Lung ventilation function measuring method and device and medium
By combining a ring-shaped multi-probe SPECT/CT device with an infrared laser camera, automated assessment of lung ventilation function is achieved, solving the problem of lack of objective analysis in existing technologies and providing a reliable assessment tool.
Patent Information
- Application Number
- CN202511179642.7
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2025-08-22
- Publication Date
- 2025-12-02
AI Technical Summary
Existing lung ventilation imaging technology lacks objective and automated image analysis methods, and relies on inconsistent subjective judgment standards by doctors.
A ring-shaped multi-probe SPECT/CT device was used to acquire real-time dynamic four-dimensional tomographic signals. Combined with an infrared laser camera to track the patient's respiratory status, the radioactivity count of the region of interest was extracted through spatial standardization and registration techniques. The peak filling rate and time to peak were calculated, and the location and degree of abnormal lung ventilation were marked using 3D rendering icons.
It enables an objective and reliable assessment of lung ventilation function, reduces the bias of doctors' subjective judgment, and provides an automated assessment tool.
Smart Images
Figure CN121040935A_ABST
Abstract
Description
Technical Field
[0001] This invention relates to the field of nuclear medicine imaging technology, and in particular to a method, device and medium for measuring pulmonary ventilation function. Background Technology
[0002] Lung ventilation imaging is a nuclear medicine examination method that assesses lung ventilation function using a radioactive tracer (imaging agent). The most reliable radioactive tracer is 99mTc-labeled ultrafine carbon microparticle radioactive powder, generated using a technetium gas generator. The prepared radioactive technetium gas mixed with pure argon gas is inhaled by the patient in a seated position via a mouth-held nebulizer. The exhalation-inhalation-breath-holding sequence is repeated multiple times until the gamma detector records a radioactivity count of 2000 Kc / s in both lungs, at which point the inhalation of the radioactive gas is stopped. The tracer will deposit in different levels of the airways and alveoli with each breath, distributing evenly throughout the lungs. After the patient is moved to the examination room, a gamma camera or SPTCT device is used to detect and acquire data on the distribution of radioactivity in the lungs. After reconstructing the imaging data, the ventilation function of different parts of both lungs is assessed. This technique visually displays airway patency and alveolar ventilation function by detecting the distribution of radioactive material in the lungs.
[0003] However, this imaging technology and image analysis process still rely on the doctor's judgment, and each doctor's judgment criteria are not uniform. Therefore, there is a lack of reliable, objective, and automated image analysis methods. Summary of the Invention
[0004] In view of the above problems, the present invention provides a method, apparatus and medium for measuring pulmonary ventilation function that overcomes or at least partially solves the above problems.
[0005] In a first aspect, the present invention provides a method for measuring pulmonary ventilation function, comprising:
[0006] After the patient inhales technetium gas, the annular multi-probe SPECT / CT device is activated to initiate the real-time dynamic tomography four-dimensional signal acquisition of single-photon signals;
[0007] The patient's respiratory status is identified and tracked using an infrared laser camera, and the patient's respiratory cycle is divided into 16 phases according to the amplitude of respiratory movements.
[0008] Based on the 16 time phases, CT structural images of the patient at the end of inspiration and SPECT images of each time phase of the respiratory cycle were acquired.
[0009] The SPECT images of each phase of the respiratory cycle are spatially standardized according to the SPECT images of the end-expiratory phase to obtain spatially standardized SPECT images.
[0010] The spatially standardized SPECT image is registered with the CT structural image to obtain a registered SPECT image, so that the outline and spatial position of the registered SPECT image are consistent with the outline and spatial position of the CT structural image.
[0011] Based on the anatomical landmarks on the CT structural images, the radioactivity counts in the regions of interest are extracted from the registered SPECT images to obtain the frame-by-frame curves of radioactivity counts over time at the three levels of lung lobe, lung segment, and voxel.
[0012] Based on the curve of the radioactivity count over time, the peak filling rate, time to peak, and average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase were calculated.
[0013] Based on the average of the peak filling rate, time to peak filling, and standard uptake values of the radioactive tracer in both lung tissues, the location, extent, and degree of abnormal lung ventilation are marked on a 3D rendering of the patient's lungs.
[0014] Preferably, after the patient inhales technetium gas and before the annular multi-probe SPECT / CT device is activated to initiate the four-dimensional signal acquisition of real-time dynamic tomography of single-photon signals, the procedure further includes:
[0015] Connect the technetium gas generator mask to the oxygen tubing, turn on the technetium generator while controlling the oxygen supply, and guide the patient to perform multiple Cheyne-Stokes breaths.
[0016] Preferably, after acquiring CT structural images of the patient's breath-holding state at the end of inspiration and SPECT images of each phase of the respiratory cycle based on the 16 time phases, the method further includes:
[0017] Scatter correction was performed on the SPECT images of each phase of the respiratory cycle.
[0018] Preferably, the SPECT images of each phase of the respiratory cycle are spatially normalized according to the SPECT image of the end-expiratory phase to obtain spatially normalized SPECT images, including:
[0019] An infrared laser camera is used to collect the three-dimensional coordinate position changes of radioactive tracer points in the patient's lungs at different phases of the respiratory cycle, and a displacement vector is generated. The displacement vector includes translation, rotation, and scaling parameters.
[0020] Based on the displacement vector, the data coordinates of the SPECT images at each phase of the respiratory cycle are mapped according to the data coordinates of the SPECT images at the end of the expiration phase to obtain spatially standardized SPECT images.
[0021] Preferably, after registering the spatially normalized SPECT image with the CT structural image to obtain the registered SPECT image, the method further includes:
[0022] Based on the CT structural image, an attenuation-corrected μ map is generated;
[0023] Based on the attenuation correction μ map, the registered SPECT image is subjected to frame-by-frame attenuation correction to obtain a corrected SPECT image.
[0024] Preferably, based on the anatomical landmarks on the CT structural image, the radioactivity count within the region of interest is extracted from the registered SPECT image to obtain frame-by-frame curves showing the radioactivity count over time at the lobe, segment, and voxel levels, including:
[0025] Based on the CT structural images, the anatomical landmarks of the lobes and segments of both lungs were determined.
[0026] Based on the anatomical landmarks, the regions of interest for lung lobes and lung segments in the registered SPET images are delineated and segmented.
[0027] Based on the region of interest, the corresponding radioactivity counts are extracted, and a frame-by-frame curve of the radioactivity counts over time is generated at the three levels of lung lobe, lung segment, and voxel.
[0028] Preferably, based on the curve of the radioactivity count changing over time, the peak filling rate, time to peak, and average value of the standard uptake of the radioactive tracer in the lung tissue during the stable phase are calculated. Specifically, the average value of the standard uptake of the radioactive tracer in the lung tissue during the stable phase is calculated as follows:
[0029] SUV = C / (D / W)
[0030] Where C is the average uptake of radioactive tracer in both lung tissues, D is the injection dose, W is the patient's weight, and SUV is the average of the standard uptake of radioactive tracer in both lung tissues.
[0031] Preferably, based on the average of the peak filling rate, time to peak filling, and the standard uptake values of the radiotracer in both lung tissues, the location, extent, and degree of abnormal lung ventilation are marked on a 3D rendering of the patient's lungs, including:
[0032] The differences between the average values of the peak filling rate, time to peak, and standard uptake values of the radioactive tracer in the bilateral lung tissue and their respective reference values are calculated.
[0033] Determine whether the difference exceeds a preset value;
[0034] If so, identify the corresponding location and mark the location, extent, and degree of abnormal lung ventilation on the 3D rendering of the patient's lungs.
[0035] Secondly, the present invention also provides a pulmonary ventilation function measuring device, comprising:
[0036] The acquisition module is used to activate the annular multi-probe SPECT / CT device to acquire four-dimensional signals of real-time dynamic tomography of single-photon signals after the patient inhales technetium gas.
[0037] The tracking module is used to identify and track the patient's respiratory status using an infrared laser camera, and divides the patient's respiratory cycle into 16 phases according to the amplitude of respiratory movements.
[0038] The acquisition module is used to acquire CT structural images of the patient at the end of inspiratory breath-holding state and SPECT images of each phase of the respiratory cycle based on the 16 time phases.
[0039] The first obtaining module is used to spatially standardize the SPECT images of each phase of the respiratory cycle according to the SPECT image of the end-expiratory phase, so as to obtain a spatially standardized SPECT image.
[0040] The second obtaining module is used to register the spatially standardized SPECT image with the CT structural image to obtain a registered SPECT image, so that the outline and spatial position of the CT structural image are consistent with the outline and spatial position of the registered SPECT image.
[0041] The third module is used to extract the radioactivity count in the region of interest of the registered SPECT image based on the anatomical landmarks on the CT structural image, and obtain the curve of radioactivity count changing with time frame by frame at the three levels of lung lobe, lung segment, and voxel.
[0042] The calculation module is used to calculate the peak filling rate, peak time, and average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase, based on the curve of the radioactive count changing over time.
[0043] The annotation module is used to annotate the location, extent, and degree of abnormal lung ventilation on a 3D rendering of the patient's lungs based on the peak filling rate, peak time, and the average value of the standard uptake of the radiation tracer in the lung tissue.
[0044] Thirdly, the present invention also provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the method described in the first aspect.
[0045] One or more technical solutions in the embodiments of the present invention have at least the following technical effects or advantages:
[0046] This invention provides a method for measuring pulmonary ventilation function, comprising: after a patient inhales technetium gas, activating a ring-shaped multi-probe SPECT / CT device to initiate real-time dynamic tomography four-dimensional signal acquisition of single-photon signals; identifying and tracking the patient's respiratory state using an infrared laser camera, and dividing the patient's respiratory cycle into 16 phases according to the amplitude of respiratory movements; acquiring CT structural images of the patient's end-inspiratory breath-hold state and SPECT images of each phase of the respiratory cycle based on the 16 phases; spatially standardizing the SPECT images of each phase of the respiratory cycle according to the SPECT image of the end-expiratory phase to obtain spatially standardized SPECT images; and registering the spatially standardized SPECT images according to the CT structural images to obtain registered SPECT images, so that the registered SPECT images... The contours and spatial locations are consistent with those of the CT structural images. Based on the anatomical landmarks on the CT structural images, radioactivity counts within the regions of interest are extracted from the registered SPECT images, resulting in frame-by-frame curves showing the radioactivity counts over time at the lobe, segment, and voxel levels. Based on these curves, the peak filling rate, time to peak, and average standard uptake values of the radiotracer in the lung tissue during the stable phase are calculated. Using these peak filling rates, time to peak, and average standard uptake values of the radiotracer in the lung tissue, the location, extent, and degree of abnormal lung ventilation are marked on a 3D rendering of the patient's lungs. Through autonomous computer analysis and judgment, the patient's lung ventilation function is objectively and reliably assessed. Attached Figure Description
[0047] Various other advantages and benefits will become apparent to those skilled in the art upon reading the following detailed description of preferred embodiments. The accompanying drawings are for illustrative purposes only and are not intended to limit the invention. Furthermore, the same reference numerals denote the same parts throughout the drawings. In the drawings:
[0048] Figure 1 A schematic flowchart of the method for measuring pulmonary ventilation function in an embodiment of the present invention is shown;
[0049] Figure 2 This diagram illustrates how, in an embodiment of the present invention, the patient's respiratory cycle is divided into 16 phases according to the amplitude of respiratory movements.
[0050] Figure 3 This diagram illustrates how SPECT images of the same respiratory phase in each respiratory cycle in an embodiment of the present invention maintain consistency in both spatial location and morphology.
[0051] Figure 4 A schematic diagram of SPECT images at various time phases in an embodiment of the present invention is shown;
[0052] Figure 5 A schematic diagram of spatially standardized SPECT images in an embodiment of the present invention is shown;
[0053] Figure 6 A schematic diagram of the registered SPECT image is shown in an embodiment of the present invention;
[0054] Figure 7 A schematic diagram of the rib surface of the lung is shown in an embodiment of the present invention;
[0055] Figure 8 This is a schematic diagram of the mediastinal surface of the lung in an embodiment of the present invention;
[0056] Figure 9 This is a schematic diagram of the diaphragm surface of the lung in an embodiment of the present invention;
[0057] Figure 10 The curves showing the changes in radioactivity counts over time at the three levels of lung lobe, lung segment, and voxel in an embodiment of the present invention are illustrated.
[0058] Figure 11 A schematic diagram showing the location of abnormal lung ventilation on the costal surface of the lung in an embodiment of the present invention is shown;
[0059] Figure 12 A schematic diagram showing the location of abnormal lung ventilation on the mediastinal surface of the lung in an embodiment of the present invention is shown;
[0060] Figure 13 A schematic diagram showing the location of abnormal lung ventilation on the diaphragmatic surface of the lung in an embodiment of the present invention is shown;
[0061] Figure 14 A schematic diagram of the pulmonary ventilation function measuring device in an embodiment of the present invention is shown. Detailed Implementation
[0062] Exemplary embodiments of the invention will now be described in more detail with reference to the accompanying drawings. While exemplary embodiments of the invention are shown in the drawings, it should be understood that the invention may be implemented in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided to enable a more thorough understanding of the invention and to fully convey the scope of the invention to those skilled in the art.
[0063] Example 1:
[0064] Embodiments of the present invention provide a method for measuring pulmonary ventilation function, such as... Figure 1 As shown, it includes:
[0065] S101: After the patient inhales technetium gas, the annular multi-probe SPECT / CT device is activated to start the real-time dynamic tomographic acquisition of single-photon signals.
[0066] S102 uses an infrared laser camera to identify and track the patient's respiratory status and divides the patient's respiratory cycle into 16 phases according to the amplitude of respiratory movements.
[0067] S103, based on 16 time phases, acquires CT structural images of the patient at the end of inspiratory breath-holding state and SPECT images of each time phase of the respiratory cycle.
[0068] S104. Spatial standardization of SPECT images at each phase of the respiratory cycle is performed according to the SPECT images at the end of the expiration phase to obtain spatially standardized SPECT images.
[0069] S105, register the spatially standardized SPECT image with the CT structural image to obtain the registered SPECT image, so that the outline and spatial position of the registered SPECT image are consistent with the outline and spatial position of the CT structural image.
[0070] S106, based on anatomical landmarks on CT structural images, extracts the radioactivity count in the region of interest from the registered SPECT images, and obtains the curves of radioactivity count changing over time frame by frame at the three levels of lung lobe, lung segment, and voxel.
[0071] S107, based on the curve of radioactive count changing over time, calculates the peak filling rate of radioactive count, the time to peak, and the average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase.
[0072] S108, based on the average of peak filling rate, time to peak filling, and standard uptake values of radiotracers in both lung tissues, marks the location, extent, and degree of abnormal lung ventilation on a 3D rendering of the patient's lungs.
[0073] Conventional techniques often employ mouth-mounted nebulizers for technetium inhalation. However, because the mouth and nebulizer mouthpiece are not sealed during exhalation, radioactive technetium diffuses into the air, causing indoor radioactive contamination and unnecessary internal radiation damage to staff and their families. This invention uses a face mask for inhalation, simultaneously connecting the technetium generator's mask to an oxygen tubing. The technetium generator is activated while controlling oxygen supply, guiding the patient through multiple Cheyne-Stokes breaths. This method, through the introduction of an oxygen tubing, ensures the safety and feasibility of breathing under prolonged mask-sealed conditions.
[0074] Specifically, 0.1 ml of pertechnetate solution (with a radioactivity typically between 10 and 20 mCi) is placed in a technetium gas generator to prepare radioactive technetium gas for later use. Then, by connecting the technetium gas generator mask to the oxygen ventilation tube, and after confirming that the mask is securely fitted to the patient in a supine position on the SPECT / CT examination table and that the airtightness is good, the ventilation switch of the technetium gas generator is turned on, and the patient is guided to perform multiple Cheyne-Stokes breaths until the radioactivity count in both lungs reaches 2000 Kc / s. Alternatively, for patients with severely impaired lung ventilation function who cannot reach the target, the ventilation valve of the technetium gas generator is closed after the radioactivity count in both lungs has stabilized for 1 minute, while the oxygen pipeline remains open.
[0075] Next, in step S101, after the patient inhales technetium gas, the annular multi-probe SPECT / CT device is activated to begin real-time dynamic tomography acquisition of four-dimensional signals from single-photon signals. The acquisition time is 10 minutes.
[0076] By performing dynamic imaging while the patient is in a supine position inhaling radioactive technetium gas, and keeping the position consistent with the lung perfusion imaging agent and imaging posture, false mismatches caused by gravity factors affecting lung ventilation imaging and lung perfusion phenomena under different body positions can be avoided.
[0077] Among them, the ring-shaped multi-probe SPECT / CT device is a nuclear medicine examination device that combines single-photon emission computed tomography (SPECT) and computed tomography (CT). It has a ring detector structure and a multi-probe design, and the same detector ring can realize dual functions of PET and CT.
[0078] Next, in S102, the patient's respiratory status is identified and tracked by an infrared laser camera, and the patient's respiratory cycle is divided into 16 phases according to the amplitude of respiratory movements.
[0079] The respiratory cycle refers to the complete time process from the start of one inhalation to the start of the next inhalation, which includes four phases: inhalation trigger, inhalation phase, exhalation start, and exhalation phase.
[0080] For calm breathing, inhalation takes up about 1 / 3 of the time and exhalation takes up about 2 / 3. Divide the total time into 16 segments, and the duration of each segment = total time / 16.
[0081] This ensures that the SPECT images of the same respiratory phase in each respiratory cycle remain consistent in spatial location and morphology.
[0082] like Figure 2 The diagram shows 16 equally divided time phases. (As shown...) Figure 3 As shown, SPECT images of the same respiratory phase in each respiratory cycle maintain consistency in spatial location and morphology. Figure 4The image shown is a SPECT image at various time points.
[0083] Following S103, it also includes: scatter correction of SPECT images at each phase of the respiratory cycle.
[0084] The core purpose of scattering correction is to remove signal interference caused by scattered photons in SPECT images, thereby improving the accuracy and spatial resolution of SPECT images. In SPECT images at different phases of the respiratory cycle, respiratory motion may exacerbate the scattering effect. Correction can ensure the reliability of the absorbance values of SPECT images at each phase and avoid artifacts affecting clinical diagnosis. Specifically, scattered signals cause the measured absorbance values to deviate from the true attenuation values. By estimating and subtracting the scattered components through techniques such as convolution-subtraction or fitting, image contrast can be significantly improved.
[0085] Next, step S104 is executed to spatially standardize the SPECT images from each phase of the respiratory cycle according to the SPECT images from the end-expiratory phase, resulting in spatially standardized SPECT images. For example... Figure 5 The image shown is a spatially normalized SPECT image.
[0086] Specifically, an infrared laser camera is used to collect the three-dimensional coordinate position changes of radioactive tracer points in the patient's lungs at each phase of the respiratory cycle, generating a displacement vector. The displacement vector includes translation, rotation, and scaling parameters. Based on the displacement vector, the data coordinates of the SPECT images at each phase of the respiratory cycle are mapped according to the data coordinates of the SPECT images at the end of the expiration phase to obtain spatially standardized SPECT images.
[0087] Based on infrared laser camera marker tracking technology, displacement parameters (specifically displacement vectors) of radioactive tracer points in lung tissue during the respiratory cycle are established. Using the Monte Carlo algorithm, the distribution periodic change model of radioactive tracer points under different respiratory states is further simulated based on the raw SPECT data of different phases of the respiratory cycle. Thus, the SPECT image data of each phase of the respiratory cycle are spatially standardized with reference to the SPECT image of the end-expiratory phase.
[0088] Standardization of SPECT images based on the end-expiratory phase is advantageous because the lung volume is smallest and relatively stable at the end-expiratory phase, the anatomical structure is fixed and has minimal variation, making it easier to accurately align SPECT images from other phases and reduce artifacts and registration errors caused by respiratory motion.
[0089] Next, step S105 is executed to register the spatially normalized SPECT image with the CT structural image, resulting in a registered SPECT image. This ensures that the contour and spatial position of the registered SPECT image are consistent with those of the CT structural image. Figure 6The image shown is a registered SPECT image.
[0090] Specifically, a spatial transformation algorithm is used to precisely align the functional metabolic image data of spatially normalized SPECT images with the anatomical structures of CT structural images in space. The spatially normalized SPECT images primarily reflect the tracking of radioactive tracer points, while the CT structural images provide higher-resolution anatomical details; registration ensures that the coordinate systems of the two are aligned.
[0091] Following S105, it also includes:
[0092] Based on CT structural images, generate attenuation-corrected μ maps;
[0093] Based on the attenuation correction μ map, frame-by-frame attenuation correction is performed on the registered SPECT image to obtain the corrected SPECT image.
[0094] By employing the frame-by-frame attenuation correction described above, the signal attenuation problem caused by the absorption or scattering of gamma photons in the patient's lung tissue can be resolved, thereby improving the quantitative accuracy and diagnostic reliability of the registered SPECT images.
[0095] Next, S106 is executed. Based on the anatomical landmarks on the CT structural images, the radioactivity counts in the region of interest of the registered SPECT images are extracted to obtain the curves of radioactivity counts changing over time frame by frame at the three levels of lung lobe, lung segment, and voxel.
[0096] Specifically, based on CT structural images, anatomical landmarks of the lobes and segments of both lungs are determined;
[0097] Based on anatomical landmarks, regions of interest in lung lobes and segments are delineated and segmented in the registered SPECT images;
[0098] Based on the region of interest, the corresponding radioactivity counts are extracted, and a frame-by-frame curve of the radioactivity counts over time is generated at the three levels of lung lobe, lung segment, and voxel.
[0099] Specifically, the boundaries between lung lobes and segments are shown from different perspectives, including, for example... Figure 7 The rib surface 70 shown is as follows: Figure 8 The diaphragmatic surface 80 shown, and as shown Figure 9 The diaphragm surface 90 shown, and as shown Figure 10 The curves shown represent the changes in radioactivity counts over time at the three levels of lung lobe, lung segment, and voxel.
[0100] Next, S107 is performed to calculate the peak filling rate, time to peak, and average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase, based on the curve of radioactive count changing over time.
[0101] Peak filling rate is the rate at which the linear radioactive count changes over time during the inspiratory phase of the respiratory cycle; time to peak is the duration from the initial time point to the plateau phase in the curve of this radioactive count over time. These two factors can be directly used to assess the patency of airways at all levels.
[0102] The formula for calculating the average standard uptake of radiotracer in lung tissue during the stable phase of radioactivity counting is as follows:
[0103] SUV = C / (D / W)
[0104] Where C is the average uptake of the radiotracer in both lung tissues, D is the injected dose of the radiotracer, W is the patient's weight, and SUV is the average of the standard uptake of the radiotracer in both lung tissues.
[0105] The average uptake of the radioactive tracer in the lung tissue can be determined by the pixels in the image.
[0106] S108, based on the average of peak filling rate, time to peak filling, and standard uptake values of radiotracers in both lung tissues, marks the location, extent, and degree of abnormal lung ventilation on a 3D rendering of the patient's lungs.
[0107] Specifically, the differences between the average of the peak filling rate, the time to peak, and the standard uptake values of the radioactive tracer in both lung tissues and their respective reference values were calculated.
[0108] Determine whether the difference exceeds the preset value;
[0109] If so, identify the corresponding location and mark the location, extent, and degree of abnormal lung ventilation on the 3D rendering of the patient's lungs.
[0110] For example, if the difference exceeds two standard deviations, it indicates an abnormality in lung ventilation in the corresponding area. This abnormality is then marked on a 3D rendering using different colors or grayscale levels to show the location, extent, and severity of the ventilation abnormality. Specifically... Figure 11 , Figure 12 as well as Figure 13 As shown in the diagram, lighter-colored areas represent areas with mildly impaired lung ventilation, while darker-colored areas represent areas with severely impaired lung ventilation.
[0111] One or more technical solutions in the embodiments of the present invention have at least the following technical effects or advantages:
[0112] This invention provides a method for measuring pulmonary ventilation function, comprising: after a patient inhales technetium gas, activating a ring-shaped multi-probe SPECT / CT device to initiate real-time dynamic tomography four-dimensional signal acquisition of single-photon signals; identifying and tracking the patient's respiratory state using an infrared laser camera, and dividing the patient's respiratory cycle into 16 phases according to the amplitude of respiratory movements; acquiring CT structural images of the patient's end-inspiratory breath-hold state and SPECT images of each phase of the respiratory cycle based on the 16 phases; spatially standardizing the SPECT images of each phase of the respiratory cycle according to the SPECT image of the end-expiratory phase to obtain spatially standardized SPECT images; and registering the spatially standardized SPECT images according to the CT structural images to obtain registered SPECT images, so that the registered SPECT images... The contours and spatial locations are consistent with those of the CT structural images. Based on the anatomical landmarks on the CT structural images, radioactivity counts within the regions of interest are extracted from the registered SPECT images, resulting in frame-by-frame curves showing the radioactivity counts over time at the lobe, segment, and voxel levels. Based on these curves, the peak filling rate, time to peak, and average standard uptake values of the radiotracer in the lung tissue during the stable phase are calculated. Using these peak filling rates, time to peak, and average standard uptake values of the radiotracer in the lung tissue, the location, extent, and degree of abnormal lung ventilation are marked on a 3D rendering of the patient's lungs. Through autonomous computer analysis and judgment, the patient's lung ventilation function is objectively and reliably assessed.
[0113] Example 2
[0114] Based on the same inventive concept, the present invention also provides a pulmonary ventilation function testing device, such as... Figure 14 As shown, it includes:
[0115] The acquisition module 1401 is used to activate the annular multi-probe SPECT / CT device to start real-time dynamic tomography four-dimensional signal acquisition of single-photon signals after the patient inhales technetium gas.
[0116] The tracking module 1402 is used to identify and track the patient's respiratory status through an infrared laser camera, and to divide the patient's respiratory cycle into 16 phases according to the amplitude of respiratory movements.
[0117] The acquisition module 1403 is used to acquire CT structural images of the patient at the end of inspiratory breath-holding state and SPECT images of each phase of the respiratory cycle based on the 16 time phases.
[0118] The first module 1404 is used to spatially standardize the SPECT images of each phase of the respiratory cycle according to the SPECT image of the end-expiratory phase to obtain a spatially standardized SPECT image.
[0119] The second obtaining module 1405 is used to register the spatially standardized SPECT image with the CT structural image to obtain a registered SPECT image, so that the outline and spatial position of the CT structural image are consistent with the outline and spatial position of the registered SPECT image.
[0120] The third module 1406 is used to extract the radioactivity count in the region of interest of the registered SPECT image based on the anatomical landmarks on the CT structural image, and obtain the curve of radioactivity count changing with time frame by frame at the three levels of lung lobe, lung segment and voxel.
[0121] The calculation module 1407 is used to calculate the peak filling rate, peak time, and average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase of the radioactive count based on the curve of the radioactive count changing over time.
[0122] The annotation module 1408 is used to annotate the location, extent, and degree of abnormal lung ventilation on a 3D rendering of the patient's lungs based on the peak filling rate, peak time, and the average value of the standard uptake of the radioactive tracer in the lung tissue.
[0123] In one alternative implementation, the method further includes a preparation phase, specifically comprising:
[0124] Connect the technetium gas generator mask to the oxygen tubing, turn on the technetium generator while controlling the oxygen supply, and guide the patient to perform multiple Cheyne-Stokes breaths.
[0125] In one optional implementation, it further includes: a scattering correction module, used for
[0126] Scatter correction was performed on the SPECT images of each phase of the respiratory cycle.
[0127] In one alternative implementation, the first receiving module 1404 is configured to:
[0128] An infrared laser camera is used to collect the three-dimensional coordinate position changes of radioactive tracer points in the patient's lungs at different phases of the respiratory cycle, and a displacement vector is generated. The displacement vector includes translation, rotation, and scaling parameters.
[0129] Based on the displacement vector, the data coordinates of the SPECT images at each phase of the respiratory cycle are mapped according to the data coordinates of the SPECT images at the end of the expiration phase to obtain spatially standardized SPECT images.
[0130] In one optional implementation, it further includes: an attenuation correction module, used for:
[0131] Based on the CT structural image, an attenuation-corrected μ map is generated;
[0132] Based on the attenuation correction μ map, the registered SPECT image is subjected to frame-by-frame attenuation correction to obtain a corrected SPECT image.
[0133] In one alternative implementation, the third obtaining module 1406 is used for:
[0134] Based on the CT structural images, the anatomical landmarks of the lobes and segments of both lungs were determined.
[0135] Based on the anatomical landmarks, the regions of interest for lung lobes and lung segments in the registered SPET images are delineated and segmented.
[0136] Based on the region of interest, the corresponding radioactivity counts are extracted, and a frame-by-frame curve of the radioactivity counts over time is generated at the three levels of lung lobe, lung segment, and voxel.
[0137] In one alternative implementation, the calculation module 1407 specifically calculates the average value of the standard uptake of the radiotracer in the lung tissue during the stable phase as follows:
[0138] SUV = C / (D / W)
[0139] Where C is the average uptake of radioactive tracer in both lung tissues, D is the injection dose, W is the patient's weight, and SUV is the average of the standard uptake of radioactive tracer in both lung tissues.
[0140] In one alternative implementation, the annotation module 1408 is used for:
[0141] The differences between the average values of the peak filling rate, time to peak, and standard uptake values of the radioactive tracer in the bilateral lung tissue and their respective reference values are calculated.
[0142] Determine whether the difference exceeds a preset value;
[0143] If so, identify the corresponding location and mark the location, extent, and degree of abnormal lung ventilation on the 3D rendering of the patient's lungs.
[0144] Example 3:
[0145] Based on the same inventive concept, embodiments of the present invention provide a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the steps of the above-described method for measuring pulmonary ventilation function.
[0146] The algorithms and displays provided herein are not inherently related to any particular computer, virtual system, or other device. Various general-purpose systems can also be used in conjunction with the teachings herein. The required structure for constructing such systems is apparent from the above description. Furthermore, this invention is not directed to any particular programming language. It should be understood that the contents of the invention described herein can be implemented using various programming languages, and the above description of specific languages is for the purpose of disclosing the best mode of implementation of the invention.
[0147] Numerous specific details are set forth in the specification provided herein. However, it will be understood that embodiments of the invention may be practiced without these specific details. In some instances, well-known methods, structures, and techniques have not been shown in detail so as not to obscure the understanding of this specification.
[0148] Similarly, it should be understood that, in order to simplify the invention and aid in understanding one or more of the various inventive aspects, in the above description of exemplary embodiments of the invention, various features of the invention are sometimes grouped together in a single embodiment, figure, or description thereof. However, this disclosure should not be construed as reflecting an intention that the claimed invention requires more features than are explicitly recited in each embodiment. Rather, as reflected in each embodiment, inventive aspects lie in fewer than all features of the single foregoing disclosed embodiment. Therefore, the claims, following the detailed description, are hereby expressly incorporated into this detailed description, wherein each claim itself is a separate embodiment of the invention.
[0149] Those skilled in the art will understand that modules in the device of the embodiments can be adaptively changed and placed in one or more devices different from that embodiment. Modules, units, or components in the embodiments can be combined into a single module, unit, or component, and further, they can be divided into multiple sub-modules, sub-units, or sub-components. Except where at least some of such features and / or processes or units are mutually exclusive, any combination can be used to combine all features disclosed in this specification (including the accompanying claims, abstract, and drawings) and all processes or units of any method or device so disclosed. Unless expressly stated otherwise, each feature disclosed in this specification (including the accompanying claims, abstract, and drawings) may be replaced by an alternative feature that serves the same, equivalent, or similar purpose.
[0150] Furthermore, those skilled in the art will understand that although some embodiments herein include certain features included in other embodiments but not others, combinations of features from different embodiments are meant to be within the scope of the invention and form different embodiments. For example, in the specific implementation, any of the claimed embodiments can be used in any combination.
[0151] The various component embodiments of the present invention can be implemented in hardware, or as software modules running on one or more processors, or a combination thereof. Those skilled in the art will understand that microprocessors or digital signal processors (DSPs) can be used in practice to implement some or all of the functions of some or all of the components in the pulmonary ventilation function measuring device according to embodiments of the present invention. The present invention can also be implemented as a device or apparatus program (e.g., a computer program and computer program product) for performing part or all of the methods described herein. Such programs implementing the present invention can be stored on a computer-readable medium or can be in the form of one or more signals. Such signals can be downloaded from an Internet website, provided on a carrier signal, or provided in any other form.
[0152] It should be noted that the above embodiments are illustrative of the invention and not restrictive, and that those skilled in the art can devise alternative embodiments without departing from the scope of the appended claims. In the claims, any reference signs placed between parentheses should not be construed as limiting the claims. The word "comprising" does not exclude the presence of elements or steps not listed in the claims. The word "a" or "an" preceding an element does not exclude the presence of a plurality of such elements. The invention can be implemented by means of hardware comprising several different elements and by means of a suitably programmed computer. In the unit claims enumerating several means, several of these means may be embodied by the same item of hardware. The use of the words first, second, and third, etc., does not indicate any order. These words can be interpreted as names.
Claims
1. A method for measuring pulmonary ventilation function, characterized in that, include: After the patient inhales technetium gas, the annular multi-probe SPECT / CT device is activated to initiate the real-time dynamic tomography four-dimensional signal acquisition of single-photon signals; The patient's respiratory status is identified and tracked using an infrared laser camera, and the patient's respiratory cycle is divided into 16 phases according to the amplitude of respiratory movements. Based on the 16 time phases, CT structural images of the patient at the end of inspiration and SPECT images of each time phase of the respiratory cycle were acquired. The SPECT images of each phase of the respiratory cycle are spatially standardized according to the SPECT images of the end-expiratory phase to obtain spatially standardized SPECT images. The spatially standardized SPECT image is registered with the CT structural image to obtain a registered SPECT image, so that the outline and spatial position of the registered SPECT image are consistent with the outline and spatial position of the CT structural image. Based on the anatomical landmarks on the CT structural images, the radioactivity counts in the regions of interest are extracted from the registered SPECT images to obtain the frame-by-frame curves of radioactivity counts over time at the three levels of lung lobe, lung segment, and voxel. Based on the curve of the radioactivity count over time, the peak filling rate, time to peak, and average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase were calculated. Based on the average of the peak filling rate, time to peak filling, and standard uptake values of the radioactive tracer in both lung tissues, the location, extent, and degree of abnormal lung ventilation are marked on a 3D rendering of the patient's lungs.
2. The method as described in claim 1, characterized in that, After the patient inhales technetium gas, and before the annular multi-probe SPECT / CT device is activated to begin real-time dynamic tomography of single-photon signals for four-dimensional signal acquisition, the following steps are also included: Connect the technetium gas generator mask to the oxygen tubing, turn on the technetium generator while controlling the oxygen supply, and guide the patient to perform multiple Cheyne-Stokes breaths.
3. The method as described in claim 1, characterized in that, After acquiring CT structural images of the patient at the end of inspiration and SPECT images of each phase of the respiratory cycle based on the 16 time phases, the process further includes: Scatter correction was performed on the SPECT images of each phase of the respiratory cycle.
4. The method as described in claim 1, characterized in that, The SPECT images of each phase of the respiratory cycle are spatially normalized according to the SPECT image of the end-expiratory phase to obtain spatially normalized SPECT images, including: An infrared laser camera is used to collect the three-dimensional coordinate position changes of radioactive tracer points in the patient's lungs at different phases of the respiratory cycle, and a displacement vector is generated. The displacement vector includes translation, rotation, and scaling parameters. Based on the displacement vector, the data coordinates of the SPECT images at each phase of the respiratory cycle are mapped according to the data coordinates of the SPECT images at the end of the expiration phase to obtain spatially standardized SPECT images.
5. The method as described in claim 1, characterized in that, After registering the spatially normalized SPECT image with the CT structural image to obtain the registered SPECT image, the process further includes: Based on the CT structural image, an attenuation-corrected μ map is generated; Based on the attenuation correction μ map, the registered SPECT image is subjected to frame-by-frame attenuation correction to obtain a corrected SPECT image.
6. The method as described in claim 1, characterized in that, Based on the anatomical landmarks on the CT structural images, radioactivity counts within the regions of interest are extracted from the registered SPECT images, resulting in frame-by-frame curves showing the radioactivity counts over time at the lobe, segment, and voxel levels, including: Based on the CT structural images, the anatomical landmarks of the lobes and segments of both lungs were determined. Based on the anatomical landmarks, the regions of interest for lung lobes and lung segments in the registered SPET images are delineated and segmented. Based on the region of interest, the corresponding radioactivity counts are extracted, and a frame-by-frame curve of the radioactivity counts over time is generated at the three levels of lung lobe, lung segment, and voxel.
7. The method as described in claim 1, characterized in that, Based on the curve of the radioactivity count changing over time, the peak filling rate, time to peak, and average value of the standard uptake of the radioactive tracer in the lung tissue during the stable phase were calculated. Specifically, the average value of the standard uptake of the radioactive tracer in the lung tissue during the stable phase was calculated as follows: SUV = C / (D / W) Where C is the average uptake of radioactive tracer in both lung tissues, D is the injection dose, W is the patient's weight, and SUV is the average of the standard uptake of radioactive tracer in both lung tissues.
8. The method as described in claim 1, characterized in that, Based on the average of the peak filling rate, time to peak filling, and standard uptake values of the radiotracer in both lung tissues, the location, extent, and degree of abnormal lung ventilation are marked on a 3D rendering of the patient's lungs, including: The differences between the average values of the peak filling rate, time to peak, and standard uptake values of the radioactive tracer in the bilateral lung tissue and their respective reference values are calculated. Determine whether the difference exceeds a preset value; If so, identify the corresponding location and mark the location, extent, and degree of abnormal lung ventilation on the 3D rendering of the patient's lungs.
9. A device for measuring pulmonary ventilation function, characterized in that, include: The acquisition module is used to activate the annular multi-probe SPECT / CT device to acquire four-dimensional signals of real-time dynamic tomography of single-photon signals after the patient inhales technetium gas. The tracking module is used to identify and track the patient's respiratory status using an infrared laser camera, and divides the patient's respiratory cycle into 16 phases according to the amplitude of respiratory movements. The acquisition module is used to acquire CT structural images of the patient at the end of inspiratory breath-holding state and SPECT images of each phase of the respiratory cycle based on the 16 time phases. The first obtaining module is used to spatially standardize the SPECT images of each phase of the respiratory cycle according to the SPECT image of the end-expiratory phase, so as to obtain a spatially standardized SPECT image. The second obtaining module is used to register the spatially standardized SPECT image with the CT structural image to obtain a registered SPECT image, so that the outline and spatial position of the CT structural image are consistent with the outline and spatial position of the registered SPECT image. The third module is used to extract the radioactivity count in the region of interest of the registered SPECT image based on the anatomical landmarks on the CT structural image, and obtain the curve of radioactivity count changing with time frame by frame at the three levels of lung lobe, lung segment, and voxel. The calculation module is used to calculate the peak filling rate, peak time, and average value of the standard uptake of radioactive tracer in the lung tissue during the stable phase, based on the curve of the radioactive count changing over time. The annotation module is used to annotate the location, extent, and degree of abnormal lung ventilation on a 3D rendering of the patient's lungs based on the peak filling rate, peak time, and the average value of the standard uptake of the radiation tracer in the lung tissue.
10. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the program is executed by the processor, it implements the method as described in any one of claims 1 to 8.