Dosage Adjustment Method, Device, Computer Equipment and Readable Storage Medium

Abstract

The present application relates to a dose adjustment method, device, computer device, and readable storage medium. The method includes: obtaining plain film data of an area of interest, obtaining plain film information of each section of an object to be scanned based on the plain film data, determining at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, determining the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals, and performing scanning using the radiation dose. The method of the present application introduces the collimation width factor to optimize the radiation dose difference at the junction of each CT scan circle and weaken the image difference at the junction.

Description

Technical Field

[0001] This application relates to the field of medical image technology, and particularly to a dose adjustment method, device, computer device, and readable storage medium. Background Art

[0002] CT dose modulation scanning technology refers to a technology that continuously adjusts the scanning dose according to different patients, different scanning parts, etc. during the scanning process. This technology can reduce the radiation dose while ensuring the image quality and improve the noise consistency in the Z direction of the image. During the dose modulation process, the attenuation size of the unscanned position is usually estimated based on the attenuation information of the known scanning position, and then an appropriate scanning dose is recommended.

[0003] In actual situations, each time the X-ray is emitted, the range of the collimation width will be covered in the Z direction. When the collimation width is large, it often leads to a large difference in dose between two adjacent scanning positions, resulting in a large difference in the images at the junction of the two adjacent scanning positions, and further resulting in poor image consistency. Summary of the Invention

[0004] To solve the above problems, the embodiments of this application provide a dose adjustment method, device, computer device, and readable storage medium to optimize the dose difference of the X-ray emission at the junction, weaken the image difference at the junction, and obtain a better image effect.

[0005] The embodiments of this application adopt the following technical solutions:

[0006] In the first aspect, a dose adjustment method is provided, and the method includes:

[0007] Obtain the flat panel data of the region of interest, and obtain the flat panel information of each section of the object to be scanned based on the flat panel data;

[0008] Determine at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determine the X-ray emission dose of each tomographic scanning interval according to the flat panel information of each section corresponding to each tomographic scanning interval and the adjacent flat panel information of the adjacent tomographic scanning intervals;

[0009] Perform scanning using the X-ray emission dose.

[0010] In the second aspect, a dose adjustment device is provided, and the device includes:

[0011] A flat panel dose determination unit, configured to obtain the flat panel data of the region of interest, and obtain the flat panel information of each section of the object to be scanned based on the flat panel data;

[0012] A radiation dose determination unit, configured to determine at least two adjacent tomographic scanning intervals according to a scanning direction length and a collimation width, and determine the radiation dose for each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals;

[0013] A scanning unit, configured to perform scanning using the radiation dose.

[0014] In a third aspect, an embodiment of the present application further provides a computer device, including a memory, a processor, and a computer program stored in the memory and executable on the processor. When the processor executes the computer program, the steps of the above dose adjustment method are implemented.

[0015] In a fourth aspect, an embodiment of the present application further provides a computer-readable storage medium. The computer-readable storage medium stores a computer program, and when the computer program is instructed by the processor, the steps of the above dose adjustment method are implemented.

[0016] At least one of the above technical solutions adopted in the embodiments of the present application can achieve the following beneficial effects:

[0017] The dose adjustment method provided by the present application obtains the plain film data of the region of interest, obtains the plain film information of each section of the object to be scanned based on the plain film data, determines at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determines the radiation dose for each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals, and performs scanning using the radiation dose. The dose adjustment method provided by the present application introduces the collimation width factor to optimize the radiation dose difference at the junction of each CT scan circle, weakens the image difference at the junction, and obtains a better image effect. This method is most obvious in the tomographic scanning of wide slices and is also applicable to small slices and spiral scans. Description of the Drawings

[0018] The drawings described herein are used to provide a further understanding of the present application and constitute a part of the present application. The schematic embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation to the present application. In the drawings:

[0019] Figure 1 A brief component diagram of a CT machine system in the prior art is shown;

[0020] Figure 2 A flowchart of a dose adjustment method according to an embodiment of the present application is shown;

[0021] Figure 3 A schematic diagram of adjacent tomographic scanning intervals according to an embodiment of the present application is shown;

[0022] Figure 4 Schematic diagram showing the radiation dose of each tomographic scan interval according to an embodiment of the present application;

[0023] Figure 5 Schematic diagram showing the tube angle according to an embodiment of the present application;

[0024] Figure 6 Schematic diagram showing the flat - film attenuation corresponding to each section according to an embodiment of the present application;

[0025] Figure 7 Graph showing the relationship between the flat - film dose corresponding to each section according to an embodiment of the present application;

[0026] Figure 8 Schematic diagram showing the overall characteristic value of the flat - film information of each section corresponding to each tomographic scan interval according to an embodiment of the present application;

[0027] Figure 9 Schematic flowchart showing the dose adjustment method according to another embodiment of the present application;

[0028] Figure 10 Schematic diagram showing the structure of the dose adjustment device according to an embodiment of the present application;

[0029] Figure 11 Schematic diagram showing the structure of a computer device according to an embodiment of the present application. Detailed implementation manners

[0030] To make the objectives, technical solutions, and advantages of the present application clearer, the technical solutions of the present application will be clearly and completely described below in conjunction with the specific embodiments of the present application and the corresponding drawings. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the scope of protection of the present application.

[0031] The following will detail the technical solutions provided by each embodiment of the present application in conjunction with the drawings.

[0032] The concept of the present application lies in that during the dose modulation process, in addition to considering the attenuation of the scanning position itself, the image differences at the junction due to the collimation width are also considered to obtain better image effects. Figure 1 Shows a simplified component diagram of a CT machine system in the prior art. According to Figure 1As shown, the CT system mainly includes an X-ray tube, a detector, and a high-voltage system. The detector generally consists of hundreds of channels. The main console computer receives the detector data, performs calculations, and sends the beam dose control command to the high-voltage system; the high-voltage system receives this command and controls the X-ray tube.

[0033] In Figure 1 the CT system shown, Figure 2 a dose adjustment method proposed in an embodiment of the present application is shown. According to Figure 2 what is shown, this method includes steps S210 to S230:

[0034] Step S210, obtain the plain film data of the region of interest, and obtain the plain film information of each section of the object to be scanned based on the plain film data.

[0035] The present application first obtains the plain film data of the region of interest. This plain film data can be but is not limited to being obtained based on plain film scanning, or retrieving historical data stored in a database. Based on the plain film data, the plain film information of each section of the object to be scanned is obtained. The plain film information includes but is not limited to plain film attenuation or plain film dose. The object to be scanned can be but is not limited to any object including a human body, an animal, a phantom, etc.

[0036] Step S220, determine at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determine the beam dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals.

[0037] When performing CT scanning, due to the constraint of the collimation width, the scanning direction length needs to be scanned in multiple circles, and each circle of scanning covers a tomographic scanning interval. According to the collimation width, the scanning direction length (which is also the length of the region of interest in the Z direction, where the Z direction is the length direction of the CT scanning chamber) is divided into at least two adjacent tomographic scanning intervals, and each tomographic scanning interval includes multiple sections within its scanning direction position range. According to the plain film information of each section determined in step S210, the adjacent plain film information of adjacent tomographic scanning intervals is determined, so as to determine the beam dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals.

[0038] There is often a gradient in the theoretical beam dose corresponding to each tomographic scanning interval, resulting in an obvious difference in the theoretical beam dose around the connection point between two adjacent tomographic scanning intervals, and further resulting in poor image consistency. Therefore, the theoretical beam dose corresponding to each tomographic scanning interval is corrected by the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals, and the dose gradient between adjacent tomographic scanning intervals is reduced.

[0039] After calibration, the difference between the radiation doses released in any two adjacent tomographic scan intervals is less than the difference between the theoretical radiation doses released in these two adjacent tomographic scan intervals. For example, taking two tomographic scan intervals as an example, the difference between the theoretical radiation doses released in the two tomographic scan intervals is the first difference; after calibration, the difference between the radiation doses released in the two tomographic scan intervals is the second difference; the second difference is less than the first difference. It should be noted that the radiation dose released in each tomographic scan interval in the embodiments of the present invention can be as Figure 4 shown, with the second difference existing, or the second difference may not exist (i.e., the second difference can be zero), that is to say, the radiation doses released in the two tomographic scan intervals can be equal.

[0040] Figure 3 FIG. shows a schematic diagram of adjacent tomographic scan intervals according to an embodiment of the present application. Figure 3 For the sake of convenient description, this is only a schematic example, and the present application is not limited thereto. Combining Figure 3 as shown, the length of the scanning direction a - d is Length, and the collimation width is Width. By taking the integer part of the ratio of the scanning direction length to the collimation width downward, two adjacent tomographic scan intervals are determined. The two adjacent tomographic scan intervals are b - c and c - d respectively. That is to say, during CT scanning, the distance between b - d needs to be scanned twice. The first scan range is b - c, and the second scan range is c - d. It should be noted that the adjacent tomographic scan intervals in the embodiments of the present invention can be adjacent with the boundaries of the scan intervals shared as Figure 3 shown, and also include that there is a certain interval between the scan intervals, and the reconstruction positions on both sides of the adjacent interval share at least part of the data with each other.

[0041] Figure 4 FIG. shows a schematic diagram of the radiation dose released in each tomographic scan interval according to an embodiment of the present application. As Figure 4 shown, there is a large difference between the first theoretical radiation dose in the b - c region and the second theoretical radiation dose in the c - d region. If the radiation is directly released according to the first theoretical radiation dose and the second theoretical radiation dose, it will cause obvious inconsistencies at the adjacent positions c around c - (located in b - c) and c + (located in c - d). Therefore, through the flat film information of each section corresponding to each tomographic scan interval and the adjacent flat film information of adjacent tomographic scan intervals, the first theoretical radiation dose corresponding to the b - c region is calibrated to obtain the first radiation dose, and the second theoretical radiation dose corresponding to the c - d region is calibrated to obtain the second radiation dose, so that the difference between the first radiation dose and the second radiation dose is less than the difference between the first theoretical radiation dose and the second theoretical radiation dose, thereby making there be no obvious mutation at the adjacent positions around c.

[0042] Step S230: Perform scanning using the radiation dose for wire placement.

[0043] After obtaining the radiation dose for wire placement in each tomographic scanning interval, use the radiation dose for wire placement to scan the object to be scanned. The dose can be adjusted by adjusting the tube current, so as to achieve scanning with the radiation dose for wire placement in each tomographic scanning interval. Even when the difference in the radiation dose for wire placement in each tomographic scanning interval is zero (i.e., the radiation dose for wire placement in each tomographic scanning interval is equal), scanning can be performed with a constant dose, thereby greatly weakening the image difference at the junction of each tomographic scanning interval.

[0044] As can be seen from Figure 2 the method shown, the dose adjustment method provided by this application obtains the plain film data of the region of interest, and obtains the plain film information of each section of the object to be scanned based on the plain film data; determines at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determines the radiation dose for wire placement in each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals; performs scanning using the radiation dose for wire placement. The dose adjustment method provided by this application introduces the collimation width factor to optimize the difference in the radiation dose for wire placement at the junction of each circle in CT scanning, weakens the image difference at the junction, and obtains a better image effect. This method is most obvious in the tomographic scanning of wide slices, and is also applicable to small slices and spiral scanning.

[0045] In some embodiments of this application, in the above method, the plain film information includes: plain film dose and / or plain film attenuation. Obtaining the plain film information of each section of the object to be scanned based on the plain film data includes: obtaining the plain film dose of each section of the object to be scanned based on the plain film data; and / or, obtaining the plain film attenuation of each section of the object to be scanned based on the plain film data.

[0046] The plain film information may include plain film dose and / or plain film attenuation. The method of obtaining the plain film dose and / or plain film attenuation of each section of the object to be scanned based on the plain film data is relatively mature. The following is only a brief introduction taking the plain film scanning of the human body as an example. Figure 5 shows a schematic diagram of the tube angle according to an embodiment of this application, Figure 6 shows a schematic diagram of the plain film attenuation corresponding to each section according to an embodiment of this application, Figure 7 shows a relationship diagram of the plain film dose corresponding to each section according to an embodiment of this application. According to Figures 5 to 7 shown, the above step S210 is elaborated in detail.

[0047] Perform a plain film scan on the scanning object in the scanning direction. Taking the human body as an example, the Z direction of the human body is the scanning direction. The Z direction of the human body is the parallel direction connecting the head and feet of the human body, that is, the Z direction can be the direction from the head of the human body to the feet or the direction from the feet of the human body to the head, and it is also the length direction of the scanning cavity. The scanning section is a cross-section of the human body perpendicular to the Z direction at a certain position in the Z direction. Combined with Figure 3 As shown, the range of the plain film scan in the scanning direction of the human body is a to d, and the data is sampled along the scanning direction (the bed advancing and retreating direction), and each sample is a section.

[0048] Extract the plain film attenuation of each section. The plain film attenuation can but is not limited to include the attenuation information of the filter or the attenuation information corrected by the human body size. Determine the plain film dose of each section according to the plain film attenuation. Combined with Figure 5 and Figure 6 As shown, select the positive plain film, that is, the tube is directly above at 0°, and the clockwise angle increases. The scanning range is a to d, the data is sampled along the scanning direction, each sample is a section, and the plain film attenuation of each section is extracted. Figure 6 The abscissa of

[0049] For each section, determine the attenuation area of the equivalent circular water phantom corresponding to this section according to the plain film attenuation of this section. The attenuation area of the equivalent circular water phantom corresponding to this section can be obtained by the following formula 1:

[0050]

[0051] where, μ i is the average attenuation coefficient of the i-th detection channel, l i is the attenuation path of the i-th detection channel, i = 0, 1,......, N - 1, N is the number of detection channels covered by the wire laying position, Δ is the distance between the centers of adjacent detection channels, where, R is the rotation radius, and α is the fan angle formed between the detector and the tube.

[0052] Determine the diameter of the equivalent circular water phantom corresponding to this section according to the attenuation area of the equivalent circular water phantom corresponding to this section. The diameter of the equivalent circular water phantom corresponding to this section can be obtained by the following formula 2:

[0053]

[0054] where, μ water is the attenuation coefficient of water.

[0055] Determine the plain film dose of this section according to the diameter of the equivalent circular water phantom corresponding to this section. The plain film dose of this section can be obtained by the following formula 3:

[0056]

[0057] Among them, mAs base is the reference dose, D base is the reference equivalent water phantom diameter, and cof is the adjustment coefficient.

[0058] By using the above formulas 1 - 3 to sequentially determine the plain film dose of each section, the relationship diagram of the plain film dose corresponding to each section as shown in Figure 7 can be obtained.

[0059] Figure 7 The plain film dose distribution curve along the scanning direction is shown, Figure 7 the abscissa of which is the position in the scanning direction (i.e., each consecutive section), Figure 7 and the ordinate is the plain film dose corresponding to each section. The unit of dose is milligray (mGy). However, in actual use, when other conditions remain unchanged, the product mAs of the current value (mA) and the scanning time (s) can be used to measure the dose magnitude, that is, the larger the mAs, the larger the dose. Or the dose magnitude can also be measured by the voltage value or other parameters, which is not specifically limited here.

[0060] In some embodiments of the present application, in the above method, at least two adjacent tomographic scanning intervals are determined according to the scanning direction length and the collimation width, including: determining the number of scanning circles according to the ratio of the scanning direction length to the collimation width; and determining at least two adjacent tomographic scanning intervals according to the number of scanning circles.

[0061] Still referring to Figure 3 shown, the length of the scanning direction a - d is Length, and the collimation width is Width. The number of scanning circles is determined according to the ratio of the scanning direction length to the collimation width. For example, the number of scanning circles can be obtained through the following formula 4:

[0062]

[0063] Therefore, by taking the integer part of the ratio of the scanning direction length to the collimation width downward, two adjacent tomographic scanning intervals are determined. The two adjacent tomographic scanning intervals are b - c and c - d respectively. The two tomographic scanning intervals are adjacent at point c.

[0064] In some embodiments of the present application, in the above method, according to the plain film information of each section corresponding to each tomographic scanning interval, including: determining the overall characteristic value of the plain film information of each section corresponding to each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval; among them, the overall characteristic value includes the average value or the maximum value.

[0065] For each tomographic scanning interval, the overall characteristic value can be determined based on the plain film information of each section included therein. The overall characteristic value may include an average value or a maximum value. The following takes the plain film information as the plain film dose for detailed description.

[0066] In an alternative scenario, the overall characteristic value of the plain film dose for each section corresponding to the tomographic scanning interval can be obtained through the following formula 5:

[0067]

[0068] In an alternative scenario, the overall characteristic value of the plain film dose for each section corresponding to the tomographic scanning interval can be obtained through the following formula 6:

[0069] mAs y =max(mAs scan ) (Formula 6).

[0070] Through the above formula 5 or formula 6, the overall characteristic value of the plain film information for each section corresponding to each tomographic scanning interval is determined in sequence.

[0071] Figure 8 Shows a schematic diagram of the overall characteristic value of the plain film information for each section corresponding to each tomographic scanning interval in an embodiment of the present application. In Figure 8 the overall characteristic value is the average value.

[0072] In some embodiments of the present application, in the above method, according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals, determining the radiation dose for each tomographic scanning interval includes: determining the image parameters of each tomogram according to the overall characteristic value of the plain film information of each section corresponding to each tomographic scanning interval; assigning weight coefficients to the image parameters of each tomogram; wherein, in each tomographic scanning interval, the weight coefficients of the image parameters of a preset number of tomograms close to the adjacent point are greater than the weight coefficients of the image parameters of other tomograms; parsing the radiation dose of each tomographic scanning interval based on a preset processing rule; wherein the radiation dose minimizes the variance of the product of the image parameters of each tomogram and the weight coefficient of the image parameter.

[0073] In order to weaken the inconsistency of the images at the junction of two adjacent scanning positions, the following gives the first method for optimizing the dose by imposing constraints on the image parameters to determine the scanning dose for each tomographic scanning interval. The image parameters may include, but are not limited to, the image noise value or the image resolution. The methods where the image parameters are the image noise value or the image resolution are basically the same. The following takes the image parameter as the image noise value for detailed description.

[0074] First, in each tomographic scanning interval, according to the overall characteristic value of the plain film information of each section, determine the image noise value of each tomogram corresponding to each tomographic scanning interval. Taking the plain film information as the plain film dose as an example, the image noise value of each tomogram corresponding to each tomographic scanning interval can be obtained through the following formula 7:

[0075]

[0076] where μ water is the attenuation coefficient of water, D scan,x is the diameter of the equivalent circular water phantom corresponding to each tomogram, D scan,x can be, but is not limited to, obtained by the average value of the diameters of the equivalent circular water phantoms corresponding to multiple sections included in each tomogram, mAs y is the overall characteristic value of the plain film doses of each section in each tomographic scanning interval, x = 1, 2,......, n, where n is the number of tomograms, M is the number of scanning circles, wherein, Width is the collimation width, ImgThick is the image thickness, and Length is the scanning direction length.

[0077] Assign weight coefficients to the image noise values of each tomogram. Since this application focuses on the connection points of adjacent tomographic scanning intervals, different weight coefficients are applied to the image noise values at each tomogram position.

[0078] Combined with Figure 3 as shown, in the b - c region, higher weight coefficients are assigned to the image noise values of several tomograms closer to point c. For example, in the b - c region, higher weight coefficients of 10 are assigned to the image noise values of 5 tomograms closer to point c, and general weight coefficients of 1 are assigned to the image noise values of other tomograms. Another example is that in the b - c region, weight coefficients of 10, 9, and 8 are respectively assigned to the image noise values of 3 tomograms closer to point c from near to far from point c, and weight coefficients of 1 are assigned to the image noise values of other tomograms. That is to say, as long as it is ensured that in the b - c region, the weight coefficients of the image noise values of a preset number of tomograms close to the adjacent point are greater than the weight coefficients of the image noise values of other tomograms, it is not limited that the weight coefficients of the image noise values of the preset number of tomograms are the same, and / or the weight coefficients of the image noise values of other tomograms are the same.

[0079] In the c-d region, the method of assigning weight coefficients to the image noise values of each corresponding fault is the same as that in the b-c region, which will not be elaborated here. Additionally, it is not limited that the number of faults assigned higher weight coefficients in the b-c region is the same as the number of faults assigned higher weight coefficients in the c-d region, nor is it limited that the weight coefficients assigned to the image noise values of each fault in the b-c region are the same as the weight coefficients assigned to the image noise values of each fault in the c-d region. Increasing the weight coefficients of the image noise values at the positions around the adjacent points can make the radiation dose pay more attention to the noise consistency at the sensitive positions. The above examples are only illustrative preferences, and this application is not limited thereto.

[0080] Based on the preset processing rules, analyze the radiation dose for each tomographic scanning interval, so that the variance of the product of the image noise value of each fault and the weight coefficient of the image noise value is minimized. The radiation dose can be analyzed through the following formula 8:

[0081]

[0082] where W y,x is the weight coefficient of the image noise value of each fault corresponding to each tomographic scanning interval.

[0083] By analyzing f(mAs), the variance of the product of the image noise value of each fault and the weight coefficient of the image noise value is minimized, thereby obtaining an appropriate radiation dose. The analysis method of f(mAs) can be, but is not limited to, determining the radiation dose that minimizes the variance of the product of the image noise value of each fault and the weight coefficient of the image noise value in a gradient manner, or enumerating the plain film doses of each section to determine the radiation dose that minimizes the variance of the product of the image noise value of each fault and the weight coefficient of the image noise value, etc. This application does not make specific limitations on the analysis method of f(mAs). The radiation doses obtained for each tomographic scanning interval by analyzing the radiation dose for each tomographic scanning interval based on the preset processing rules are equal, that is, after correction, scanning is performed at a constant dose. The above analysis method is a preferred implementation manner, but this application is not limited thereto.

[0084] In some embodiments of the present application, in the above method, according to the plain film information of each cross-section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals, determining the radiation dose for each tomographic scanning interval includes: determining the image parameters of each tomogram according to the overall characteristic value of the plain film information of each cross-section corresponding to each tomographic scanning interval; parsing the radiation dose for each tomographic scanning interval based on a preset processing rule; wherein, the radiation dose is such that the difference in image parameters between the tomogram close to the adjacent point in the first tomographic scanning interval and the tomogram close to the adjacent point in the second tomographic scanning interval among any two adjacent tomographic scanning intervals is less than the maximum difference between the image parameters of each tomogram corresponding to the first tomographic scanning interval and less than the maximum difference between the image parameters of each tomogram corresponding to the second tomographic scanning interval; and / or, the radiation dose is such that the variance of the image parameters of each tomogram in the tomographic scanning interval is minimized.

[0085] The following gives a second method for determining the radiation dose for each tomographic scanning interval. The image parameters may include, but are not limited to, the image noise value or the image resolution. The methods where the image parameter is the image noise value or the image resolution are basically the same, and the following will detail the case where the image parameter is the image noise value. Among them, the tomogram close to the adjacent point in the first tomographic scanning interval may be the first tomogram close to the adjacent point within the first tomographic scanning interval, and the tomogram close to the adjacent point in the second tomographic scanning interval is the first tomogram close to the adjacent point within the second tomographic scanning interval. That is to say, the tomogram close to the adjacent point in the first tomographic scanning interval and the tomogram close to the adjacent point in the second tomographic scanning interval are adjacent.

[0086] Another set of constraint conditions can be given, and based on the preset processing rule, parsing this set of constraint conditions to determine the radiation dose for each tomographic scanning interval. Taking Figure 3 the two adjacent tomographic scanning intervals b - c and c - d shown as an example, this method will be introduced in detail.

[0087] In the b - c region, the first radiation dose corresponding to this tomographic scanning interval is parsed, and according to the first radiation dose, the image noise value of each tomogram corresponding to the b - c region is determined. Among the image noise values of each tomogram corresponding to the b - c region, the largest image noise value is the first maximum image noise value, the smallest image noise value is the first minimum image noise value, and the image noise value of the tomogram closest to the adjacent point c is the first adjacent image noise value. The difference between the first maximum image noise value and the first minimum image noise value is the first maximum difference in image noise values.

[0088] In the c-d region, the second beam dose corresponding to the tomographic scanning interval is parsed, and the image noise value of each tomogram corresponding to the c-d region is determined according to the second beam dose. Among the image noise values of each tomogram corresponding to the c-d region, the largest image noise value is the second largest image noise value, the smallest image noise value is the second smallest image noise value, and the image noise value of the tomogram closest to the adjacent point c is the second adjacent image noise value. The difference between the second largest image noise value and the second smallest image noise value is the second maximum image noise value difference.

[0089] The first beam dose and the second beam dose obtained by parsing must satisfy the following conditions:

[0090] The difference between the first adjacent image noise value and the second adjacent image noise value is less than the first maximum image noise value difference and less than the second maximum image noise value difference.

[0091] And / or, the variance of the image noise values of each tomogram corresponding to the b-c region and the variance of the image noise values of each tomogram corresponding to the c-d region are the smallest.

[0092] The parsing method for the first beam dose and / or the second beam dose may, but is not limited to, determining the beam dose that satisfies the above conditions in a gradient manner, or determining the beam dose that satisfies the above conditions by exhaustively listing the plain film doses of each section, etc. The above parsing method is a preferred implementation manner, but the present application is not limited thereto.

[0093] In the dose adjustment method provided by the present application, during the dose modulation process, in addition to considering the attenuation effect of the scanning position itself, the image difference at the scanning junction caused by the collimation width is also considered. By performing CT scanning with the optimized beam dose, a better image effect can be obtained.

[0094] Figure 9 Illustrates the dose adjustment method proposed in another embodiment of the present application. According to Figure 9 As shown, the dose adjustment method of this embodiment includes the following steps S901 to step S910:

[0095] Step S901, obtain the plain film data of the region of interest, and obtain the plain film information of each section of the object to be scanned based on the plain film data; wherein, the plain film information includes plain film attenuation and / or plain film dose.

[0096] Step S902, determine the number of scanning circles according to the ratio of the scanning direction length to the collimation width.

[0097] Step S903, determine at least two adjacent tomographic scanning intervals according to the number of scanning circles.

[0098] Step S904: Determine the overall eigenvalue of the plain film information of each cross-section corresponding to each tomographic scanning interval; wherein, the overall eigenvalue includes the average value or the maximum value.

[0099] Step S905: Determine the image parameters of each tomogram according to the overall eigenvalue of the plain film information of each cross-section corresponding to each tomographic scanning interval; wherein, the image parameters include the image noise value and / or the image resolution.

[0100] Step S906: Assign weight coefficients to the image parameters of each tomogram; wherein, in each tomographic scanning interval, the weight coefficients of the image parameters of a preset number of tomograms close to the adjacent point are greater than the weight coefficients of the image parameters of other tomograms.

[0101] Step S907: Analyze the radiation dose of each tomographic scanning interval based on a preset processing rule; wherein, the radiation dose minimizes the variance of the product of the image parameters of each tomogram and the weight coefficients of the image parameters.

[0102] Alternatively, Step S908: Determine the image parameters of each tomogram according to the overall eigenvalue of the plain film information of each cross-section corresponding to each tomographic scanning interval; wherein, the image parameters include the image noise value and / or the image resolution.

[0103] Step S909: Analyze the radiation dose of each tomographic scanning interval based on a preset processing rule; wherein, the radiation dose makes the difference between the image parameters of the tomogram close to the adjacent point in the first tomographic scanning interval and the tomogram close to the adjacent point in the second tomographic scanning interval less than the maximum difference between the image parameters of each tomogram corresponding to the first tomographic scanning interval, and less than the maximum difference between the image parameters of each tomogram corresponding to the second tomographic scanning interval; and / or, the radiation dose minimizes the variance of the image parameters of each tomogram in the tomographic scanning interval.

[0104] Step S910: Perform scanning using the radiation dose.

[0105] Figure 10 The dose adjustment device proposed in an embodiment of the present application is provided. According to Figure 10 As shown, the device 1000 includes:

[0106] A plain film dose determination unit 1001, configured to obtain the plain film data of the region of interest and obtain the plain film information of each cross-section of the object to be scanned based on the plain film data.

[0107] The present application first obtains the plain film data of the region of interest. The plain film data can be, but is not limited to, obtained based on plain film scanning or retrieved from historical data stored in a database. Based on the plain film data, the plain film information of each section of the object to be scanned is obtained. The plain film information includes, but is not limited to, plain film attenuation and plain film dose. The object to be scanned can be, but is not limited to, any object such as a human body, an animal, a phantom, etc.

[0108] The radiation dose determination unit 1002 is configured to determine at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determine the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals.

[0109] During CT scanning, due to the constraint of the collimation width, the scanning direction length needs to be scanned in multiple circles, and each circle of scanning covers a tomographic scanning interval. According to the collimation width, the scanning direction length is divided into at least two adjacent tomographic scanning intervals, and each tomographic scanning interval includes multiple sections within its scanning direction position range. The plain film information of each determined section is used to determine the adjacent plain film information of adjacent tomographic scanning intervals, so as to determine the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals.

[0110] There is often a gradient in the theoretical radiation dose corresponding to each tomographic scanning interval, resulting in an obvious difference in the theoretical radiation dose around the connection point between two adjacent tomographic scanning intervals, and further resulting in poor image consistency. Therefore, the theoretical radiation dose corresponding to each tomographic scanning interval is corrected by the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals, so as to reduce the dose gradient between adjacent tomographic scanning intervals.

[0111] After correction, the difference between the radiation doses of any two adjacent tomographic scanning intervals is less than the difference between the theoretical radiation doses of the two adjacent tomographic scanning intervals. For example, taking two tomographic scanning intervals as an example, the difference between the theoretical radiation doses of the two tomographic scanning intervals is the first difference; after correction, the difference between the radiation doses of the two tomographic scanning intervals is the second difference; the second difference is less than the first difference. It should be noted that the radiation dose of each tomographic scanning interval in the embodiments of the present invention can be as Figure 4 shown with the existence of the second difference, or there may be no second difference (i.e., the second difference can be zero), that is to say, the radiation doses of the two tomographic scanning intervals can be equal.

[0112] Figure 3 FIG. shows a schematic diagram of adjacent tomographic scanning intervals according to an embodiment of the present application. Figure 3For the sake of illustrative convenience only, the present application is not limited thereto. In combination with Figure 3 As shown, the lengths of the scanning directions a to d are Length, and the collimation width is Width. By taking the integer part of the ratio of the scanning direction length to the collimation width, two adjacent tomographic scanning intervals are determined. The two adjacent tomographic scanning intervals are b to c and c to d respectively. That is to say, during CT scanning, the distance between b and d needs to be scanned twice. The first scanning range is b to c, and the second scanning range is c to d. It should be noted that the adjacent tomographic scanning intervals in the embodiments of the present invention can be adjacent with the boundaries of the scanning intervals shared as shown in Figure 3 shown, or it also includes that there is a certain interval between the scanning intervals, and at least part of the data is shared between the reconstruction positions adjacent to both sides of the interval.

[0113] Figure 4 shows a schematic diagram of the radiation dose for each tomographic scanning interval in an embodiment of the present application. As shown in Figure 4 shown, there is a large difference between the first theoretical radiation dose in the b to c region and the second theoretical radiation dose in the c to d region. If the radiation is directly carried out according to the first theoretical radiation dose and the second theoretical radiation dose, it will cause obvious inconsistencies at c - (located in b to c) and c + (located in c to d) around the adjacent positions of the two scans. Therefore, through the flat film information of each section corresponding to each tomographic scanning interval and the adjacent flat film information of adjacent tomographic scanning intervals, the first theoretical radiation dose corresponding to the b to c region is corrected to obtain the first radiation dose, and the second theoretical radiation dose corresponding to the c to d region is corrected to obtain the second radiation dose, so that the difference between the first radiation dose and the second radiation dose is less than the difference between the first theoretical radiation dose and the second theoretical radiation dose, thereby making there be no obvious mutation at the adjacent positions around c.

[0114] The scanning unit 1003 is used to perform scanning using the radiation dose.

[0115] After obtaining the radiation dose for each tomographic scanning interval, the object to be scanned is scanned using the radiation dose. The dose can be adjusted by adjusting the tube current, so as to achieve scanning with the radiation dose in each tomographic scanning interval. Even when the difference in the radiation dose between each tomographic scanning interval is zero (that is, the radiation doses in each tomographic scanning interval are equal), scanning can be performed with a constant dose, thereby greatly weakening the image difference at the junction of each tomographic scanning interval.

[0116] In some embodiments of the present application, in the above device, the flat film information determination unit 1001 is further used for: obtaining the flat film dose of each section of the object to be scanned based on the flat film data and / or obtaining the flat film attenuation of each section of the object to be scanned based on the flat film data.

[0117] In some embodiments of the present application, in the above-mentioned device, the wire release dose determination unit 1002 further includes: a scan cycle number determination module, configured to determine the scan cycle number according to the ratio of the scan direction length to the collimation width;

[0118] a tomographic scan interval determination module, configured to determine at least two adjacent tomographic scan intervals according to the scan cycle number.

[0119] In some embodiments of the present application, in the above-mentioned device, the wire release dose determination unit 1002 is further configured to: determine an overall characteristic value of the radiograph information of each section corresponding to each tomographic scan interval according to the radiograph information of each section corresponding to each tomographic scan interval; wherein, the overall characteristic value includes an average value or a maximum value.

[0120] In some embodiments of the present application, in the above-mentioned device, the wire release dose determination unit 1002 further includes: an image parameter determination module, configured to determine the image parameters of each tomogram according to the overall characteristic value of the radiograph information of each section corresponding to each tomographic scan interval;

[0121] a weight coefficient determination module, configured to assign a weight coefficient to the image parameters of each tomogram; wherein, in each tomographic scan interval, the weight coefficients of the image parameters of a preset number of tomograms close to the adjacent point are greater than the weight coefficients of the image parameters of other tomograms;

[0122] a wire release dose determination module, configured to analyze the wire release dose of each tomographic scan interval based on a preset processing rule; wherein, the wire release dose minimizes the variance of the product of the image parameters of each tomogram and the weight coefficient of the image parameters.

[0123] In some embodiments of the present application, in the above-mentioned device, the wire release dose determination unit 1002 further includes:

[0124] an image parameter determination module, configured to determine the image parameters of each tomogram according to the overall characteristic value of the radiograph information of each section corresponding to each tomographic scan interval;

[0125] a wire release dose analysis module, configured to analyze the wire release dose of each tomographic scan interval based on a preset processing rule; wherein, the wire release dose makes the difference between the image parameters of the tomogram close to the adjacent point in the first tomographic scan interval and the tomogram close to the adjacent point in the second tomographic scan interval less than the maximum difference between the image parameters of each tomogram corresponding to the first tomographic scan interval, and less than the maximum difference between the image parameters of each tomogram corresponding to the second tomographic scan interval; and / or, the wire release dose minimizes the variance of the image parameters of each tomogram in each tomographic scan interval.

[0126] In some embodiments of the present application, in the above device, the image parameters determined by the image parameter determination module for each tomographic slice corresponding to each tomographic scan interval include: the image noise value of each tomographic slice corresponding to each tomographic scan interval; or, the image resolution of each tomographic slice corresponding to each tomographic scan interval.

[0127] The weight coefficient determination module is further configured to assign a weight coefficient to the image noise value of each tomographic slice; and / or, assign a weight coefficient to the image resolution of each tomographic slice.

[0128] It should be noted that the dose adjustment device can implement the foregoing dose adjustment method one by one, and details thereof will not be described herein again.

[0129] Figure 11 is a schematic structural diagram of a computer device according to an embodiment of the present application. As Figure 11 shown, at the hardware level, the computer device includes a processor, and optionally also includes an internal bus, a network interface, and a memory. Among them, the memory may include a memory, such as a high-speed random access memory (Random-Access Memory, RAM), and may also include a non-volatile memory, such as at least one disk memory, etc. Of course, the computer device may also include other hardware required for other services.

[0130] The processor, network interface, and memory can be interconnected through an internal bus, which can be an ISA (Industry Standard Architecture) bus, a PCI (Peripheral Component Interconnect) bus, or an EISA (Extended Industry Standard Architecture) bus, etc. The bus can be divided into an address bus, a data bus, a control bus, etc. For the sake of convenience of representation, Figure 11 only a bidirectional arrow is shown in, but it does not mean that there is only one bus or one type of bus.

[0131] The memory is used to store programs. Specifically, the program may include program code, and the program code includes computer operation instructions. The memory may include a memory and a non-volatile memory, and provide instructions and data to the processor.

[0132] The processor reads the corresponding computer program from the non-volatile memory into the memory and then runs it, forming a dose adjustment device logically. The processor executes the program stored in the memory and is specifically configured to perform the following operations:

[0133] Obtain the plain film data of the region of interest, and obtain the plain film information of each section of the object to be scanned based on the plain film data;

[0134] Determine at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determine the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals;

[0135] Perform scanning using the radiation dose.

[0136] The above method performed by the dose adjustment device as described in this application Figure 10 can be applied to or implemented by a processor. The processor may be an integrated circuit chip with the ability to process signals. In the implementation process, each step of the above method can be completed by the integrated logic circuit in the hardware of the processor or the instructions in the form of software. The above processor may be a general-purpose processor, including a central processing unit (CPU), a network processor (NP), etc.; it may also be a digital signal processor (DSP), an application specific integrated circuit (ASIC), a field programmable gate array (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components. It can implement or execute the various methods, steps and logic block diagrams disclosed in the embodiments of the present application. The general-purpose processor may be a microprocessor or the processor may also be any conventional processor, etc. The steps of the method disclosed in combination with the embodiments of the present application can be directly embodied as being executed and completed by the hardware decoding processor, or executed and completed by the combination of the hardware and software modules in the decoding processor. The software module may be located in a mature storage medium in the art such as a random access memory, a flash memory, a read-only memory, a programmable read-only memory or an electrically erasable programmable memory, a register, etc. The storage medium is located in the memory, and the processor reads the information in the memory and combines its hardware to complete the steps of the above method.

[0137] The computer device can also execute Figure 10 the method performed by the dose adjustment device in Figure 10 and implement the functions of the dose adjustment device in the embodiments shown. The embodiments of the present application will not be elaborated here.

[0138] The embodiments of the present application also propose a computer-readable storage medium storing one or more programs, and the one or more programs include instructions that, when executed by a computer device including a plurality of application programs, can cause the computer device to execute Figure 10 the method executed by the dose adjustment device in the illustrated embodiment, and specifically used to execute:

[0139] Obtain the plain film data of the region of interest, and obtain the plain film information of each section of the object to be scanned based on the plain film data;

[0140] Determine at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determine the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals;

[0141] Perform scanning using the radiation dose.

[0142] Those skilled in the art should understand that the embodiments of the present application can be provided as a method, a device, or a computer program product. Therefore, the present application can adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment combining software and hardware aspects. Moreover, the present application can adopt the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program code.

[0143] The present application is described with reference to the flowcharts and / or block diagrams of methods, devices (systems), and computer program products according to the embodiments of the present application. It should be understood that each process and / or block in the flowchart and / or block diagram can be realized by computer program instructions, and the combination of processes and / or blocks in the flowchart and / or block diagram can also be realized by computer program instructions. These computer program instructions can be provided to the processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing devices to generate a machine, so that the instructions executed by the processor of the computer or other programmable data processing devices generate a device for realizing the functions specified in Figure 1 one process or multiple processes and / or blocks Figure 1 one block or multiple blocks.

[0144] These computer program instructions can also be stored in a computer-readable memory that can direct a computer or other programmable data processing device to work in a specific manner, so that the instructions stored in the computer-readable memory generate a manufactured article including an instruction device, and the instruction device realizes the functions specified in Figure 1 one process or multiple processes and / or blocks Figure 1 one block or multiple blocks.

[0145] These computer program instructions can also be loaded onto a computer or other programmable data processing device, so that a series of operation steps are executed on the computer or other programmable device to generate a computer-implemented process, and thus the instructions executed on the computer or other programmable device provide for implementing the steps in a process Figure 1 one process or multiple processes and / or blocks Figure 1 steps of the functions specified in one block or multiple blocks.

[0146] In a typical configuration, a computing device includes one or more processors (CPUs), an input / output interface, a network interface, and memory.

[0147] The memory may include non-permanent memory in the computer-readable medium, in the form of random access memory (RAM) and / or non-volatile memory, such as read-only memory (ROM) or flash RAM. The memory is an example of a computer-readable medium.

[0148] Computer-readable media includes permanent and non-permanent, removable and non-removable media and can store information by any method or technology. The information can be computer-readable instructions, data structures, program modules, or other data. Examples of computer storage media include, but are not limited to, phase change memory (PRAM), static random access memory (SRAM), dynamic random access memory (DRAM), other types of random access memory (RAM), read-only memory (ROM), electrically erasable programmable read-only memory (EEPROM), flash memory or other memory technologies, compact disc read-only memory (CD-ROM), digital versatile disc (DVD) or other optical storage, magnetic cassettes, magnetic tape magnetic disk storage or other magnetic storage devices, or any other non-transmission media that can be used to store information that can be accessed by a computing device. As defined herein, computer-readable media does not include transitory media such as modulated data signals and carrier waves.

[0149] It should also be noted that the term "comprising", "including" or any other variation thereof is intended to cover non-exclusive inclusion, so that a process, method, commodity or device comprising a series of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, commodity or device. Without further limitation, an element defined by the statement "comprising an..." does not exclude the presence of additional identical elements in the process, method, commodity or device comprising the element.

[0150] Those skilled in the art should understand that the embodiments of the present application can be provided as a method, a system, or a computer program product. Therefore, the present application can take the form of a complete hardware embodiment, a complete software embodiment, or an embodiment combining software and hardware aspects. Moreover, the present application can take the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) that contain computer-usable program code.

[0151] The above-described embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that they can still modify the technical solutions recorded in the foregoing embodiments, or perform equivalent replacements on some of the technical features; and these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention, and should all be included in the protection scope of the present invention.

Claims

1. A dose adjustment method, characterized in that, the method comprises: obtaining the plain film data of the region of interest, and obtaining the plain film information of each section of the object to be scanned based on the plain film data; determining at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determining the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals; performing scanning using the radiation dose; the determining the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals includes: determining the overall characteristic value of the plain film information of each section corresponding to each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval; determining the image parameters of each tomographic scanning interval according to the overall characteristic value of the plain film information of each section corresponding to each tomographic scanning interval; assigning a weight coefficient to the image parameters of each tomographic scanning interval; wherein, in each tomographic scanning interval, the weight coefficients of the image parameters of a preset number of toms close to the adjacent point are greater than the weight coefficients of the image parameters of other toms; analyzing the radiation dose of each tomographic scanning interval based on a preset processing rule; wherein, the radiation dose minimizes the variance of the product of the image parameters of each tomographic scanning interval and the weight coefficient of the image parameters.

2. The dose adjustment method according to claim 1, characterized in that, the plain film information includes: plain film dose and / or plain film attenuation; the obtaining the plain film information of each section of the object to be scanned based on the plain film data includes: obtaining the plain film dose of each section of the object to be scanned based on the plain film data; and / or, obtaining the plain film attenuation of each section of the object to be scanned based on the plain film data.

3. The dose adjustment method according to claim 1, characterized in that, the determining at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width includes: determining the number of scanning circles according to the ratio of the scanning direction length to the collimation width; determining at least two adjacent tomographic scanning intervals according to the number of scanning circles.

4. The dose adjustment method according to claim 1, characterized in that, the overall characteristic value includes an average value or a maximum value.

5. The dose adjustment method according to claim 1, characterized in that, the image parameters include: image noise value and / or image resolution.

6. A dose adjustment method, characterized in that, the method comprises: obtaining the plain film data of the region of interest, and obtaining the plain film information of each section of the object to be scanned based on the plain film data; determining at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determining the radiation dose of each tomographic scanning interval according to the plain film information of each section corresponding to each tomographic scanning interval and the adjacent plain film information of adjacent tomographic scanning intervals; performing scanning using the radiation dose; Determining the radiation dose for each tomographic scan interval based on the plain film information of each section corresponding to each tomographic scan interval and the adjacent plain film information of adjacent tomographic scan intervals includes: Determining the overall eigenvalue of the plain film information of each section corresponding to each tomographic scan interval based on the plain film information of each section corresponding to each tomographic scan interval; Determining the image parameters of each tomogram based on the overall eigenvalue of the plain film information of each section corresponding to each tomographic scan interval; Analyzing the radiation dose for each tomographic scan interval based on a preset processing rule; wherein, the radiation dose is such that, among any two adjacent tomographic scan intervals, the difference in image parameters between the tomogram close to the adjacent point in the first tomographic scan interval and the tomogram close to the adjacent point in the second tomographic scan interval is less than the maximum difference between the image parameters of each tomogram corresponding to the first tomographic scan interval, and less than the maximum difference between the image parameters of each tomogram corresponding to the second tomographic scan interval; and / or, the radiation dose is such that the variance of the image parameters of each tomogram in the tomographic scan interval is minimized.

7. The dose adjustment method according to claim 6, wherein, the plain film information includes: plain film dose and / or plain film attenuation; Obtaining the plain film information of each section of the object to be scanned based on the plain film data includes: Obtaining the plain film dose of each section of the object to be scanned based on the plain film data; and / or, Obtaining the plain film attenuation of each section of the object to be scanned based on the plain film data.

8. The dose adjustment method according to claim 6, wherein, Determining at least two adjacent tomographic scan intervals according to the scanning direction length and the collimation width includes: Determining the number of scanning circles according to the ratio of the scanning direction length to the collimation width; Determining at least two adjacent tomographic scan intervals according to the number of scanning circles.

9. The dose adjustment method according to claim 6, wherein, the overall eigenvalue includes an average value or a maximum value.

10. The dose adjustment method according to claim 6, wherein, the image parameters include: image noise value and / or image resolution.

11. A dose adjustment device, wherein, the device includes: A plain film information determination unit for obtaining the plain film data of the region of interest and obtaining the plain film information of each section of the object to be scanned based on the plain film data; A radiation dose determination unit for determining at least two adjacent tomographic scan intervals according to the scanning direction length and the collimation width, and determining the radiation dose for each tomographic scan interval according to the plain film information of each section corresponding to each tomographic scan interval and the adjacent plain film information of adjacent tomographic scan intervals; A scanning unit for performing scanning using the radiation dose; The radiation dose determination unit further includes: An image parameter determination module, configured to determine an overall eigenvalue of the flat film information of each cross-section corresponding to each tomographic scanning interval according to the flat film information of each cross-section corresponding to each tomographic scanning interval, and determine the image parameters of each tomographic according to the overall eigenvalue of the flat film information of each cross-section corresponding to each tomographic scanning interval; A weight coefficient determination module, configured to assign a weight coefficient to the image parameters of each tomographic; wherein, in each tomographic scanning interval, the weight coefficients of the image parameters of a preset number of toms near the adjacent point are greater than the weight coefficients of the image parameters of other toms; A radiation dose determination module, configured to analyze the radiation dose of each tomographic scanning interval based on a preset processing rule; wherein the radiation dose minimizes the variance of the product of the image parameters of each tomographic and the weight coefficient of the image parameters.

12. A dose adjustment device, characterized in that, the device includes: A flat film information determination unit, configured to obtain flat film data of an area of interest and obtain the flat film information of each cross-section of an object to be scanned based on the flat film data; A radiation dose determination unit, configured to determine at least two adjacent tomographic scanning intervals according to the scanning direction length and the collimation width, and determine the radiation dose of each tomographic scanning interval according to the flat film information of each cross-section corresponding to each tomographic scanning interval and the adjacent flat film information of adjacent tomographic scanning intervals; A scanning unit, configured to perform scanning using the radiation dose; The radiation dose determination unit further includes: An image parameter determination module, configured to determine an overall eigenvalue of the flat film information of each cross-section corresponding to each tomographic scanning interval according to the flat film information of each cross-section corresponding to each tomographic scanning interval, and determine the image parameters of each tomographic according to the overall eigenvalue of the flat film information of each cross-section corresponding to each tomographic scanning interval; A radiation dose analysis module, configured to analyze the radiation dose of each tomographic scanning interval based on a preset processing rule; wherein the radiation dose makes the difference between the image parameters of the tom near the adjacent point in the first tomographic scanning interval and the tom near the adjacent point in the second tomographic scanning interval less than the maximum difference between the image parameters of each tom corresponding to the first tomographic scanning interval and less than the maximum difference between the image parameters of each tom corresponding to the second tomographic scanning interval in any two adjacent tomographic scanning intervals; and / or, the radiation dose minimizes the variance of the image parameters of each tom in the tomographic scanning interval.

13. A computer device, including a memory, a processor, and a computer program stored in the memory and executable on the processor, characterized in that, when the processor executes the computer program, the steps of the dose adjustment method according to any one of claims 1 to 10 are implemented.

14. A computer-readable storage medium storing a computer program, characterized in that, The computer program, when instructed by a processor, implements the steps of the dose adjustment method according to any one of claims 1 to 10.

Images