A method of using a portable specimen imaging device

Abstract

The application relates to a portable specimen imaging device and a use method thereof. The device comprises a display screen, an operation table, a radiation bin, a touch operation screen arranged obliquely upward in the front of the operation table, an L-shaped support frame extended behind the touch operation screen, a display screen arranged on the support frame, a radiation bin below the touch operation screen, a ball tube and a camera installed on the top of the radiation bin, the ball tube and the camera facing a display panel at the bottom of the radiation bin, a placing disc arranged between the display panel and the ball tube and the camera, a cavity for placing a power supply and a power supply controller below the radiation bin, the power supply supplying power to the display screen, the operation table, the touch operation screen, the ball tube and the camera, wherein the end of the ball tube is provided with a high-voltage power supply, and the operation table is internally provided with a control chip. The application has the advantages of simple structure, convenient use, accurate measurement and the like.

Description

Technical Field

[0001] This invention relates to a method of using a portable specimen imaging device, belonging to the technical field of specimen imaging devices. Background Technology

[0002] Specimen imaging equipment utilizes X-ray imaging technology to allow doctors to examine the pathological condition of removed tissue in real time during surgery. It includes a high-voltage radiation source, a radiation chamber, an X-ray display panel, and a control module. During operation, medical personnel place the pathological tissue inside the radiation chamber and initiate the imaging process. Upon receiving a command, the control module activates the high-voltage radiation source. After the radiation stabilizes, it receives image data from the display panel, processes the image data in real time, and determines whether the imaging process is complete. After imaging is finished, the radiation source is turned off, an image file is generated, and the imaging results are output to the monitor. The following key technical points describe the data processing algorithms involved in the system's real-time data processing. Summary of the Invention

[0003] The technical problem to be solved by the present invention is to design a method for using a portable specimen imaging device that is simple in structure, easy to use, and accurate in measurement, in order to address the above-mentioned problems.

[0004] This invention is achieved through the following technical solution: a portable specimen imaging device, comprising a display screen, an operating table, and a radiation chamber. A touch screen is arranged diagonally upwards at the front of the operating table, and an L-shaped support frame extends from its rear. The display screen is mounted on the support frame. Below the touch screen is the radiation chamber, and an X-ray tube and a camera are installed at the top of the radiation chamber. The X-ray tube and camera face the display panel at the bottom of the radiation chamber. A storage tray is also provided between the display panel and the X-ray tube and camera. Below the radiation chamber is a chamber for housing a power supply and a power controller. The power supply provides electricity to the display screen, operating table, touch screen, X-ray tube, and camera. A high-voltage power supply is provided at the end of the X-ray tube. A control chip is installed inside the operating table.

[0005] Preferably, the chamber of the power supply contains a conventional power supply and a high-voltage power supply. The conventional power supply provides electricity to the display screen, operating table, touch screen, and camera, while the high-voltage power supply provides electricity to the X-ray tube, through which high-voltage rays are emitted. Both the conventional power supply and the high-voltage power supply are controlled by a power controller.

[0006] Preferably, the storage tray is placed in the middle of the side wall of the radiation chamber, between two protruding horizontal bars on opposite sides, with the X-ray tube and camera directly above it and the display panel directly below it.

[0007] Preferably, a movable base is provided below the chamber of the power supply and power controller. The movable base is fixed to the chamber of the power supply and power controller by positioning holes and positioning blocks provided at the four corners. The top of the movable base is provided with a placement groove for placing the chamber of the power supply and power controller, fixing the chamber of the power supply and power controller in place. Universal wheels are also provided at the four corners below the movable base.

[0008] Preferably, the control chip integrates a program control module, an output module, a receiving module, and a power control module. The program control module is connected to the operating console, the X-ray tube, and the camera. The operating console controls the X-ray tube and the camera to issue operating commands. The receiving module receives and analyzes the detected data, and the output module outputs and displays the specific analysis results. The power control module controls the power controller.

[0009] A method of using a portable specimen imaging device, the method comprising the following steps:

[0010] 1) Medical staff place pathological tissue into the radiation chamber and initiate the imaging process;

[0011] 2) Upon receiving the instruction, the control module turns on the high-voltage radiation source. After the radiation stabilizes, it receives the image data from the display panel. The control module processes the image data in real time and determines whether the imaging process has ended.

[0012] 3) After imaging is complete, turn off the radiation source, generate an image file, and output the imaging results on the monitor;

[0013] In step 2, the image data of the display tablet is received, and the control module processes the image data in real time. The control module obtains the data through noise suppression, exposure compensation, gain interpolation calculation, and defect correction.

[0014] Preferably, the noise suppression module includes the following method:

[0015] 1) Background Correction. The X-ray source is turned off, and the imaging data from the display panel is read to generate background correction data. During X-ray imaging, for each frame, the brightness value of all pixels is subtracted from the brightness value of the corresponding pixel in the background correction data, thereby obtaining imaging data with static noise eliminated.

[0016] 2) Moving average. This reduces random noise amplitude through a multi-frame image brightness averaging algorithm. Let the current image be the nth frame, the image data have undergone background correction, and the brightness value of a certain pixel in the image be λ. n The calculated brightness value is β. n The noise intensity is γ n ,but

[0017] When the noise amplitude γ of all pixels n When the result is less than 1%, the imaging process ends, the X-ray source is turned off, and the result is output.

[0018] Preferably, the exposure compensation module operates by performing a blank image before taking the picture to obtain imaging gain data under the current X-ray intensity. Let the brightness value of a pixel in the imaging data (with noise suppression already completed) be λ, and the corresponding pixel value in the gain data be α, with relative brightness... Pixel brightness in the output image The image depth is 16 bits.

[0019] Preferably, the gain interpolation calculation module is designed to address the issue that the brightness distribution of the imaging flat panel is related not only to the location of the X-ray source but also to the intensity of the X-rays. Therefore, when performing exposure compensation calculations, blank imaging of all X-ray intensities is required to obtain the corresponding gain data. To simplify the operation, the device uses interpolation calculations to reduce the amount of gain correction data. After fitting calculations with a large amount of exposure data, it was found that the imaging brightness value is proportional to the fourth power of the X-ray exposure voltage. Therefore, four correction levels (20, 38, 45, and 50) are set for the exposure voltage range of 20V to 50V. Let the exposure voltage be V, the level less than V be V0, and its gain pixel brightness be α0; let the level greater than V be V1, and its gain pixel brightness be α1. Then, the exposure gain pixel brightness...

[0020] Preferably, the defect correction module is designed for imaging flat panels that are constantly exposed to X-ray radiation. Inevitably, some pixels may become damaged and unable to respond to X-rays, failing to output correct brightness data. In the image data after background correction, the pixel brightness value at the defective pixel location is 0. The software detects pixels with a value of zero and fills the zero value with the average brightness of its neighboring pixels.

[0021] Preferably, the images captured by the camera are processed by software through stretching, cropping, and other data processing to obtain a 1:1 color image of the actual object, mirroring the X-ray image. This allows physicians to compare the X-ray images with the actual object, helping them accurately determine the location of lesions in the specimen tissue.

[0022] The present invention has the following key technical features:

[0023] 1. Noise Suppression. X-ray imaging noise includes static noise and random noise. Static noise is caused by non-uniformity of photosensitive pixels due to random factors during the manufacturing process of the imaging plate. Random noise is caused by electromagnetic fluctuations in the environment and circuitry during the imaging process. The equipment eliminates noise through the following methods:

[0024] 2. Exposure Compensation. During X-ray imaging, because the X-ray source is a point source rather than a parallel source, the brightness of the image produced by the developing plate is radially distributed, interfering with image interpretation. To solve this problem, exposure compensation is used to calculate the relative brightness as the imaging result. Before taking the film, a blank image is first performed to obtain the imaging gain data under the current X-ray intensity.

[0025] 3. Gain Interpolation Calculation. The brightness distribution of flatbed imaging is related not only to the location of the X-ray source but also to the intensity of the X-rays. Therefore, exposure compensation calculations require blank imaging of all X-ray intensities to obtain the corresponding gain data. To simplify the operation, the equipment uses interpolation calculations to reduce the amount of gain correction data.

[0026] 4. Defect Correction. The display panel operates continuously under X-ray radiation, and some pixels inevitably become damaged, failing to respond to X-rays and output correct brightness data. In the image data after background correction, the brightness value of pixels at the defective locations is 0. The software detects pixels with zero values ​​and fills the zero value with the average brightness of its neighboring pixels.

[0027] This invention has many advantages, such as simple structure, convenient use, and accurate measurement. Attached Figure Description

[0028] Figure 1 This is a front view of the present invention.

[0029] Figure 2 This is a rear view of the present invention.

[0030] Figure 3 This is a perspective view of the present invention.

[0031] Figure 4 This is a schematic diagram of the control chip in this invention. Detailed Implementation

[0032] The invention will now be described in detail with reference to the accompanying drawings: Figure 1-3As shown, a portable specimen imaging device includes a display screen 1, an operating table 2, and a radiation chamber 3. A touch screen 4 is arranged diagonally upwards at the front of the operating table 2, and an L-shaped support frame 5 extends from its rear. The display screen 1 is mounted on the support frame 5. Below the touch screen 4 is the radiation chamber 3. An X-ray tube 6 and a camera 7 are installed at the top of the radiation chamber 3, directly facing a display panel 8 at the bottom of the radiation chamber 3. A storage tray 9 is also provided between the display panel 8 and the X-ray tube 6 and camera 7. Below the radiation chamber 3 is a chamber 12 housing a power supply 10 and a power controller 11. The power supply 10 supplies power to the display screen 1, operating table 2, and radiation chamber 3. The system includes a platform 2, a touch screen 4, an X-ray tube 6, and a camera 7. The end of the X-ray tube 6 is equipped with a high-voltage power supply. The platform 2 contains a control chip 19. The chamber 12 of the power supply 10 contains both a normal power supply and a high-voltage power supply. The normal power supply powers the display screen 1, platform 2, touch screen 4, and camera 7, while the high-voltage power supply powers the X-ray tube 6, through which high-voltage rays are emitted. Both the normal power supply and the high-voltage power supply are controlled by a power controller 11. The storage tray 9 is placed in the middle of the side wall of the radiation chamber 3, between two protruding horizontal bars 13 on opposite sides. The tray faces the X-ray tube 6 and camera 7 above and the display panel 8 below.

[0033] A movable base 14 is also provided below the chamber 12 of the power supply 10 and the power controller 11. The movable base 14 is fixed to the chamber 12 of the power supply 10 and the power controller 11 by positioning holes 15 and positioning blocks 16 provided at the four corners. The top of the movable base 14 is provided with a placement groove 17 for placing the chamber 12 of the power supply 10 and the power controller 11, fixing the chamber 12 of the power supply 10 and the power controller 11 in place within the placement groove 17. Universal wheels 18 are also provided at the four corners below the movable base 14.

[0034] like Figure 4 As shown, the control chip 19 integrates a program control module 20, an output module 21, a receiving module 22, and a power control module 23. The program control module 20 is connected to the operating console 2, the X-ray tube 6, and the camera 7. The operating console 2 controls the X-ray tube 6 and the camera 7 to issue operation commands. The receiving module 22 receives and analyzes the detected data, and then outputs and displays the specific analysis results through the output module 21. The power control module 23 controls the power controller 11.

[0035] A method of using a portable specimen imaging device, the method comprising the following steps:

[0036] 1) Medical staff place pathological tissue into the radiation chamber and initiate the imaging process;

[0037] 2) Upon receiving the instruction, the control module turns on the high-voltage radiation source. After the radiation stabilizes, it receives the image data from the display panel. The control module processes the image data in real time and determines whether the imaging process has ended.

[0038] 3) After imaging is complete, turn off the radiation source, generate an image file, and output the imaging results on the monitor;

[0039] In step 2, the image data of the display tablet is received, and the control module processes the image data in real time. The control module obtains the data through noise suppression, exposure compensation, gain interpolation calculation, and defect correction.

[0040] The noise suppression module includes the following methods:

[0041] 1) Background Correction. The X-ray source is turned off, and the imaging data from the display panel is read to generate background correction data. During X-ray imaging, for each frame, the brightness value of all pixels is subtracted from the brightness value of the corresponding pixel in the background correction data, thereby obtaining imaging data with static noise eliminated.

[0042] 2) Moving average. This reduces random noise amplitude through a multi-frame image brightness averaging algorithm. Let the current image be the nth frame, the image data have undergone background correction, and the brightness value of a certain pixel in the image be λ. n The calculated brightness value is β. n The noise intensity is γ n , then β When the noise amplitude γ of all pixels n When the result is less than 1%, the imaging process ends, the X-ray source is turned off, and the result is output.

[0043] The exposure compensation module specifically operates by performing a blank imaging process before taking the film, acquiring imaging gain data under the current X-ray intensity. Let λ be the brightness value of a pixel in the imaging data (with noise suppression already completed), and α be the corresponding pixel value in the gain data, representing the relative brightness... Pixel brightness in the output image The image depth is 16 bits.

[0044] The gain interpolation calculation module works as follows: the brightness distribution of the imaging flat panel is related not only to the position of the X-ray source but also to the intensity of the X-rays. Therefore, when performing exposure compensation calculations, blank imaging is required for all X-ray intensities to obtain the corresponding gain data. To simplify the operation process, the device uses interpolation calculations to reduce the amount of gain correction data. After fitting calculations with a large amount of exposure data, it was found that the imaging brightness value is proportional to the fourth power of the X-ray exposure voltage. Therefore, four correction levels (20, 38, 45, and 50) are set for the exposure voltage range of 20V to 50V. Let the exposure voltage be V, the level less than V be V0, and its gain pixel brightness be α0; let the level greater than V be V1, and its gain pixel brightness be α1. Then the exposure gain pixel brightness...

[0045] The defect correction module is designed for imaging flat panels that are constantly exposed to X-ray radiation. Inevitably, some pixels may become damaged and unable to respond to X-rays, failing to output correct brightness data. In the image data after background correction, the brightness value of pixels at the defective locations is 0. The software detects pixels with a value of zero and fills the zero with the average brightness of its neighboring pixels.

[0046] The present invention has the following key technical features:

[0047] 1. Noise Suppression. X-ray imaging noise includes static noise and random noise. Static noise is caused by non-uniformity of photosensitive pixels due to random factors during the manufacturing process of the imaging plate. Random noise is caused by electromagnetic fluctuations in the environment and circuitry during the imaging process. The equipment eliminates noise through the following methods:

[0048] 2. Exposure Compensation. During X-ray imaging, because the X-ray source is a point source rather than a parallel source, the brightness of the image produced by the developing plate is radially distributed, interfering with image interpretation. To solve this problem, exposure compensation is used to calculate the relative brightness as the imaging result. Before taking the film, a blank image is first performed to obtain the imaging gain data under the current X-ray intensity.

[0049] 3. Gain Interpolation Calculation. The brightness distribution of flatbed imaging is related not only to the location of the X-ray source but also to the intensity of the X-rays. Therefore, exposure compensation calculations require blank imaging of all X-ray intensities to obtain the corresponding gain data. To simplify the operation, the equipment uses interpolation calculations to reduce the amount of gain correction data.

[0050] 4. Defect Correction. The display panel operates continuously under X-ray radiation, and some pixels inevitably become damaged, failing to respond to X-rays and output correct brightness data. In the image data after background correction, the brightness value of pixels at the defective locations is 0. The software detects pixels with zero values ​​and fills the zero value with the average brightness of its neighboring pixels.

[0051] The images captured by camera 7 are processed by software, including stretching and cropping, to obtain a 1:1 color image of the actual object, mirroring the X-ray image. This allows physicians to compare the X-ray images with the actual object, helping them accurately determine the location of lesions in the specimen.

[0052] The above description is only a preferred embodiment of the present invention, but the scope of protection of the present invention is not limited thereto. Any changes or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in the present invention should be included within the scope of protection of the present invention.

Claims

1. A method of using a portable specimen imaging device, the device comprising a display screen, an operating table, and a radiation chamber, characterized in that: A touch screen is positioned diagonally upwards at the front of the control panel, with an L-shaped support extending from its rear. A display screen is mounted on the support. Below the touch screen is a radiation chamber, inside which an X-ray tube and camera are mounted at the top. The X-ray tube and camera face a display panel at the bottom of the radiation chamber. A storage tray is positioned between the display panel and the X-ray tube and camera. Below the radiation chamber is a chamber housing a power supply and power controller. This power supply provides electricity to the display screen, control panel, touch screen, X-ray tube, and camera. A high-voltage power supply is located at the end of the X-ray tube. A control chip is located inside the control panel. The method of use includes the following steps: 1) Medical staff place pathological tissue into the radiation chamber and initiate the imaging process; 2) Upon receiving the instruction, the control module turns on the high-voltage radiation source. After the radiation stabilizes, it receives the image data from the display panel. The control module processes the image data in real time and determines whether the imaging process has ended. 3) After imaging is complete, turn off the radiation source, generate an image file, and output the imaging results on the monitor; In step 2, the image data of the display tablet is received, and the control module processes the image data in real time. The control module obtains the data through noise suppression, exposure compensation, gain interpolation calculation, and defect correction. At the same time, the camera above the radiation chamber of the equipment takes pictures. The gain interpolation calculation module works as follows: The brightness distribution of the imaging flat panel is related not only to the position of the X-ray source but also to the intensity of the X-rays. Therefore, when performing exposure compensation calculations, blank imaging is required for all X-ray intensities to obtain the corresponding gain data. To simplify the operation process, the device reduces the amount of gain correction data through interpolation calculations. After fitting calculations with a large amount of exposure data, it was found that the imaging brightness value is proportional to the fourth power of the X-ray exposure voltage. Therefore, for the exposure voltage range of 20V to 50V, four correction levels of 20, 38, 45, and 50 are set. Let the exposure voltage be V, the level less than V be V0, and its gain pixel brightness be α0; the level greater than V be V1, and its gain pixel brightness be α1. Then the exposure gain pixel brightness... The defect correction module is designed for display panels that are constantly exposed to X-ray radiation. Some pixels may inevitably become damaged and fail to respond to X-rays by outputting correct brightness data. In the image data after background correction, the brightness value of the pixels at the defective locations is 0. When the software detects a pixel with a value of zero, it will fill the zero value with the average brightness of its neighboring pixels.

2. The method of using the portable specimen imaging device according to claim 1, characterized in that: The noise suppression module includes the following methods: 1) Background correction: Turn off the X-ray source, read the imaging data of the imaging flat panel, and generate background correction data. When performing X-ray imaging, for each frame of the image, the brightness value of all pixels is subtracted from the brightness value of the corresponding pixel in the background correction data, thereby obtaining imaging data that eliminates static noise. 2) Moving average: This reduces the amplitude of random noise by using a multi-frame image brightness averaging algorithm. Let the current image be the nth frame. The image data has undergone background correction, and the brightness value of a certain pixel in the image is λ. n The calculated brightness value is β. n The noise intensity is γ n ,but When the noise amplitude γn of all pixels is less than 1%, the imaging process ends, the X-ray source is turned off, and the results are output.

3. The method of using the portable specimen imaging device according to claim 1, characterized in that: The exposure compensation module specifically operates by performing a blank image before taking the picture, acquiring imaging gain data under the current X-ray intensity, and assuming the brightness value of a certain pixel in the imaging data is λ, the corresponding pixel value in the gain data is α, and the relative brightness... Pixel brightness in the output image The image depth is 16 bits.

4. The method of using the portable specimen imaging device according to claim 1, characterized in that: The images captured by the camera are processed by software through stretching and cropping to obtain a 1:1 color image of the actual object, which can be compared with the X-ray image when the doctor reads the X-ray image, helping the doctor to accurately determine the location of lesions in the specimen tissue.

5. The method of using the portable specimen imaging device according to claim 1, characterized in that: The power supply chamber contains a conventional power supply and a high-voltage power supply. The conventional power supply provides electricity to the display screen, operating table, touch screen, and camera, while the high-voltage power supply provides electricity to the X-ray tube, through which high-voltage rays are emitted. Both the conventional power supply and the high-voltage power supply are controlled by a power controller.

6. The method of using the portable specimen imaging device according to claim 1, characterized in that: The storage tray is placed in the middle of the side wall of the radiation chamber, between two protruding horizontal bars on opposite sides, with the X-ray tube and camera directly above it and the display panel directly below it.

7. The method of using the portable specimen imaging device according to claim 1, characterized in that: A movable base is provided below the chamber of the power supply and power controller. The movable base is fixed to the chamber of the power supply and power controller by positioning holes and positioning blocks at the four corners. The top of the movable base is provided with a placement groove for placing the chamber of the power supply and power controller, fixing the chamber of the power supply and power controller in place. Universal wheels are also provided at the four corners below the movable base.

8. The method of using the portable specimen imaging device according to claim 1, characterized in that: The control chip integrates a program control module, an output module, a receiving module, and a power control module. The program control module is connected to the operating console, the X-ray tube, and the camera. It sends operation commands to the X-ray tube and the camera through the operating console. The receiving module receives and analyzes the detected data, and then outputs and displays the specific analysis results through the output module. The power control module controls the power controller.

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