CN105310712A - Method and system for measuring tumor standard uptake value with single photon imaging in nuclear medicine - Google Patents

Abstract

The invention relates to a method and a system for measuring a tumor standard uptake value by a nuclear medicine single photon image, which utilizes Single Photon Emission Computed Tomography (SPECT) or single photon emission computed tomography/computed tomography (SPECT/CT) to measure the tumor standard uptake value by the image, and the method comprises the following steps: the invention solves the problems of physical interference and patient movement in dynamic single photon emission computed tomography, and has the quantification capability of tumor standard uptake value of the patient.

Description

Method and system for measuring tumor standard uptake value with single photon imaging in nuclear medicine

technical field

The present invention relates to an image measurement method and system design, in particular to a method and system for nuclear medicine single-photon image measurement of tumor standard uptake values.

Background technique

At present, in clinical practice, in order to measure the standardized uptake value (SUV) of tumors for drugs, it is first necessary to establish the ) obtained images with the same attributes. However, although PET or PET/CT can accurately measure the standard uptake value of tumors, they cannot be widely used in hospitals at all levels due to problems such as the popularity of contrast drugs and the high burden of examination funds.

Compared with PET and PET/CT, the imaging modes of SPECT and SPECT/CT have the advantages of economical parity, and can be widely used in hospitals at all levels. However, traditional SPECT and SPECT/CT angiography have problems such as physical interference and low spatial resolution. , diagnosis often encounters image artifacts and insufficient accuracy, and cannot be used to quantify tumor standard uptake values, thus limiting SPECT and SPECT/CT as an economical clinical tool for diagnosing tumor diseases . In view of the above, there is a real need for an economical quantitative imaging system for the quantification of tumor standard uptake values.

Contents of the invention

Therefore, the object of the present invention is to provide a method and system for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine, so as to improve the problems of the prior art and achieve economical and accurate measurement.

The technical means adopted by the present invention to solve the problems of the prior art is a method for measuring the standard uptake value of tumors by single-photon imaging in nuclear medicine, using single-photon emission computed tomography or single-photon emission computed tomography/computed tomography Carrying out image measurement of tumor standard uptake value, the method includes: a photographing step, by single-photon emission computed tomography or single-photon emission computed tomography/computed tomography to take an image of a patient; a scatter correction step, by obtaining an image from a correcting the scatter component of the image by subtracting the scatter component from the raw projection of the photopeak energy window; an attenuation correction step calculating the attenuation number per radiographic pixel of the scatter-corrected image by converting the computed tomography image and the radionuclide image ; an image resolution restoration step, by establishing a point spread function matrix from a point source movement measurement and then iteratively integrating and reconstructing the point spread function matrix to restore the resolution; a noise removal step, passing the reconstructed image through an analysis noise The filter and a Poisson simulator are iteratively integrated and reconstructed to remove the noise in the image; and an uptake value calculation step is to calculate an ROI of the noise-removed image according to a density image-ray relationship The corresponding isotope concentration, and according to the patient's weight and the dose of the isotope applied to the patient, the patient's tumor standard uptake value is calculated.

In an embodiment of the present invention, in the scatter correction step, the isotope attenuation of the image is further corrected according to the rotation time of a radiation probe and the half-life of the isotope.

In an embodiment of the invention, in the attenuation correction step, an attenuation matrix is created by calculating attenuation numbers for each radiographic pixel of the image using attenuation numbers from computed tomography or radionuclide penetration images, and in The attenuation matrix is integrated in an iterative reconstruction to correct for attenuation.

In an embodiment of the present invention, in the image resolution restoration step, the characteristics of a collimator are measured by establishing a depth-dependent PSF matrix.

In one embodiment of the present invention, it further includes a patient motion correction step, including correcting intra-scan patient motion (Intra-scan patient motion) and correcting inter-scan patient motion (Inter-scan patient motion), wherein correcting scan patient motion Involves measuring the displacement of patient movement in iterative projections against the angle of the radiation probe, correcting for patient movement between scans involves manually realigning computed tomography and radionuclide images.

In an embodiment of the present invention, in the step of calculating the uptake value, the tumor standard uptake value is further normalized according to the patient's whole body mass, body fat percentage, and/or whole body surface area.

In one embodiment of the present invention, in the uptake value calculation step, the concentration image ray relationship is based on the concentration of the isotope injected into a phantom, the image of the phantom taken by single photon emission computed tomography, and the isotope injected The radiation intensity of the prosthesis was calculated.

In an embodiment of the present invention, in the step of calculating the uptake value, the prosthesis is a symmetrical prosthesis.

Another technical means adopted by the present invention to solve the problems of the prior art is a system for measuring the standard uptake value of tumors using single-photon emission computed tomography or single-photon emission computed tomography/computer tomography nuclear medicine single-photon images , comprising a single photon emission computed tomography/computed tomography device, a computer, and a program product. The single photon emission computed tomography/computed tomography device is used for taking a single photon emission computed tomography or single photon emission computed tomography/computed tomography image. The computer has a processing unit. The program product includes a computer-readable program code loaded by a processing unit of a computer to perform the following steps: receiving a single photon emission computed tomography or single photon emission computed tomography/computed tomography image; correcting the scattering of the image; correcting the image attenuation; restore the spatial resolution of the image; remove the image noise of the image; and calculate a tumor standard uptake value corresponding to the image.

Through the technical means adopted in the present invention, by solving the problems of physical interference and low spatial resolution of SPECT and SPECT/CT, avoiding image artifacts and misjudgment problems caused by low accuracy in the diagnosis of tumor diseases, and As an economical clinical tool to quantify the standard uptake value of tumors, it achieves the effect of economical and accurate measurement.

Description of drawings

The specific embodiments adopted by the present invention will be further described through the following embodiments and attached drawings.

FIG. 1 is a flow chart showing a method for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine according to an embodiment of the present invention.

FIG. 2 is an equipment diagram showing a system for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine according to an embodiment of the present invention.

FIG. 3 is a block diagram showing a system for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine according to an embodiment of the present invention.

FIG. 4A is a schematic diagram showing a system for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine according to an embodiment of the present invention, taking images of patients from the right front oblique to the left rear oblique.

4B is a schematic diagram showing a system for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine according to an embodiment of the present invention, taking images of patients from front to back.

4C is a schematic diagram showing a system for measuring standard uptake values of tumors with single-photon imaging in nuclear medicine according to an embodiment of the present invention, taking images of patients from the left front oblique to the right rear oblique.

FIG. 4D is a schematic diagram showing a system for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine according to an embodiment of the present invention, taking images of patients from the rear to the front.

FIG. 5A is a flowchart showing steps of patient motion correction according to an embodiment of the present invention.

FIG. 5B is a schematic diagram showing a patient image before resolution restoration according to an embodiment of the present invention.

FIG. 5C is a schematic diagram showing a patient image after resolution restoration according to an embodiment of the present invention.

6A to 6C are schematic diagrams showing patient images before SPECT and CT alignment according to the present invention.

7A to 7C are schematic diagrams showing the alignment of SPECT and CT images of patients according to the present invention.

FIG. 8 is a schematic diagram showing an attenuation matrix of a patient image according to an embodiment of the present invention.

FIG. 9A is a schematic diagram showing a patient image without correction according to an embodiment of the present invention.

9B to 9F are schematic diagrams showing various corrections of patient images according to an embodiment of the present invention.

10A to 10C are schematic diagrams showing CT, SPECT, and SPECT/CT images of patients before tumor treatment according to the present invention.

11A to 11C are schematic diagrams showing CT, SPECT, and SPECT/CT images of patients after tumor treatment according to the present invention.

in:

100 nuclear medicine single-photon imaging system for measuring tumor standard uptake values

1 Single Photon Emission Computed Tomography/Computed Tomography Equipment

10 radiation probes

12 radiation probes

14 Computed tomography cameras

16 imaging table

18 racks

2 computers

3 program products

30 computing modules

31 image receiving module

32 scatter correction modules

33 attenuation correction module

34 resolution recovery module

35 noise removal modules

36 Patient Movement Correction Modules

a, b, c, d, e, f, g reference points

M1 decay matrix

P1 processing unit

Patient U

detailed description

The present invention provides a quantitative single-photon emission computed tomography (SPECT) reconstruction system, which quantifies tumor standard uptake values by means of SPECT or single-photon emission computed tomography/computed tomography (SPECT/CT) dynamic imaging. Please refer to FIG. 2 and FIG. 3 . According to an embodiment of the present invention, a system 100 for measuring standard uptake values of tumors by single-photon imaging in nuclear medicine uses single-photon emission computed tomography or single-photon emission computed tomography/computed tomography. The photographed image is used to measure the standard uptake value of the tumor. The system 100 includes a single photon emission computed tomography/computed tomography device 1, a computer 2, and a program product 3 (loaded on the computer 2).

The program product 3 may include computer-readable program codes loaded by the computer 2 to execute some processing steps. The computer 2 may include, but is not limited to, any type of computer, including desktop computers, notebook computers, and smart devices, such as tablet computers and smart phones. The program product 2 may comprise software, which may be loaded on or accessed by the computer 2 . The loaded software may include a program loaded on the hard disk of the computer 2, or an application program of the smart device. In some embodiments, the software can be accessed through computer 2 using a web browser. The computer 2 can use the Internet, external network, internal network, host server (hostserver), and network cloud (internetcloud) to access the software. The invention can be converted into computer software for medical imaging in a medical environment, so as to conduct SPECT or SPECT/CT research on patients.

The single photon emission computed tomography/computed tomography apparatus 1 is used for taking a single photon emission computed tomography or single photon emission computed tomography/computed tomography image for an exemplary patient U (cooperating with FIGS. 4A-4B ). In order to take the image, the exemplary patient U may be placed on an imaging table 16 of the single photon emission computed tomography/computed tomography apparatus 1 . The single-photon emission computed tomography/computed tomography system 1 can have a radiation probe 10 , 12 . A computed tomography camera 14 may be placed within the gantry 18 . Rack 18 may include a cylindrical scanner assembly to capture the image.

The computer 2 has a processing unit P1. The program product 3 includes a computer-readable program code loaded by the processing unit P1 of the computer 2 to perform the following steps: receiving single photon emission computed tomography or single photon emission computed tomography/computed tomography images; correcting the scattering of the images ; correcting the attenuation of the image; restoring the spatial resolution of the image; removing the image noise of the image; and calculating a tumor standard uptake value corresponding to the image. As shown in Figure 3, in this embodiment, the program product 3 may include an image receiving module 31, a scatter correction module 32, an attenuation correction module 33, a resolution restoration module 34, a noise removal module 35, a patient The movement correction module 36 and a calculation module 30 respectively execute the above steps in sequence.

Please refer to FIG. 1 , the method for measuring the standard uptake value of a tumor by nuclear medicine single-photon imaging according to an embodiment of the present invention is to use single-photon emission computed tomography or single-photon emission computed tomography/computed tomography Carrying out imaging measurement of tumor standard uptake value, the method for measuring tumor standard uptake value by single-photon imaging in nuclear medicine includes a photography step (step S1), a scattering correction step (step S2), an attenuation correction step (step S3), an image resolution step A rate restoration step (step S4), a noise removal step (step S5), and an uptake value calculation step (step S6). In conjunction with the system 100 for measuring standard uptake values of tumors by nuclear medicine single-photon imaging shown in FIG.

Firstly, in the imaging step (step S1 ), an image of the patient U is captured by single-photon emission computed tomography or single-photon emission computed tomography/computed tomography. The image capture is a form of image data obtained by the radiation probes 10 and 12 going around the patient U after the isotope injection by 180 degrees or 360 degrees. In each round of rotation, the image data is represented by two indexes of dynamic frame (frame) and angle. The isotope can be drugs such as 鎝-99m, iodine-131, iodine-123, gallium-67, fluorine-18, but not limited thereto. As shown in Figures 4A to 4D, the radiation probes 10 and 12 can be moved from a right front oblique to left front and rear (Figure 4A), front to rear (Figure 4B), left front oblique and right rear oblique (Figure 4C), rear The patient U is imaged in a rotational direction to the front (FIG. 4D), or in a direction opposite to the rotational direction. The present invention may include capturing and receiving image data in a standard digital imaging and communications in medicine (DICOM) format or in a machine-specific format for subsequent image processing. The images may be images taken from SPECT or SPECT/CT, and CT images in DICOM format from SPECT/CT or CT, or data from radionuclide images in machine specific format or DICOM format from SPECT.

Then, in the scatter correction step (step S2 ), the scatter component of the image is corrected by subtracting the scatter component from the original projection obtained from an optical peak energy window (step S21 ). The scatter correction can be calculated by rescaling counts from raw projections from, for example, Compton scatter windows, and subtracting the scatter component from raw projections from a photopeak window (measurement projections) . Besides, in a preferred embodiment, in the scatter correction step (step S2), the isotope attenuation of the image is corrected according to the rotation time of the radiation probes 10, 12 and the half-life of the isotope (step S22). In some embodiments, isotopic decay correction may be performed on the imagery. Isotopic decay correction of raw projections for SPECT can be performed by rescaling the counts in the raw projections corresponding to the frame and angle in the SPECT acquisition. As the SPECT gantry 18 surrounds the patient U, the readjustment factor can be calculated by an exponential decay model with a time factor defined for the angle and frame at the corresponding point in time.

Thereafter, the attenuation correction step (step S3 ) calculates the attenuation number of each radiographic image pixel of the scatter-corrected (step S2 ) image by converting the computed tomography image and the radionuclide image. Specifically, in this embodiment, an attenuation matrix M1 is created by calculating the attenuation number of each radiographic pixel of the image using the attenuation number obtained from computed tomography or radionuclide penetration images, and in an iterative reconstruction Integrate the attenuation matrix M1 to correct for attenuation. Attenuation can be corrected by using attenuation coefficients from computed tomography or radionuclide penetration images at 140 kiloelectron volts (keV) or specific energies corresponding to other SPECT isotopes. Computed tomography or radionuclide penetration images can be converted into an attenuation matrix M1 that records the values corresponding to each pixel in an image labeled with five labels (x, y, z, angle, frame) The magnitude of photon attenuation. Image alignment between SPECT/CT and CT was performed before attenuation correction to improve the accuracy of attenuation correction. After image alignment between SPECT/CT and CT (Fig. 6A to 6B) have correct image location data.

Then, the image resolution restoration step (step S4 ) restores the resolution of the image by establishing a point spread function matrix from a point source movement measurement and iteratively integrating and reconstructing the point spread function matrix (point spread function, PSF). Specifically, in this embodiment, the resolution of the image is restored by establishing a point spread function matrix from a point source movement measurement and iteratively integrating and reconstructing the point spread function matrix. In this way, the characteristics of a collimator (not shown in the figure) of the single photon emission computed tomography/computed tomography apparatus 1 can be further measured by establishing a depth-dependent point spread function matrix. A set of PSFs can be measured for a SPECT scanner type with a particular type of collimator. The PSF can be modeled by analytical functions such that for each image pixel with a known distance to the collimator surface (labeled by six labels (x, y, z, distance, angle, frame)) Generate a complete set of PSFs. The PSF can then be applied to the radiographic image prior to the front projection step in iterative reconstruction. Besides, the aforementioned attenuation matrix M1 can also be applied to the radiological images before the front projection step in the iterative reconstruction.

In order to avoid the interference of the patient U movement, preferably, a patient movement correction step (step S15) is further included, including correcting the patient U movement (Intra-scanpatientmotion) in the scan and correcting the patient U movement (Inter-scanpatientmotion) between scans. ), which is implemented by a patient movement correction module 36, as shown in FIG. 5A , where correcting the patient U movement in the scan includes measuring the displacement of the patient U movement in an iterative projection manner for the angles of the radiation probes 10 and 12 , correcting for patient U movement between scans involves manually realigning the computed tomography and radionuclide images. Among them, the patient U movement (Intra-scanpatientmotion) in the correction scan must be performed before the scatter correction step (step S2), and the patient U movement between correction scans (Inter-scanpatientmotion) only needs to be performed in the attenuation correction step (step S3) Execute before.

Intra-scan patient motion is a type of patient motion that occurs during a dynamic SPECT scan, and the movement of the patient U in the scan may cause artifacts. The movement of the patient U in the scan in the measured projections of each dynamic frame is evaluated individually for correction. In some embodiments, this correction may be performed by iteratively displacing the measured projections for angle and frame. The vertical and horizontal displacements for angle and frame can be defined by comparing the measured projections with the front projection projections by maximizing the individual cross-correlations between both vertical and horizontal directions. The same process can be performed iteratively for multiple angles and frames until each projection reaches a stable maximum cross-correlation.

Inter-scan patient motion is a type of patient motion caused between dynamic SPECT scans and CT or radionuclide penetration scans. Patient motion between scans can cause attenuation correction artifacts. film. Patient motion between scans between SPECT and CT, or between SPECT and through-images, can be individually corrected by manually realigning the x, y, z directions and σ, δ, θ angles. After the alignment of the SPECT/CT and CT images ( FIGS. 7A to 7B ) has correct image position data compared to before the alignment of the SPECT/CT and CT images ( FIGS. 6A to 6B ).

After the image resolution restoration step (step S4), the image resolutions of the reference points a, b, c, d, e, f, and g in Fig. 4A to Fig. 4B are compared with those before restoration (Fig. 5C) (FIG. 5B) There was a clear improvement.

Subsequently, the noise removal step (step S5 ) is to iteratively integrate and reconstruct the image reconstructed (step S4 ) through an analysis noise filter and a Poisson simulator to remove noise in the image. Image noise can be removed by applying a controllable analysis filter to the front-projected projection data, resulting in an averaged noise distribution of the measured projection data that is also Filtering can be done during the step of comparing the two data sets in the iterative reconstruction by means of an equivalent analytical filter. As an alternative embodiment, the noise in the projections of the front projection can be simulated by a stochastic process of Poisson distribution to generate an averaged noise of the measured projection data during the iterative reconstruction step comparing the two data sets distributed.

Finally, the uptake value calculation step (step S6) is to calculate the isotope concentration corresponding to a region of interest in the image after noise removal (step S5) according to the ray relationship of a concentration image, and calculate the isotope concentration corresponding to a region of interest of the image after denoising (step S5), and according to the weight of the patient U and the The dose of the isotope of U is used to calculate the standard uptake value of the patient U's tumor. Among them, in order to correct the radioactive penetration of the human body, in this embodiment, the concentration image ray relationship is based on the concentration of the isotope injected into a prosthesis, the image of the prosthesis taken by single photon emission computed tomography, and the injected The radiation intensity of the prosthesis with isotope is calculated. For the convenience of measurement, preferably, the prosthesis is a symmetrical prosthesis. However, due to biological specificity, in this embodiment, the tumor standard uptake value is normalized according to the patient U's body mass, body fat percentage, and body surface area. In still other embodiments, the tumor standard uptake value can also be normalized only according to one or both of the patient U's whole body mass, body fat percentage, and whole body surface area. Of course, the present invention is not limited thereto, and the tumor standard uptake value can also be normalized according to other physiological parameters of the patient U, for example, the tumor standard uptake value of the bone tumor can be normalized by using the osteoporosis degree of the patient U.

Figures 9A to 9F show, respectively, an uncorrected image (Figure 9A), a noise-removed image (Figure 9B), a noise-removed, patient-motion-corrected image (Figure 9C), a noise-removed, patient-motion image of patient U, respectively. Corrected, attenuation-corrected image (Fig. 9D), noise-removed, patient-motion-corrected, attenuation-corrected, scatter-corrected image (Fig. 9E), noise-removed, patient-motion-corrected, attenuation-corrected, scatter-corrected, image-reconstructed image ( Figure 9F). From the comparison of Figures 9A to 9F, the tumor location and image radiation intensity can be clearly observed and defined.

10A to 10C are schematic diagrams showing CT, SPECT, and SPECT/CT images of patients before tumor treatment according to the present invention. 11A to 11C are schematic diagrams showing CT, SPECT, and SPECT/CT images of patients after tumor treatment according to the present invention. It can be proved that compared with the prior art, the difference of the tumor before and after treatment can be more clearly observed by the naked eye through the technical means of the present invention.

The computer-based data processing system and method described above are for illustrative purposes only, and can be implemented in the form of any computer system, programming, or processing environment, or a computer program alone or in combination with hardware. The present invention can also be implemented as software stored on a computer readable medium and executed as a computer program for a general purpose or special purpose computer. For the sake of brevity, this article only describes the aspects of these systems closely related to the present invention, and details of products well known in the art are omitted. For the same reason, the computer hardware will not be further described in detail. Therefore, it should be understood that the present invention is not limited to any particular computer language, program, or computer. It is further contemplated that the present invention may operate on a stand-alone computer system, or on a computer server system that can be accessed by multiple client computer systems interconnected by an internal network, or on a Accessed by clients over the Internet. Furthermore, the many embodiments of the present invention are applicable in a wide range of industries. The present invention discloses a system, a method implemented by the system, and software stored on a computer-readable medium and used as a computer program to execute the method on a general-purpose or special-purpose computer, all within the scope of the present invention. Furthermore, the present invention discloses a method and a device system configured to implement the method, and they are all included in the scope of the present invention.

The above narration is only a description of the preferred embodiment of the present invention, and those who are proficient in this art can make other various improvements according to the above description, but these changes still belong to the spirit of the present invention and the defined patent scope middle.

Claims (9)

1. the method for a core doctor single photon radiographic measurement tumor standard uptake value, the party's genealogy of law utilizes Single Photon Emission computer tomography or utilizes Single Photon Emission computer tomography/computer tomography to carry out radiographic measurement tumor standard uptake value, and the method comprises:

One photography step, by Single Photon Emission computer tomography or Single Photon Emission computer tomography/computer tomography to take an image of a patient;

One scatter correction step, deducts scattering component by the original projection deriving from a photopeak energy window and corrects the scattering component of this image;

One correction for attenuation step, calculates the attenuation quotient of each irradiation image pixel of this image through scatter correction by coordinate conversion computer tomography image and lschemic cardiomyopathy;

One image resolution recovering step, by setting up a point spread function matrix from a point source traverse measurement and this point spread function matrix number being given iteration integration reconstruction and again recover resolution;

One noise remove step, analyzes noise filter by the image through image reconstruction via one and fore-telling Herba Orostachyos (Poisson) emulator gives iteration integration reconstruction, to remove the noise in this image; And

One uptake values calculation procedure, according to a concentration image rays relation, calculate this isotopes concentration corresponding to a region of interest through removing the image of noise, and according to the body weight of this patient and the isotopic dosage putting on this patient, calculate the tumor standard uptake value of this patient.

2. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 1, is characterized in that, in this scatter correction step, more decay according to the rotation time of a lonizing radiation probe and the isotope of this isotopic this image of half-life compensation.

3. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 1, it is characterized in that, in this correction for attenuation step, system uses and derives from the attenuation quotient that computer tomography or radionuclide penetrate image and calculate the attenuation quotient of each irradiation image pixel of this image and create a damping matrix, and in an iterative approximation, integrates this damping matrix with correcting attenuation.

4. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 1, is characterized in that, in this image resolution recovering step, is that this point spread function matrix number by setting up depth dependence is to measure the characteristic of a collimator.

5. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 1, it is characterized in that, more comprise patient's shift calibrating step, the patient that the system patient comprised in correct scan moves between (Intra-scanpatientmotion) and correct scan moves (Inter-scanpatientmotion), patient wherein in this correct scan moves the angle comprising and pop one's head in for lonizing radiation measures this patient's movement displacement in iterative projection mode, patient between this correct scan moves to comprise and manually again aims at this computer tomography image and this lschemic cardiomyopathy.

6. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 1, it is characterized in that, in this uptake values calculation procedure, more this tumor standard uptake value of normalization according to the whole body quality of this patient, body fat rate and/or total body surface area.

7. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 1, it is characterized in that, in this uptake values calculation procedure, this concentration image rays relation according to flow into a prosthese this isotopic concentration, calculated by the image of this prosthese captured by this Single Photon Emission computer tomography and the intensity of radiation that is injected with this this prosthese isotopic and obtain.

8. the method for core doctor single photon radiographic measurement tumor standard uptake value as claimed in claim 7, it is characterized in that, in this uptake values calculation procedure, wherein this prosthese is a symmetry prosthese.

9. utilize a system for the core doctor single photon radiographic measurement tumor standard uptake value of Single Photon Emission computer tomography or Single Photon Emission computer tomography/computer tomography, comprise:

One Single Photon Emission computer tomography/computed tomography apparatus, for taking the image of a Single Photon Emission computer tomography or Single Photon Emission computer tomography/computer tomography;

One computer, has a processing unit; And

One program product, comprises a computer readable program code, and the processing unit via this computer loads and performs the following step:

Receive the image of this Single Photon Emission computer tomography or this Single Photon Emission computer tomography/computer tomography;

Correct the movement of a patient;

Correct the scattering of this image;

Correct the decay of this image;

Recover the spatial resolution of this image;

Remove the image noise of this image; And

Calculate the tumor standard uptake value corresponding to this image.