensional central line;
connecting the starting point with the turning point, the turning point with the end point;
acquiring the included angle degree of the two straight lines;
the lumen volume value of the measurement segment is obtained by solving the pixel sums of the plurality of cross sections.
7. An auxiliary airway stent design method based on airway morphological parameters, which is characterized in that based on the quantitative acquisition method of airway morphological parameters as in any one of claims 1 to 6, the design method comprises the following steps:
determining the inner diameter of a lumen, the area of the lumen, the length of a lesion, the volume of the lumen and the included angle of branches corresponding to the lesion part;
making the inner diameter of a bracket of the airway bracket correspond to the inner diameter of a lumen, the area of the bracket corresponds to the area of the lumen, the length of the bracket corresponds to the length of a focus, the volume of the bracket corresponds to the volume of the lumen, and the included angle of the bracket corresponds to the included angle of a branch;
and designing the airway stent according to various morphological parameter values and pathological change states.
8. An apparatus for quantitative acquisition of airway morphological parameters, comprising:
the cutting module is used for cutting the section of the chest CT image and dividing the bronchial tree into a plurality of cross sections;
the fitting module is used for performing centerline fitting on the plurality of cross sections and determining the three-dimensional centerline of each bronchus;
the modeling module is used for building a bronchial tree model according to the three-dimensional central line and the cross section;
the measurement module is used for determining branch included angles of a plurality of trachea branches on the bronchial tree;
the study region selection module is used for determining a far-end point and a near-end point on the bronchial tree, selecting a bronchus between the far-end point and the near-end point, and setting the bronchus as a measurement section;
the first calculation module is used for selecting a measuring point on a three-dimensional central line of the measuring section and acquiring morphological parameter values at a plurality of measuring points, wherein the morphological parameter values comprise: the multiple measuring points correspond to the inner diameter and the area of the lumen of the orthogonal section; measuring the length of the segment and the lumen volume;
the second calculation module is used for calculating the stenosis rate of the corresponding measurement point, and the calculation formula is as follows:
wherein A is stenosis rate;
n is a reference normal inner diameter value/area value/volume value;
n is the true inside diameter value/area value/volume value.
9. A terminal for quantitative acquisition of airway morphology parameters, comprising a memory, a processor and a computer program stored in the memory and executable on the processor, characterized in that the processor, when executing the computer program, implements the steps of the method according to any one of claims 1-6.
10. A computer-readable storage medium, in which a computer program is stored which, when being executed by a processor, carries out the steps of the method according to any one of claims 1-6.
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