WO2005000122A1 - Dispositif de tomodensitometrie a rayons x - Google Patents

Dispositif de tomodensitometrie a rayons x Download PDF

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Publication number
WO2005000122A1
WO2005000122A1 PCT/JP2004/008900 JP2004008900W WO2005000122A1 WO 2005000122 A1 WO2005000122 A1 WO 2005000122A1 JP 2004008900 W JP2004008900 W JP 2004008900W WO 2005000122 A1 WO2005000122 A1 WO 2005000122A1
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WO
WIPO (PCT)
Prior art keywords
ray
reliability
specific phase
subject
tomographic image
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PCT/JP2004/008900
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English (en)
Japanese (ja)
Inventor
Hiroto Kokubun
Osamu Miyazaki
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Hitachi Medical Corporation
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Publication date
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Publication of WO2005000122A1 publication Critical patent/WO2005000122A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]

Definitions

  • the present invention relates to an X-ray CT apparatus suitable for imaging a target part that moves periodically in a predetermined phase.
  • An X-ray CT apparatus transmits an X-ray from an X-ray source toward a subject while rotating an X-ray source and an X-ray detector, which are arranged to face each other around the subject in a circumferential direction.
  • An X-ray detector that emits radiation and has a plurality of detection elements arranged in an arc shape facing the X-ray source detects an attenuated X-ray dose that has passed through the subject, and an image based on the detected attenuation data.
  • Patent Document 1 JP-A-2002-330961
  • FIGS. Figure 8 shows an example of correctly creating a tomographic image at a heartbeat phase of 70% during a heartbeat cycle. Time is plotted on the horizontal axis, and ECG information and projection data collected during imaging are shown side by side. The projection data extraction range is determined based on the R-wave position, and the projection data necessary for image reconstruction is extracted. By performing an image reconstruction operation on the extracted projection data, a tomographic image at a heartbeat phase of 70% can be created.
  • Figure 9 shows a comparison between the case where the ECG information is normal and the case where an abnormality has occurred.
  • the noises 61 and 62 may be erroneously recognized as R waves.
  • the signal strength of the R wave 53 is weak as shown in FIG. 9C
  • the signal may not be recognized as the R wave.
  • non-R-waves 61 and 62 may be detected as R-waves, or detection of R-waves 53 may be missed.
  • it becomes impossible to accurately extract projection data of the heartbeat phase and as a result, it becomes impossible to obtain an appropriate tomographic image.
  • the projection data used to create the tomographic image includes projection data corresponding to a phase different from the target phase.
  • the operator himself looks at the tomographic image and judges the appearance of the image.
  • the operator directly looks at the electrocardiographic information so as to avoid erroneous recognition of noise, a weak R wave, or the like when grasping the electrocardiographic information, and judges that the electrocardiographic information is noise and not an R wave. It takes time.
  • judgment requires visual observation by the operator, and is burdensome for the operator, and it is difficult to reduce oversight of noise and weak R waves.
  • an object of the present invention is to provide an X-ray CT apparatus capable of displaying the reliability of a tomographic image at a target heartbeat phase. Disclosure of the invention
  • an X-ray source that emits X-rays and is arranged to face each other with a subject interposed therebetween, and attenuated through the subject.
  • An X-ray detector for detecting an X-ray dose, means for sequentially rotating and moving the irradiation and detection directions of the X-ray source and the X-ray detector substantially on the circumference of the subject, and the inside of the subject.
  • a periodic motion measuring means for measuring a periodic motion of a part which performs a periodic motion, and a means for storing the measurement time of the periodic motion, the detection time of the X-ray dose, and the detection data of the X-ray dose in association with each other.
  • FIG. 1 is a block diagram showing an overall configuration of an X-ray CT apparatus according to the present invention.
  • FIG. 2 is a flowchart showing a procedure from completion of measurement to display of an image.
  • FIG. 3 is a diagram showing a dropout in an R-wave position.
  • FIG. 4 is an example of a list of each tomographic image displayed on the display device.
  • FIG. 5 is an example of a tomographic image display screen displayed on the display device.
  • FIG. 6 is a flowchart showing a procedure for increasing the reliability of a tomographic image while re-specifying an R-wave position specifying parameter.
  • FIG. 7 is a diagram showing re-specification of an R-wave position.
  • FIG. 8 is a view showing a method of extracting projection data using electrocardiographic information.
  • FIG. 9 is a diagram showing an abnormal example of electrocardiographic information.
  • FIG. 1A is a block diagram showing the overall configuration of an X-ray CT apparatus according to one embodiment of the present invention.
  • the X-ray CT device creates a scanner gantry unit 2 that irradiates and detects X-rays, and creates projection data to be used for reconstruction calculation from the measurement data detected by the scanner gantry unit 2 and converts the projection data into a CT image signal.
  • An image processing device 7 for processing and a display device 5 for outputting a CT image are provided.
  • the scanner gantry unit 2 includes a rotating disk 8 driven by a rotation driving device 10 controlled by a measurement control device 11, an X-ray tube 1 mounted on the rotating disk 8, and an X-ray tube 1 attached to the rotating disk 8.
  • the X-ray intensity generated from the X-ray tube 1 is controlled by a measurement control device 11, which is controlled by a computer 12 having an input device 13.
  • the image processing device 7 is connected to the electrocardiograph 6 for acquiring an electrocardiographic waveform of the subject, and further connected to a storage medium 14 for storing the processing results of the image processing device 7.
  • the image processing device 7 is configured to have various functions.
  • the R-wave position specifying means 7a which specifies the R-wave position (unit: time) using the R-wave position specifying parameter, from the electrocardiographic information collected at the same time as the imaging, is obtained by the R-wave position specifying means 7a
  • Projection data extraction means 7b for extracting projection data necessary for image reconstruction at a desired heartbeat phase and slice position based on the R-wave position obtained, and image reconstruction from the projection data extracted by the projection data extraction means 7b.
  • Image reconstruction means 7c for creating a tomographic image according to the configuration
  • reliability calculating means 7d for calculating the reliability of the tomographic image created by the tomographic image creating means 7c, a plurality of tomographic images and names of the tomographic images
  • a reliability group selection means 7e for selecting a combination of a number and a reliability into a plurality of groups using the reliability as a reference value, and a parameter for updating the R-wave position identification parameter for better R-wave position identification.
  • the X-rays are set by the collimator 9.
  • the irradiated X-ray irradiation field is detected by the X-ray detector 4.
  • X-rays are measured using the X-ray detector 4 while changing the direction in which the subject is irradiated with X-rays.
  • the measurement data thus detected is once transferred to the storage medium 14 and stored.
  • electrocardiographic information of the subject is also measured by the electrocardiograph 6, and is once transferred to the storage medium 14 and stored.
  • step 1 the electrocardiographic information obtained simultaneously with the X-ray measurement is read into the image processing device 7.
  • step 2 the input device 13 inputs, for example, an initial value of a threshold value of the wave height as the R wave position specifying parameter.
  • step 3 the R-wave position specifying means 7a specifies the position (time) of the R-wave of the electrocardiographic information using the R-wave position specifying parameter input in step 2.
  • step 4 parameters required for image creation are input from the input device 13.
  • the heartbeat phase is, for example, 70% of the R-wave interval
  • the slice position is, for example, the center of the heart.
  • step 5 the projection data forming means 7b uses the position of the R wave specified in step 3 and the parameters necessary for image re-creation input in step 4 to obtain an image from the X-ray measurement data.
  • the projection data necessary for image reconstruction of the target heartbeat phase and slice position is formed.
  • step 6 the image reconstruction means 7c performs an image reconstruction operation at a desired heartbeat phase and a desired slice position based on the projection data formed in step 5. Further, the tomographic image obtained as a result is stored in the storage medium 14. At the same time, the image name of each tomographic image is also stored in the storage medium 14.
  • the reliability calculating means 7d calculates the reliability of the tomographic image obtained in step 6.
  • the reliability is determined, for example, by calculating the difference between the average heart cycle Re of the subject measured before imaging and the R-wave cycle Ra at the time of measurement of each tomographic image (the ratio is different).
  • the R-wave period Ra is the R-wave interval substantially at the center on the time axis of the data for reconstruction. For example, as shown in Fig. 3, if the R-wave period Ra at the time of measurement of each tomographic image is significantly different from the average heartbeat period Re of the subject, it is not possible to identify a certain R-wave.
  • the noise is erroneously determined to be an R-wave, a tomographic image of a desired heartbeat phase is obtained, and the possibility is high.
  • the reliability is low. Specifically, the reliability is calculated using a calculation formula such as Equation (1) so that the higher the reliability, the higher the numerical value.
  • the value is 100 when the reliability is the highest (when Ra and Re are equal).
  • the reliability group selection means 7e classifies the tomographic images based on the reliability obtained in step 7. For example, A rank, B rank, and C rank are ranked in descending order of reliability. Which rank is assigned to which range of reliability may be arbitrarily determined.
  • step 9 a list of each tomographic image is displayed on the display device 5 as a list.
  • Figure 4 shows an example.
  • FIG. 4 shows, from left to right, image number No, image name name, shooting position, heartbeat phase, reliability, reliability group, group icon, and the like.
  • the tomographic image numbers are shown in order from the top.
  • the group icons and the darkness of the black in each column are displayed as ancillary information so that the operator can easily understand the reliability grouping.
  • the density of the ink the color or the density may be applied.
  • step 10 the operator can select a desired tomographic image with a cursor and click on the series of tomographic images of FIG. 4 displayed as a list in step 9, thereby displaying the tomographic image on the display device 5. it can.
  • the above series of operations is performed by the computer 12.
  • FIG. 5 shows No. 2 of FIG. 4 as an example.
  • Fig. 5 it is attached to the X-ray CT image 71 displayed in the center, the reliability is placed at the position 72, the reliability group is placed at the position 73, the group icon is placed at the position 74, and recalculation is performed if necessary.
  • the execute button 75 can also be displayed.
  • the R-wave position identification parameter is updated by the parameter updating means 7f, thereby increasing the reliability. Work to obtain a high-quality image. Therefore, the flowchart of FIG. 6 is executed.
  • step 11 when the reliability of the tomographic image at a certain slice position calculated in step 7 is low, for example, when the reliability of the image in FIG. 4 is low, the corresponding image is selected with the cursor on the list in FIG. In this state, select the recalculation execution button 75. Then, recalculation of the selected image with low reliability is started.
  • step 12 the operator inputs recalculation allowable parameters.
  • the recalculation allowable parameter gives a calculation index when recalculating the image selected in step 11.
  • P the target value of reliability
  • N the maximum number of calculation operations as the index to determine.
  • step 13 the R-wave position is re-specified by changing the R-wave position specifying parameter.
  • the R-wave position specifying parameter is the peak value of the R-wave, and if the peak value exceeds an arbitrary threshold Th, the R-wave is determined to be an R-wave.
  • the average cardiac cycle of the subject measured before imaging is Re
  • the cardiac cycle at the time of image measurement is Ra
  • the difference between the ratio of the two and 1 is also calculated.
  • the threshold value Th of the R wave height can be updated using the following equation (2).
  • Th Th + B * (1— Ra / Re) (2)
  • Equation 2 gives a new peak height threshold (Th) by subtracting the ratio of Ra and Re from 1 with respect to the previous peak height threshold Th n and further multiplying B by a weighting factor.
  • Equation 2 since the cardiac cycle is longer than the average value when collecting the measurement data, when it is considered that the R wave may have been overlooked, the pulse height threshold Th is lowered, and when the measurement data is collected, the cardiac cycle is increased by the average value. Since it is shorter, when it is considered that noise was picked up by mistake, an operation such as raising the peak height threshold Th can be performed.
  • the R-wave identification is repeatedly performed using a value obtained by sequentially reducing the re-specification threshold to an initial value, for example, 10%. ⁇ Adopt a method.
  • a change in the pulse height threshold Th performed in step 13 determines whether the specific position of the R wave has changed, for example, the force when the previous time was performed in step 3, for example. If yes, go to step 15 with Yes; if no, go back to step 13 with No.
  • step 15 the same steps as the creation of the projection data in step 5, the image reconstruction of the tomographic image in step 6, and the calculation of the reliability in step 7 are executed again.
  • step 16 it is determined whether or not the obtained image satisfies the allowable condition obtained in step 12. Specifically, if the reliability has reached the target value P, or if the number of calculation operations has exceeded the maximum value N, proceed to step 17 with Yes. Return to step 13 with No. When returning to step 13, the wave height threshold Th is raised and lowered again to try to change the specific position of the R wave.
  • step 17 the reliability is grouped in step 8, the tomographic image list is displayed in step 9, and the tomographic image is displayed in step 10 again.
  • step 11 the number of images for which recalculation is specified in step 11 may not be one. For example, it is also possible to collectively recalculate C groups with low reliability.
  • the reliability may not be improved so easily and may be executed indefinitely.
  • this may be the case where the cardiac cycle fluctuates due to the subject's arrhythmia, the case where the R-wave signal is completely missing, or the case where noise very similar to the R-wave signal is mixed.
  • the maximum value N of the number of calculation operations can be set in step 12. In other words, it is possible to stop the calculation when the number of times that the reliability does not improve even if it is calculated further. Steps 11 to 17 are also performed by the computer 12.
  • the R-wave position of the electrocardiographic information force read at the same time as the X-ray measurement is specified, and the heartbeat phase is determined based on the specified R-wave position.
  • a plurality of images are obtained, and the R-wave position is repeatedly specified while changing the R-wave position specifying parameter used for the R-wave specifying process, for example, the threshold value Th of the R-wave height. Then, the image is obtained repeatedly, so that the target value with reliability can be achieved.
  • the optimal R-wave position identification parameter at each measurement point without having to visually judge whether or not the appropriate reconstruction has been performed. Accuracy increases, and reliability of each tomographic image also increases.
  • FIG. 3 in Example 1 above shows that the R-wave 53 with the subject could not be identified as in FIG. 9 (c).
  • this example shows how to deal with the case where the corresponding projection data is missed.
  • FIG. This relates to the case where an R wave is erroneously detected.
  • the second embodiment uses the same apparatus configuration and the same processing as in the first embodiment unless otherwise specified. Therefore, the same components as those in the first embodiment are denoted by the same reference numerals.
  • step 2 in FIG. 2 and equation 2 are used instead of equation 1 in the reliability calculation means 7d in FIG. 1B.
  • the noise 61 is mistaken for the R wave, and the interval between the R wave 51 and the noise 61 is recognized as the R wave period Ra at the time of measuring each tomographic image.
  • the R-wave period Ra at the time of measurement is smaller than the average heartbeat period Re of the subject measured before the imaging.
  • Equation 3 below.
  • an electrocardiograph or the like picks up electromagnetic waves or the like from peripheral devices.
  • V When noise is generated. Even when there is noise due to the arrhythmia of the subject, Proper projection data can be collected without dropping the R-wave and used for image reconstruction, and the reliability of using the reconstructed image for diagnosis can be further improved.
  • the third embodiment uses the same apparatus configuration and the same processing as in the first embodiment unless otherwise specified. Therefore, the same components as those in the first embodiment are denoted by the same reference numerals.
  • Step 11 when the reliability of the tomographic image at a certain slice position calculated in Step 7 is low, for example, when the reliability of the image in FIG. 5 is low, FIG.
  • the recalculation execution button 75 was selected to recalculate the image.
  • a group having low reliability and a group having low reliability instead of an image is collectively selected.
  • the system is configured so that those in the C group with low reliability are collectively selected and recalculated.
  • selecting a group for example, if the part of the reliability C is selected from the reliability groups in FIG. 4, the group with C is selected all at once. Then, by pressing the recalculation execution button, the one with reliability C is continuously recalculated.
  • Images having the same reliability group often have similar R-wave determination values shown in Fig. 7. For this reason, for the images belonging to the same group, the number of repetitions of the loop for re-specifying the R wave position between steps 13 and 14 can be almost the same in many cases.
  • the present invention is not limited to the above-described embodiment, and can be variously modified and implemented without departing from the gist of the present invention.
  • the X-ray CT apparatus is not limited to a method in which an X-ray source and an X-ray detector are mechanically rotated to face each other. You can switch to X-ray irradiation from a point and use the X-ray method!
  • the X-ray detector is not limited to one having a single detector row in the body axis direction of the subject, but also includes one having a plurality of detector rows.
  • the reliability is a numerical value obtained by determining how much the average heart cycle of the subject matches the R-wave cycle at the time of tomographic image measurement.
  • Equation 3 the force using Equation 2 as an update equation for the R-wave position identification parameter.
  • the present invention is not limited to these.
  • Embodiment 13 is a method in which an ECG gate or a retroactive image to be reconstructed after imaging is considered.
  • Example 13 is not limited to this.
  • the present invention is also useful in an ECG trigger or a prospective case, for example, when extending the time between X-ray irradiation and measurement.
  • the ECG gate or retroactive and the ECG trigger or prospective will be described.
  • the feature of the ECG trigger or prospective is that only the data necessary for image reconstruction with less exposure is collected. is there.
  • 70% of the position when the interval between two adjacent R waves hereinafter referred to as the heartbeat cycle
  • the time of 7 seconds is determined as the scan start timing, and the gantry is rotated in synchronization with this R-wave, and X-rays are emitted at the view angle required for image reconstruction to project projection data.
  • a target tomographic image can be created. As a result, the occurrence of a situation in which the shooting is redone is reduced.
  • the present invention is particularly suitable for a case where projection data is acquired in combination with electrocardiographic information, such as an ECG gate or a retrospective. Furthermore, it is suitable for long-time imaging even in the case of ECG trigger or prospective, or when the projection data can be used in combination with ECG information.

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Abstract

L'invention concerne un dispositif de tomodensitométrie à rayons X lequel collecte les informations électrocardiographiques d'un sujet obtenues par un électrocardiogramme simultanément à la détection d'une dose de rayons X, calcule le point dans le temps d'une phase de fréquence d'impulsions spécifique à traiter en image sur la base d'une position d'onde R dans les informations électrocardiographiques, et reconstruit une image à l'aide des données de détection relatives à une dose de rayons X à ce point temporel pour capturer et afficher l'image tomographique du sujet, dans lequel la fiabilité indiquant si le point temporel de la phase de fréquence d'impulsion spécifique donne une phase ciblée ou non est calculé par un moyen de calcul de fiabilité pour permettre son affichage sur une unité d'affichage avec une image tomographique.
PCT/JP2004/008900 2003-06-25 2004-06-24 Dispositif de tomodensitometrie a rayons x WO2005000122A1 (fr)

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0767844A (ja) * 1993-09-03 1995-03-14 Fukuda Denshi Co Ltd 長時間心電図におけるｑｒｓ波検出装置及び方法
JPH08206089A (ja) * 1994-11-30 1996-08-13 Nec Corp 生体情報収録装置
JP2003164446A (ja) * 2001-11-26 2003-06-10 Ge Medical Systems Global Technology Co Llc 心臓イメージング方法及び装置
JP2004174006A (ja) * 2002-11-28 2004-06-24 Ge Medical Systems Global Technology Co Llc 信号獲得装置およびｘ線ｃｔ装置

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0767844A (ja) * 1993-09-03 1995-03-14 Fukuda Denshi Co Ltd 長時間心電図におけるｑｒｓ波検出装置及び方法
JPH08206089A (ja) * 1994-11-30 1996-08-13 Nec Corp 生体情報収録装置
JP2003164446A (ja) * 2001-11-26 2003-06-10 Ge Medical Systems Global Technology Co Llc 心臓イメージング方法及び装置
JP2004174006A (ja) * 2002-11-28 2004-06-24 Ge Medical Systems Global Technology Co Llc 信号獲得装置およびｘ線ｃｔ装置

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