JP2006047317A - Method for evaluating myocardial viability, and myocardial tomographic image processing apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a method for evaluating myocardial viability for grasping the delays, leads, or the like of the functions of local cardiac muscles. <P>SOLUTION: When the behavior of medicated radioactive medical drugs is analyzed, the count of the myocardium-tomogram data is evaluated, starting from a plurality of time phases in the local cardiac muscles. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to a myocardial viability evaluation method for analyzing the behavior of an administered radiopharmaceutical and a myocardial tomographic image processing apparatus using this evaluation method. In the present invention, evaluation of myocardial viability includes evaluation of cardiac function.

  In recent years, with the development of coronary intervention, an increasingly accurate diagnosis of myocardial viability is desired. As a typical diagnosis method, there is a myocardial viability evaluation method in which RI (radioisotope) is administered to a human body and its behavior is analyzed dynamically.

  Thus, for dynamic analysis of RI behavior, for example, 201Tl (hereinafter simply referred to as Tl) myocardial scintigraphy in which 201Tl (thallium chloride) is used for examination and interpretation. This Tl scintigraphy is roughly divided into a method of performing exercise load and drug load and a method of performing at rest.

  Tl myocardial scintigraphy that exercises or exercises is a method of inducing ischemia that cannot be obtained by resting Tl myocardial scintigraphy. By this, when each image immediately after loading and after resting after 3 to 4 hours after loading is compared, there is an advantage that the difference between the images becomes large so that diagnosis of myocardial viability is easy. Furthermore, in order to improve the diagnostic ability, devices such as a re-intravenous injection method and a delayed redistribution method have been made.

  In addition, in Tl myocardial scintigraphy at rest, the viability evaluation of the infarcted myocardium becomes a favorable scintigraphy for the patient without imposing a burden on the myocardium by imaging at rest, and excessive ischemia due to the load is prevented. There is an advantage that there are no worries about causing it.

  What supports the above Tl myocardial scintigraphy is a myocardial tomographic image processing apparatus. This myocardial tomographic image processing apparatus inputs myocardial spectroscopic images (hereinafter referred to as “myocardial tomographic images”) that are taken separately by a gunmachi camera and immediately after resting after 3-4 hours after loading. The maximum count of each tomographic data of the image immediately after loading and the image after resting is calculated without considering the phase, and the image immediately after loading and the image after resting are colored according to each level based on each maximum count. The short axis tomographic image is displayed in color with polar coordinates (concentric circles) or a developed view.

  However, in the conventional myocardial viability evaluation method described above, in the case of Tl myocardial scintigraphy that exercises exercise, since the exercise load depends on the subjectivity of the doctor, a difference occurs in the ischemic state of the myocardium depending on the load. There was a problem of poor reproducibility. In addition, in the case of resting Tl myocardial scintigraphy, there is a problem that it is difficult to discriminate because it cannot be compared with an image immediately after loading, and that scintigraphy can only be evaluated relative to the maximum value of the case. As described above, there is an element that any Tl myocardial scintigraphy misses the viable myocardium, and there is a big problem that the myocardial viability cannot be accurately evaluated.

  Moreover, in the conventional evaluation method of myocardial viability, since the diagnosis was made without considering any heartbeat or cardiac time phase, it was impossible to grasp changes occurring at each time phase. For example, the delay or progression of local myocardial function, or cardiac function in any direction remained unclear.

  Moreover, since Tl attenuates with time or is discharged from the human body immediately after loading and at rest for 3 to 4 hours after loading, it is impossible to measure the count under the same conditions. In addition, in the above-described conventional myocardial tomographic image processing apparatus, the myocardial image is distributed according to each level on the basis of the highest count level obtained at the time of each measurement immediately after loading and at rest. Is displayed. Therefore, even if each myocardial image immediately after loading is compared with resting myocardial images, the distribution criteria are different. Therefore, there is a problem that it is insufficient as a material for accurately evaluating myocardial viability. It was.

  Further, JP-A-2-226089 discloses that a myocardial tomographic image is arranged in polar coordinates by using a myocardial spectrum expert system that stores standard data relating to a normal person, and standard data and individual patient data. A method for automating the interpretation of data is disclosed. However, the standard data for normal subjects cannot be sufficiently dealt with myocardial diseases of different patients, and are based on tomographic data obtained by conventional myocardial tomographic image processing devices, so accurate interpretation is required. But I had to say that it was far from practical use.

  The invention of claim 1 has been studied in order to solve the above-described problems, and has an object to provide a method for evaluating myocardial viability so that the delay or advance of the function of the local myocardium can be grasped. And

  It is an object of the present invention to provide a method for evaluating myocardial viability so that the delay or advance of the function of the local myocardium can be grasped from the polar coordinates or the developed view in the short axis fault.

  An object of the invention of claim 3 is to provide a method for evaluating myocardial viability so that it can be grasped without overlooking the delay in contraction of the local myocardium at the end systole.

  An object of the invention of claim 4 is to provide an evaluation method in which an effective document for diagnosing myocardial viability by reflecting an arbitrary local cardiac function can be created.

  In addition to the object of claim 4, the invention of claim 5 is an evaluation method that enables creation of effective data for diagnosing myocardial viability by reflecting any local cardiac function with reference to the end diastole. The purpose is to provide.

  In addition to the objects of the inventions of claims 4 and 5, an object of the invention of claim 6 is to provide a method for evaluating myocardial viability so that a slight change in count of an arbitrary region can be clearly evaluated. .

  The related invention 1 of the present invention sets the maximum count at the end diastole for each patient as the standard for evaluation of the count by the heart rate scintigraphy of the heart rate synchronization method, and accurately determines the myocardial viability based on this standard. It is an object of the present invention to provide a method for evaluating myocardial viability that can be evaluated easily.

  In addition to the object of the invention of the related invention 1 of the present invention, the related invention 2 of the present invention provides a method for evaluating myocardial viability so that the end diastolic phase and other cardiac phases can be evaluated on the same basis. Objective.

  The related invention 3 of the present invention is based on the maximum count at the end diastole for each patient, and each myocardial tomographic data of an arbitrary tomogram is sequentially arranged for each time phase, and not only in myocardial blood flow but also in all three-dimensional directions. An object of the present invention is to provide a method for evaluating myocardial viability so that the cardiac function of a child can be grasped.

  Related invention 4 of the present invention provides a method for evaluating myocardial viability in addition to the object of related invention 3, in which the entire left ventricle is covered and sequentially displayed for each phase so that the cardiac function can be grasped. Objective.

  The related invention 5 of the present invention provides a myocardial viability evaluation method in which local regions of arbitrary cardiac phases on the short-axis tomographic plane can be matched in consideration of myocardial rotation accompanying contraction or expansion. The purpose is to do.

  A related invention 6 of the present invention is to provide a myocardial tomographic image processing apparatus which can evaluate myocardial viability from the remaining myocardial mass and the contraction ability of the remaining myocardium.

  The related invention 7 of the present invention aims to provide a myocardial tomographic image processing apparatus capable of evaluating the maximum count at the end diastole as a unified standard in addition to the object of the related invention 6.

  A related invention 8 of the present invention aims to provide a myocardial tomographic image processing apparatus which can be evaluated with the maximum count at the end diastole being 100% in addition to the object of the related invention 7.

  A related invention 9 of the present invention has an object to provide a myocardial tomographic image processing apparatus capable of visually expressing each state of the myocardium in addition to the object of the related invention 6.

  The related invention 10 of the present invention aims to provide a myocardial tomographic image processing apparatus capable of improving the visibility by a high-level distribution in addition to the object of the related invention 9.

  In the related invention 11 of the present invention, in addition to the object of the related invention 6, the locality of any cardiac phase image is matched by dealing with the rotational shift accompanying the contraction or expansion of the myocardium, and the myocardial viability is accurately expressed. An object of the present invention is to provide a myocardial tomographic image processing apparatus which can be used.

  The related invention 12 of the present invention has an object to provide a myocardial tomographic image processing apparatus capable of grasping the delay and progress of the function of the local myocardium in addition to the object of the invention of the related invention 6.

  In addition to the object of the invention of the related invention 12, the related invention 13 of the present invention is a myocardial tomographic image processing apparatus capable of grasping the delay and advancement of the function of the local myocardium based on the polar coordinates or the developed view in the short axis tomography. The purpose is to provide.

  A related invention 14 of the present invention aims to provide a myocardial tomographic image processing apparatus capable of grasping without overlooking the delay of contraction of the local myocardium in addition to the object of the invention of the related invention 13.

  The related invention 15 of the present invention aims to provide a myocardial tomographic image processing apparatus which makes it easy to visually understand the diagnosis and cardiac function of myocardial viability using the maximum count at the end diastole for each patient as a unified standard. To do.

  In addition to the object of the invention of the related invention 15, the related invention 16 of the present invention is a myocardial tomographic image processing apparatus which makes it easy to visually understand the diagnosis and cardiac function of myocardial viability based on the maximum count at the end diastole. The purpose is to provide.

  In addition to the object of the invention of the related invention 16, a related invention 17 of the present invention aims to provide a myocardial tomographic image processing apparatus that can change the distribution and perform diagnosis more easily.

  The method for evaluating myocardial viability according to the invention of claim 1 synthesizes a local maximum count between time phases from a plurality of time phases (hereinafter referred to as “maximum value synthesis”) when evaluating an arbitrary slice in any cardiac time phase. This is characterized by the fact that The delay or advance of local myocardial function due to contraction or expansion can be grasped by the maximum value synthesis in a plurality of time phases. The present inventor has named such maximum value synthesis as the maximum value synthesis method.

  The myocardial viability evaluation method according to the invention of claim 2 is characterized in that polar coordinates or a developed view is created from a short-axis fault. The lag and advance of local myocardial function due to contraction and expansion can be easily grasped by the maximum value synthesis method between a plurality of time phases from a short axis fault.

  The method for evaluating myocardial viability according to the invention of claim 3 is characterized in that a polar coordinate or a developed view at the end systole is created. The delay of local myocardial contraction can be grasped without omission.

According to the method for evaluating myocardial viability according to the invention of claim 4, the local cardiac function for each patient is expressed as follows: [In any local myocardium {(Counting myocardial tomographic data in any cardiac time phase-other cardiac time phase Myocardial tomography data count)
/ Count of myocardial tomographic data of other cardiac phases}] × 100%
It is characterized by being displayed using the change rate of the count represented by As an arbitrary cardiac time phase, myocardial tomographic data of the whole cardiac cycle can be used, and an arbitrary cardiac time phase and other cardiac time phases are different cardiac time phases.

  The myocardial viability evaluation method according to the invention of claim 5 is characterized in that the count of myocardial tomographic data of other cardiac phases is the count of myocardial tomographic data at the end diastole.

  The myocardial viability evaluation method according to the invention of claim 6 is characterized in that the change rate of the count can be changed and displayed based on an arbitrary distribution. As for the change rate of the count, the display level is changed according to the purpose, such as a slight change in count, a change above a certain level, or a change rate (negative increase rate) like a ventricular aneurysm.

  The evaluation method for myocardial viability according to the related invention 1 of the present invention is set so that the maximum count at the end diastole is used as a standard as a standard for count evaluation, and myocardial tomographic data of any cardiac phase based on this standard This is characterized in that the count of the above is evaluated. Here, the unified standard includes a relative standard that is different for each patient, but in any case, it is used as a unified standard that does not vary from one slice to another or each time phase. Arbitrary cardiac phase refers to the whole cardiac cycle related to any systole from end diastole to end systole and any diastole from end systole to end diastole. Myocardial tomographic data in this cardiac phase The count obtained from is the target. Here, the maximum count is retrieved from all the data at the end diastole, and this maximum count is used as a unified standard for any cardiac phase. The inventor named the evaluation method using such a unified standard as the unified standard method.

  The myocardial viability evaluation method according to related invention 2 of the present invention is characterized in that the maximum count at the end diastole is set to 100%.

  The myocardial viability evaluation method according to the related invention 3 of the present invention is characterized in that each myocardial tomographic image is sequentially arranged in an arbitrary tomography based on a unified standard by the unified standard method, and these are arranged for each time phase. Is. Arbitrary faults are short-axis faults, long-axis plane vertical faults, long-axis plane horizontal faults, etc., and these myocardial tomographic images are arranged in time series. The present inventor has named the method of arranging the myocardial tomographic images sequentially and time-sequentially in this way as the tomographic temporal phase arrangement method. The tomographic temporal phase array method includes myocardial tomographic data as a myocardial tomographic image, and includes an array of local myocardium at the same site.

  The myocardial viability evaluation method according to related invention 4 of the present invention is characterized in that the myocardial tomographic images are sequentially arranged so as to cover the entire left ventricle by the unified reference method. In the tomographic temporal phase arrangement method, the main purpose is to sequentially arrange so that the entire left ventricle is covered as a myocardial tomographic image.

  In the method for evaluating myocardial viability according to the related invention 5 of the present invention, when setting short-axis tomographic data of an arbitrary cardiac time phase, another short axis accompanying contraction or expansion with respect to any one short-axis tomographic plane is used. The feature is that the rotational deviation in the tomographic plane is corrected so that the local areas coincide with each other about the rotation axis. Since the myocardium rotates with contraction (the opposite is true for dilation), the local myocardium does not always match at the end diastole and end systole, and the rotation is corrected to match with the correspondence of the local myocardium. . The present inventor has named such rotation correction as a rotation correction method.

  A myocardial tomographic image processing device according to related invention 6 of the present invention includes a unified reference data setting means for evaluating based on a maximum count at the end diastole set for each patient as a unified reference for count evaluation stored in advance, and this count A cardiac phase data setting means for setting myocardial tomographic data corresponding to an arbitrary cardiac phase based on the above, and generating each myocardial image of each cardiac phase according to a predetermined distribution based on each data And a myocardial image creation means. A unified standard based on the unified reference method is used for an arbitrary cardiac phase, and a myocardial tomogram in an arbitrary cardiac phase is displayed based on the unified criterion.

  The myocardial tomographic image processing apparatus according to related invention 7 of the present invention is a diastole data setting unit in which the unified reference data setting unit evaluates with reference to the maximum count of the end diastole, and the myocardial image creation unit is arbitrarily set to the end diastole. Each myocardial image of the cardiac phase is created. Image processing is performed by measuring the counts of other cardiac phases based on the maximum count at the end diastole.

  The myocardial tomographic image processing apparatus according to the related invention 8 of the present invention is characterized in that the end diastole data setting means sets the maximum count at the end diastole to 100%. Image processing is performed by measuring the counts of other cardiac phases based on the maximum count at the end diastole. For example, in the end systole of a healthy part or a mild infarction part, it may be measured exceeding 100%.

  The myocardial tomographic image processing device according to the related invention 9 is characterized in that the myocardial image creation means sets an arbitrary range within a predetermined distribution range. As the distribution, in addition to the color distribution, it can be expressed by a density distribution, a luminance distribution, a graphic pattern, a count or a distribution by a graph for each area. In the present invention, an image is a concept including display by a graph.

  The myocardial tomographic image processing device according to related invention 10 of the present invention is characterized by adding a distribution having a higher level than the range of distribution of myocardial image data at the end diastole to the range of distribution of myocardial images at any cardiac phase. It is what. In any cardiac phase, distributions such as color, density, and brightness that are not at the end diastole are additionally displayed, and a visual contrast with the end diastole is expressed.

  In the myocardial tomographic image processing device according to the related invention 11 of the present invention, when the cardiac phase data setting means sets myocardial tomographic data of an arbitrary cardiac phase from the base of the myocardium to the apex, The present invention is characterized in that the rotation of another short-axis tomographic plane accompanying contraction or expansion is corrected with the axial tomographic plane as a reference. In the rotation correction, a shift due to rotation accompanying contraction or expansion is corrected using the center of the short-axis tomographic image as a reference, and the reference cardiac time phase image is matched with the local region.

  In the myocardial tomographic image processing device according to the related invention 12 of the present invention, when the cardiac time phase data setting means sets an arbitrary tomogram, local maximum value synthesis is performed between time phases from a plurality of time phases. It is characterized by. Since the cardiac time phase data is set by synthesizing the highest counts of a plurality of time phases, even if there is a delay or advancement of the function of the local myocardium by comparison with a single time phase, it can be displayed.

  The myocardial tomographic image processing apparatus according to the related invention 13 of the present invention is characterized in that the cardiac phase data setting means sets polar coordinates or a developed view from a short-axis slice as an arbitrary slice. The highest counts of multiple time phases are combined and displayed in polar coordinates or in a development view.

  In the myocardial tomographic image processing device according to the related invention 14 of the present invention, when the cardiac time phase data setting means sets the polar coordinate or development view at the end systole, the local maximum value synthesis between the time phases is performed from a plurality of time phases. It is characterized by doing so. Created in polar coordinates or development view representing the delay of local myocardial contraction.

  The myocardial tomographic image processing apparatus according to the related invention 15 of the present invention includes a unified reference data setting means for evaluating based on a maximum count at the end diastole set for each patient as a unified reference for count evaluation stored in advance, and this count A cardiac phase data setting means for setting myocardial tomographic data corresponding to an arbitrary cardiac phase based on the cardiac phase data, and between any cardiac phase tomographic data of any cardiac phase and any other cardiac phase tomographic data Cardiac function data setting means for setting local cardiac function data based on the rate of change of the count, and creating each myocardial image of any cardiac time phase and any other cardiac time phase according to a predetermined distribution An image creating means for creating a cardiac function image is provided. The count and rate of change are added after the count evaluation according to the unified standard, and the whole and details are displayed as an image.

  The myocardial tomographic image processing apparatus according to related invention 16 of the present invention is an end-diastolic data setting unit in which the unified reference data setting unit evaluates based on the maximum count of end diastole, and the cardiac function data setting unit is an arbitrary heart The end-diastolic myocardial tomographic data is used as the temporal myocardial tomographic data, and the image creating means uses the end-diastole as an arbitrary cardiac time phase. Based on the maximum count at the end diastole as a unified standard, the rate of change of the count is added, and the whole and details are displayed as an image based on the end diastole.

  The myocardial tomographic image processing device according to the related invention 17 of the present invention is characterized in that the image creating means is set in an arbitrary range within a predetermined distribution range. Distribution is changed according to the purpose of diagnosis.

  In the method for evaluating myocardial viability according to the first aspect of the present invention, since the local maximum value synthesis is performed from a plurality of time phases by the maximum value synthesis method, the tomographic data is evaluated. Can be grasped.

  In the method for evaluating myocardial viability according to the second aspect of the invention, polar coordinates or developments are created from the short-axis tomogram by the maximum value synthesis method, so that it is possible to grasp the delay or progress of the function of the local myocardium from the short-axis tomography. .

  According to the method for evaluating myocardial viability in the invention of claim 3, polar coordinates or a development view at the end systole is created by the maximum value synthesis method, and the delay of contraction can be grasped.

  Since the myocardial viability evaluation method in the invention of claim 4 displays the rate of change of counts in a plurality of time phases of the local myocardium, the rate of change can be treated as the cardiac function of each local myocardium for each patient. it can.

  Since the myocardial viability evaluation method in the invention of claim 5 displays the change rate of the count in the end diastole and an arbitrary cardiac time phase, the change rate is calculated as a local difference between the end diastole and another cardiac time phase. It can be treated as a cardiac function of the myocardium.

  The method for evaluating myocardial viability in the invention of claim 6 clearly expresses a slight count change in each local myocardium, focuses on observing a change of a certain level or more, or A display level can be freely set according to the purpose of the diagnosis or grasping what shows such a negative increase rate.

  Since the evaluation method of the myocardial viability in the related invention 1 of the present invention is based on the count of myocardial tomographic data of any cardiac phase based on the maximum count at the end diastole for each patient as a unified standard of count evaluation, The myocardial tomography of the cardiac phase is also expressed based on a unified standard, and comparisons can be made for each cardiac phase under the same conditions. This unified standard method can be used as a basic principle of myocardial viability.

  Since the maximum count at the end diastole is set to 100% in the method for evaluating myocardial viability in the related invention 2 of the present invention, any cardiac phase is expressed based on the maximum count at the end diastole, and is expanded under the same conditions. Comparison with the end stage becomes clear.

  In the method for evaluating myocardial viability in the related invention 3 of the present invention, the myocardial tomographic images are sequentially arranged for each time phase in accordance with the unified reference method and the tomographic temporal phase arrangement method. It is possible to grasp the heart function at

  The myocardial viability evaluation method in the related invention 4 of the present invention covers the entire left ventricle by the unified reference method and the tomographic temporal phase arrangement method, and these are sequentially displayed for each temporal phase. It becomes possible to grasp the cardiac function in the direction.

  The method for evaluating myocardial viability in the related invention 5 of the present invention is based on one short axis tomographic plane of an arbitrary cardiac phase, and rotational correction of another short axis tomography associated with myocardial contraction or expansion is performed by the rotation correction method. Since the correction is made so that the local areas coincide with each other around the rotation axis, it is possible to make the local areas of each cardiac phase image coincide with each other in consideration of the rotation accompanying the contraction or expansion.

  The myocardial tomographic image processing apparatus according to related invention 6 of the present invention evaluates the count based on the maximum count at the end diastole for each patient as a unified reference stored in advance by the unified reference data setting means, and the cardiac phase data setting means Based on the above count, tomographic data corresponding to a myocardial tomogram of any cardiac phase is set, and based on the set data, a myocardial image of any cardiac time phase is determined according to a distribution predetermined by the myocardial image creating means. Each image is processed.

  In the myocardial tomographic image processing apparatus according to the related invention 7 of the present invention, the end diastole data setting means is used as the unified reference data setting means, and this end diastole data setting means evaluates using the maximum count of the end diastole as the unified reference, Each myocardial image at the end diastole and any cardiac phase is created by the myocardial image creation means.

  The myocardial tomographic image processing apparatus according to the related invention 8 of the present invention sets the maximum count at the end diastole to 100%, and evaluates the counts in other cardiac phases based on this 100%.

  The myocardial tomographic image processing apparatus according to the related invention 9 of the present invention is visually expressed accurately by setting an arbitrary range within a predetermined distribution range by the myocardial image creating means.

  In the myocardial tomographic image processing device according to the related invention 10 of the present invention, a high-level distribution is added to a myocardial image of any cardiac phase, thereby improving the visibility.

  When the myocardial tomographic image processing apparatus according to the related invention 11 of the present invention sets myocardial short-axis tomographic data of any cardiac phase from the base of the myocardium to the apex by the cardiac time phase data setting means, the contraction or expansion is performed. The accompanying minor axis cross-section rotation is corrected.

  In the myocardial tomographic image processing device according to the related invention 12 of the present invention, since the local maximum count is synthesized from a plurality of time phases by the cardiac time phase data setting means, the delay or advance of the function of the local myocardium due to contraction or expansion is expressed. It becomes possible.

  In the myocardial tomographic image processing device according to the related invention 13 of the present invention, since the maximum value synthesis is performed by the cardiac phase setting means, the delay or advance of the function of the local myocardium accompanying contraction or expansion is expressed based on the polar coordinates or the developed view. It becomes possible.

  In the myocardial tomographic image processing apparatus according to the related invention 14 of the present invention, since the maximum value synthesis at the end systole is performed by the cardiac time phase data setting means, the contraction of the local myocardium is specified based on the polar coordinates or the developed view after specifying the end systole. It becomes possible to express the delay.

  The myocardial tomographic image processing apparatus according to the related invention 15 of the present invention evaluates based on the unified standard for each patient by the unified reference data setting means, and sets the arbitrary cardiac time phase based on the count by the cardiac time phase data setting means. Corresponding myocardial tomographic data is created, and the cardiac function data setting means is used to determine the locality based on the rate of change in the count between myocardial tomographic data at any cardiac phase and any other cardiac phase data. Cardiac function data is created, and each myocardial image of any cardiac time phase and any other cardiac time phase is created based on each data by the image creating means, and the cardiac function image is processed.

  In the myocardial tomographic image processing apparatus according to the related invention 16 of the present invention, the end diastole data setting means is used as the unified reference data setting means, and this end diastole data setting means evaluates the maximum count of the end diastole as the unified reference, Cardiac function data creation means uses myocardial tomography data at the end diastole as myocardial tomographic data at any cardiac phase, and image creation means uses the myocardial image and cardiac function image at the end diastole as any cardiac time phase To do.

  The myocardial tomographic image processing apparatus according to the related invention 17 of the present invention easily changes the distribution to an arbitrary distribution within a distribution range determined in advance by the cardiac function image creation means.

  As described above, according to the evaluation method according to the first aspect of the present invention, the tomographic data is obtained by synthesizing the local maximum counts between the time phases by the maximum value synthesis method. Delay and advance can be accurately evaluated.

  According to the evaluation method of the second aspect of the invention, since the short-axis tomographic data is obtained based on the maximum value synthesis method, the polar coordinates or the developed view is created to delay or advance the function of the local myocardium due to contraction or expansion. It is possible to accurately evaluate and to reliably prevent oversight of myocardial viability.

  According to the evaluation method of the invention of claim 3, even if there is a delay in contraction in the local myocardium by the maximum value synthesis method, the local maximum value is synthesized without overlooking the actual contraction. In addition to defining new end systole. This can reliably prevent oversight of myocardial viability due to delayed contraction of the infarcted myocardium.

  According to the evaluation method of the invention of claim 4, since the count change rate from the end diastole of the local myocardium for each patient to an arbitrary cardiac phase is displayed by the count change rate method, It can be treated as a cardiac function of each local myocardium.

  According to the evaluation method of the fifth aspect of the invention, since the count change rate from the end diastole of the local myocardium to an arbitrary cardiac phase is displayed by the count change rate method, this change rate is displayed for each local myocardium. Can be treated as a mind function.

  According to the evaluation method of the sixth aspect of the invention, the increase in the count is clearly expressed by the count change rate method, the focus is on observing the change of a certain level or more, and negative such as ventricular aneurysm It is possible to grasp what indicates an increase, and the display level can be freely set according to the purpose of diagnosis.

  According to the evaluation method according to the related invention 1 of the present invention, since the maximum end-diastolic count set for each patient by the unified reference method is used as a reference, the myocardial tomography in any cardiac phase is based on the maximum end-diastolic count. Compared with the end diastole, the myocardial tomography of any cardiac phase is expressed from the same standard, and the comparison between cardiac phases is clear. In particular, myocardial scintigraphy using the heartbeat synchronization method can be expressed from the maximum count of the end diastole, and the myocardial viability can be accurately evaluated by comparing the end diastole with the desired cardiac phase.

  According to the evaluation method according to the related invention 2 of the present invention, since the maximum count at the end diastole is set to 100%, the comparison with other cardiac phases becomes clear. In particular, when evaluating the end-diastolic phase and other cardiac phases using the unified criteria method, it is possible to display areas exceeding 100% in other cardiac phases, and when visual expression is performed. It can be evaluated more clearly.

  According to the evaluation method according to the related invention 3 of the present invention, each myocardial tomographic image of an arbitrary tomogram is sequentially arranged for each time phase by the unified reference method and the tomographic time phase arrangement method. Can evaluate cardiac function.

  According to the evaluation method according to the related invention 4 of the present invention, the entire left ventricle is covered by the tomographic time phase arrangement method and sequentially arranged for each time phase. Evaluate cardiac function in direction.

  According to the evaluation method according to the related invention 5 of the present invention, the rotation of the short-axis cross section accompanying the contraction or expansion of the myocardium is corrected by the rotation correction method. The locality of the phase image can be matched. By aligning the positions by correcting the shift due to the rotation of each local region from the base of the heart to the apex, it is possible to directly evaluate each local region.

  According to the myocardial tomographic image processing apparatus according to the related invention 6 of the present invention, the maximum count at the end diastole is evaluated as a unified standard for each patient and each cardiac phase is visually displayed. Therefore, it is possible to clarify the material to be performed from a comprehensive and objective viewpoint, and to evaluate the myocardial viability from the remaining myocardial mass and the contractility of the remaining myocardium.

  According to the myocardial tomographic image processing device according to the related invention 7 of the present invention, the end diastole and any cardiac time phase can be visually displayed from the unified standard, and any other cardiac time can be displayed based on the end diastole. The myocardial viability can be evaluated by comparing with the phase.

  According to the myocardial tomographic image processing device according to the related invention 8 of the present invention, the maximum count at the end diastole is set to 100%, and this can be easily compared with any other time phase.

  According to the myocardial tomographic image processing device according to the related invention 9 of the present invention, since the myocardial image is arbitrarily set by color distribution, graph display, etc., each state of the myocardium can be visually expressed accurately. .

  According to the myocardial tomographic image processing device according to the related invention 10 of the present invention, a high distribution can be added to the myocardial image in any cardiac phase, so that the contrast with the end diastole can be visually and clearly displayed. can do.

  According to the myocardial tomographic image processing device according to the related invention 11 of the present invention, it is possible to match the locality of an arbitrary cardiac phase image in response to the rotation accompanying the contraction or expansion of the myocardium, and to display the polar coordinate display and the developed view display. When performed, local comparison at the same display position can be performed.

  According to the myocardial tomographic image processing device according to the related invention 12 of the present invention, since the highest value is synthesized for each region in an arbitrary tomography from a plurality of time phases without being fixed to a single time phase, Progress can be grasped and myocardial viability can be accurately expressed.

  According to the myocardial tomographic image processing device according to the related invention 13 of the present invention, since the highest values are synthesized between the time phases in the short-axis tomography, the myocardial viability can be accurately expressed by polar coordinates and development views.

  According to the myocardial tomographic image processing device according to the related invention 14 of the present invention, it can be expressed as an end-systolic image without overlooking the delay in contraction of the local myocardium at the end systole.

  According to the myocardial tomographic image processing device according to the related invention 15 of the present invention, an arbitrary cardiac phase image is newly displayed using the maximum count at the end diastole as a unified reference for each patient, and the local rate is calculated from the rate of change of these counts. Since the cardiac function image is displayed together, the entire and local myocardial viability can be expressed.

  According to the myocardial tomographic image processing device according to the related invention 16 of the present invention, an arbitrary cardiac phase image is newly displayed from the maximum count at the end diastole, and the local cardiac function image is also calculated from the change rate of these counts. Can be displayed.

  According to the myocardial tomographic image processing apparatus according to the related invention 17 of the present invention, the distribution of the myocardial and cardiac function images can be independently changed according to the purpose of diagnosis.

Hereinafter, a preferred embodiment of the present invention will be described in detail with reference to the accompanying drawings.
Example 1.
In Example 1, a method for evaluating myocardial viability for analyzing the behavior of an administered radiopharmaceutical (referred to as “RI”) will be described.

  In this example, although RI is an example, 99mTc (pertechnesate, hereinafter referred to as “Tc”)-MIBI or 99mTc-sestamibi (hereinafter simply referred to as “Mibi”) is applied. Of course, it is not limited to mivi, and Tc preparations such as Tc-Tetrofosmin (tetrofosmin) and Tc-Teboroxime (teboroxime), or RI other than Tc may be used, and adsorbed or taken up by cardiomyocytes or interstitial If it stays, it can be applied for dynamic analysis. It can be applied to other nuclides and devices. For example, PET (positron emission tomography) or the like can be used.

  In the myocardial scintigraphy of the present example using such RI, an appropriate amount of the Tc preparation is intravenously administered at rest, and after 30 minutes or more, the heart rate synchronization tomographic image is collected by the heart rate synchronization method. . In the present invention, myocardial scintigraphy for applying exercise load and drug load is also included, but in the following description, the rest is described as an example.

  By the heartbeat synchronization method used in the present embodiment, a cardiac phase image of the whole cardiac cycle is obtained. In order to set the standard for comparison to the same condition, a new standard for counting evaluation was set by the uniform standard method. As this unified standard, for example, the maximum count at the end diastole is used, and this maximum count is set to 100%. By using this standard, the short axis tomographic image, the long axis vertical tomographic image, the long axis horizontal tomographic image in any cardiac phase are used. An arbitrary tomographic image such as an image is created. Any tomographic image is expressed at a level corresponding to the count. Note that this does not preclude evaluation by changing the maximum count to a standard other than 100%.

  Therefore, a method of expressing the level with a distribution such as color, density, luminance, graphic pattern, numerical value, and graph of each region is used so that the level can be visually and objectively understood. Whichever method is used, there is an advantage that the difference in count is easily grasped. As a method of expressing by color distribution, there are a tomographic temporal phase arrangement method, a polar coordinate display method obtained from a short-axis tomographic image, a developed view display method, and the like. Here, an example in which the level is expressed by a color distribution will be described.

  FIG. 1 is a diagram showing an example of a polar coordinate display distribution method used in the myocardial viability evaluation method according to the present invention. The display screen 22a of the color display unit 22 shows a table (hereinafter referred to as a color bar) used when the difference in count is expressed by color distribution, and C1 is a color bar used for the end diastole image. C2 indicates a color bar used for other cardiac phase images such as an end systolic image.

  First, the maximum count is searched from all the data at the end diastole, and this maximum count is used as a reference. In the normal part of the myocardium, if another cardiac phase image is expressed on the basis of the maximum count at the end diastole, the maximum count at the end diastole is exceeded. In order to cope with this, the level can be set so as to display a higher count than the color bar C1 of the end diastole image as shown in FIG. In the example shown in FIG. 1, the level of the color bars (C1, C2) is set stepwise for every n% (n is a positive number). For the color bar C2, for example, a two-stage level (110%, 120% or more) is set higher than the maximum count of the color bar C1. An arbitrary level such as 130% or 140% can be added so that the maximum count of each cardiac phase image can be displayed. The color bars C1 and C2 do not prevent the linear expression in addition to the stepwise display. What is important is that the count of an arbitrary cardiac phase image can be visually expressed using colors, with the maximum count at the end diastole as the unified standard.

  In FIG. 1, in order to display polar coordinates, the rotation of the myocardium accompanying contraction or dilation is corrected in advance by the rotation correction method so that the local portions of the time phase image used as a reference are matched. In FIG. 1, the side wall R is healthy in the infarct example of the anterior septum P and the lower wall (including the rear wall) Q. The healthy part R exhibits the maximum count in the end diastole image 31, and this count is set as 100% to evaluate the end systole image 32. The display level of the cardiac function image (hereinafter referred to as “functional image”) 33 can be freely changed independently according to the purpose of diagnosis. The count of the healthy part R exceeds 100% in the end systole image 32, but the change rate of the count in the functional image 33 is not so high. This is because the denominator when calculating the rate of change is large and, as a result, takes a small value, the functional image of the healthy part is expressed in a color exhibiting a low level.

  Further, the front wall septum P and the lower wall Q both exhibit a low count at the end diastole (the lower wall Q has a lower count than the front wall septum P). At the end systole, the count of the anterior septum P has risen considerably, but the count of the lower wall Q has only slightly increased. The functional image 33 shows the highest scale of the scale bar C2 in the front wall septum P (the rate of change of the count is extremely high), and it is understood that a sufficient function is maintained. Further, it is understood that the count change rate is considerably high in the lower wall Q. The viability of the anterior septum P can be easily diagnosed from the end-systolic image 32 and the functional image 33. However, in the lower wall Q, the existence of viability is difficult to understand only by the end-systolic image 32. In this case, if the functional image 33 is used together, it can be easily understood that the count change rate is high, and it can be understood that the lower wall Q has viability. Thus, it is very useful for evaluating the local myocardial viability with a low count in the end diastole image 31.

  Heretofore, myocardial scintigraphy using RI has been performed independently of the heart rate synchronization method, but even if it is evaluated using the conventional method (Tl myocardial scintigraphy) using the heart rate synchronization method, end diastole Images and end-systolic images were only relative evaluations with respective maximum counts at each time phase. According to the present embodiment, an arbitrary cardiac phase can be evaluated using the maximum count at the end diastole as a unified standard. This unified standard can be widely used for evaluation and diagnosis in all three-dimensional directions such as the state and function of the local myocardium, and the entire left ventricle, and can respond to provision of myocardial information that is clinically necessary. .

  As shown in FIG. 2, when using the development view display method, the end-diastolic and end-systolic myocardial images 31 ′ and 32 ′ and the functional image 33 ′ are developed on the display screen 22 a of the color display unit 22. Is displayed. In this development view display, for each myocardial image 31 ′, 32 ′ and functional image 33 ′, it is possible to display the region to be watched at an arbitrary position, but the place to open is usually a healthy part. is there. In FIG. 2, a developed view opened from the side wall R which is a healthy part is displayed, and color bars C1 and C2 can be displayed thereon, and the diagnosis method is the same as in the case of polar coordinate display.

  As shown in FIG. 3, the tomographic temporal phase arrangement method is used based on the unified reference method. As shown in the display screen 22a of the color display unit 22, the tomographic time phase arrangement method covers the entire left ventricle based on the heartbeat synchronization method with an arbitrary tomography, and these can be arranged sequentially for each time phase. . Since each myocardial tomogram shows a sequential change for each time phase, it is possible to grasp not only the local myocardial blood flow but also the cardiac function (wall thickness, rotation, shortening, dilation, pulling, etc.) in all directions. . This can be done by observing changes in the count of the local myocardium on each myocardial tomographic plane, changes in the area, thickness, and length of the count display area, etc. It is also possible to grasp the overall status and functions. In addition, the shortening or expansion in the direction perpendicular to each myocardial tomographic plane can be understood from the number of slices of the myocardial tomographic image at an arbitrary time phase. By using this tomographic time phase arrangement method together with the polar coordinate display method or the like, it is possible to grasp the overall state and function of the entire left ventricle. The tomographic temporal phase arrangement method is illustrated and explained on the assumption of a short-axis fault, but it is also easy to time-arrange any fault other than the short-axis fault. It is also possible to time-sequence the same part of the local myocardium to be watched by the tomographic time-phase array method.

  As shown in FIG. 4, the rotation of the short-axis tomographic plane is corrected based on an arbitrary temporary phase by a rotation correction method in consideration of the rotation accompanying contraction or expansion. As an arbitrary temporary phase, end diastole A can be used as a reference. A rotational shift accompanying the contraction or expansion of the cardiac phase B that corrects for the end diastole A is detected, and the cardiac phase B is adjusted to the degree of rotation of the end diastole A around the rotation axis O according to this rotational shift. A corrected cardiac phase B ′ is obtained. The rotational deviation differs for each time phase of the cardiac phase B, but is corrected so that the locality coincides with the end diastole A. The polar coordinate display method and the development view display method are performed from the short-axis tomographic data thus obtained, and the contrast of the local myocardium becomes clear. When rotation correction is not performed, it is possible to understand the state of rotation of the local myocardium.

  Next, as shown in FIG. 5, the maximum value synthesis can be performed by the maximum value synthesis method. When the delay related to contraction is exemplified as an arbitrary cardiac time phase, there is an infarct portion in which contraction is delayed as compared with the healthy portion. For this reason, if the end-systolic image is limited to a single time phase, the actual contraction may be overlooked. This is because there may be a local myocardium that exhibits the highest count in the time phase after the time phase set as the end systole. As shown in FIG. 5, a plurality of cardiac phases 32a and 32b are searched for in the vicinity of the end systole of the healthy part. In the previous cardiac phase 32a, the lower wall q has a lower count than the rear wall qb, but in the later cardiac phase 32b, the count of the lower wall q is reduced despite the decrease in the count of the rear wall qb. Since the count is increasing, it is understood that the contraction is delayed in the lower wall q. Therefore, in the plurality of cardiac phases 32a and 32b, the highest value of the lower wall q is used from the subsequent cardiac phase 32b, the highest value of the rear wall qb is used from the preceding cardiac phase 32a, and the locality of both of them is matched. Thus, the highest count of the lower wall (including the rear wall) Q of the end systole 32 is synthesized. In the front wall septum P and the side wall R, the maximum value is synthesized by the same method. In this way, it is desirable that the time phase of the end systole image is given a width, and the maximum value of each local count is synthesized from a plurality of time phases to create a polar coordinate or a developed view from a short axis fault as an arbitrary fault. If the myocardial tomogram obtained in this way is compared with the myocardial tomogram of a single time phase, it is possible to understand where the local area presenting the contraction delay is. Note that the maximum value synthesis method can target any fault other than the short-axis fault or any cardiac phase other than the end systole.

  FIG. 6 is an example different from FIGS. 1, 2, and 5, but as shown in FIG. 6, the change rate of the count from the end diastole image of each local myocardium to an arbitrary cardiac phase image is represented by a graph. Can do. Therefore, regarding the rate of change, [in any local myocardium {(count of myocardial tomographic data at any cardiac phase−count of myocardial tomographic data at end diastole) / count of myocardial tomographic data at end diastole} × 100% Desired. By displaying the change rate of the count in time series, the function of the local myocardium can be estimated. In this case, it is possible to express a slight change in the count clearly, to focus on observing the change above a certain level, to grasp a negative increase rate such as a ventricular aneurysm, or to diagnose The display level can be freely set according to the purpose. As shown in the color bar shown in FIG. 1, the level range can be set by selecting the color distribution, and distribution display other than the graph curve display is also possible.

  In the healthy part 81, a high count is displayed as a whole, and a high amplitude is indicated by a sudden rise. The healthy part 81 can be patterned from various factors such as the count level, the rising trend, the rising time, the height of the amplitude, and the differential analysis according to time, and the evaluation can be performed. Next, it is displayed that the count is not high in the infarct portions 82 and 83, and in particular, the time phase at which the maximum count is obtained is delayed in the infarct portion 83. Furthermore, since the ventricular aneurysm 84 is exposed to physical stress such as passive extension due to contraction of the healthy part, the count of the systolic phase 84 ′ is smaller than the count of the diastolic phase. Moreover, it becomes easy to specify a local area exhibiting a ventricular aneurysm with a negative increase rate. The present inventor named the heart function from the change rate of the count in this way as the count change rate method. The change rate of the count can be performed after the maximum value synthesis.

  FIG. 7 is a graph obtained by differentiating FIG. 6 with respect to time. The healthy part 81 shows a sharp rise and a high apex. On the other hand, the infarct portion 82 is inferior to the healthy portion 81. Further, the infarct portion 83 which has received greater damage than the infarct portion 82 exhibits delayed contraction. In the infarct portion 83, the height of the apex is not significantly different from that of the infarct portion 82, and the remaining myocardial mass is relatively maintained. However, the time to reach the apex is greatly delayed, and a decrease in function can be grasped. In the ventricular aneurysm 84, the positive and negative of the graph are reversed, and the identification is easy. Thus, by comparing the height of the apex and the time required to reach it with the healthy part 81, it becomes possible to measure the remaining myocardial mass and the remaining cardiac function. The present inventor named such a change rate of counts by time to grasp cardiac function as a count change rate time differential method. Count change rate time differentiation method is not limited to myocardial infarction, it can grasp the local myocardial state and function of cardiomyopathy, degenerative diseases such as infection, immunity, metabolism, etc. and other diseases, and diagnosis of diseases , Provide detailed information on the effectiveness of treatment, prevention, etc.

  As described above, according to the first embodiment, the unified reference method, the tomographic time phase arrangement method, the rotation correction method, the maximum value synthesis method, the count change rate method, and the count change rate time differential method are used alone or in combination. Thus, the myocardial viability and cardiac function can be accurately evaluated.

Example 2
Next, a myocardial tomographic image processing apparatus that specifically realizes the above-described first embodiment will be described using a second embodiment. In the following description, display using a short-axis tomographic image will be described as an example.

  FIG. 8 is a block diagram showing a schematic configuration of a myocardial tomographic image processing apparatus according to an embodiment of the present invention. The myocardial tomographic image processing apparatus 1 stores a tomographic data input unit 10 for inputting tomographic data obtained by a gamma camera, an operating unit 12 for performing key operations for image processing, and tomographic data of an arbitrary tomographic data. When obtaining the distribution of radiation (Tc) from the tomographic data storage unit 14 and the tomographic data, image reproduction is performed using an IC, and image processing such as tomographic time phase arrangement processing of the tomographic data, polar coordinate processing, development view processing, and the like is performed. A dedicated image processing unit 16, a display storage unit 18 for storing image-processed display data, and a color display of the image processing process, as well as any myocardial image or arbitrary end-diastolic image in any cardiac phase A color display unit 22 for displaying in color a cardiac function image obtained by imaging the rate of increase in the count to the cardiac phase image, and a series of image processing processes are printed in color and each of the above-mentioned myocardium The color printing unit 24 for color printing an image and cardiac function image, and a control unit 26 for controlling the entire apparatus, various data, address signals, and a bus 28 for transmitting control signals.

  The control unit 26 includes a CPU 26a that executes a control operation using a program, a ROM 26b that stores a control program for operating the CPU 26a, and a RAM 26c that is used as a work area for various control programs. The ROM 26b includes control programs (maximum count evaluation program, myocardial tomographic image construction program, display processing program such as polar coordinates and developed view, rotational deviation correction processing program, maximum value synthesis processing program, cardiac function shown in FIGS. And a control program such as a display program for forming the display screen shown in FIGS. 1 to 7 is stored. Each operation according to the flow of each figure is performed by each unit such as the image processing unit 16.

  The basic operation will be described with reference to FIGS. The image processing procedure is input from the tomographic data input unit 10 as tomographic data of an arbitrary tomography in an arbitrary cardiac time phase, and is stored in the tomographic data storage unit 14 (step 100). A case where a short-axis slice is selected as an arbitrary slice and an end diastole and an end systole are selected as arbitrary cardiac time phases will be described as an example (step 101). At the end diastole, the maximum count is retrieved and registered from all the data at the end diastole, and this maximum count is set to 100%, and other counts are evaluated in the subsequent processing (step 102). Since the search for the maximum count is the basis of this embodiment, it can be incorporated in an arbitrary step.

  Next, it is selected whether or not rotational deviation correction is required in the short axis fault (step 103). When a rotation deviation correction is instructed by operating the operation unit 12, rotation deviation correction is performed and registered in the image processing unit 16 (step 104). After selecting whether or not the rotation correction is necessary and processing, it is selected whether or not the short-axis tomographic plane is time-sequenced (step 105). When the time phase arrangement is instructed, the time phase arrangement processing is performed so as to cover the entire left ventricle and is registered in the image processing unit 16 (106). After selecting whether or not to perform time phase arrangement and processing, it is selected whether or not the highest value synthesis is required (step 107). When the highest value synthesis is instructed, the highest values among a plurality of time phases are synthesized and registered in the image processing unit 16. If the end systole is selected as an arbitrary cardiac time phase, the highest value at the end systole is synthesized (step 108).

  Next, image processing of the end diastole and the end systole as an arbitrary cardiac time phase is performed (step 109) and registered in the display storage unit 18. When processing a functional image, it is similarly registered in the display storage unit 18 (step 110). The processing of the functional image may be replaced with a step performed after selecting a cardiac function display described later.

  Various methods for displaying an image are selected as the display method. Here, only polar coordinates and a development view are illustrated and described (step 111). After selecting the polar coordinate display, whether or not to display the cardiac function is also selected (step 112). When the cardiac function is also displayed, each image is read from the display storage unit 18, and as shown in FIG. 1, an end-diastolic image 31, an end-systolic image 32 as an arbitrary cardiac phase image, and a functional image 33 Is displayed in color by polar coordinates. When the cardiac function is not displayed, the end diastole image 31 and the end systole image 32 as an arbitrary cardiac phase image are displayed in color (step 114).

  When the development view display is selected in step 111, the display method is different from the polar coordinate display described above. Each image is read from the display storage unit 18, and the developed views of the end diastole image 31 ′, the end systole image 32 ′, and the functional image 33 ′ are displayed in color as shown in FIG. 2 (steps 115 to 117). ).

  Furthermore, when other tomographic data other than the short axis fault is selected in step 101, the maximum count search is performed in the same manner as in step 102 described above (step 118). As shown in steps 119 to 120, tomographic data such as a major axis vertical fault and a major axis horizontal fault are processed in a tomographic time phase arrangement, and are subjected to image processing in steps 109 to 110. Other display methods are selected and displayed in color.

  The short axis tomographic plane rotational deviation correction process shown in FIGS. 11 and 4 will be described. When correcting the shift of the cardiac phase image due to each short-axis slice plane, as shown in FIG. 4, it is intended to correct the rotation of the short-axis slice plane of another whole cardiac cycle with reference to the short-axis slice plane at the end diastole. It is performed before polar coordinates or development processing. Of course, there is a case where the rotational deviation correction is not selected (see step 103).

  By operating the operation unit 12, a time phase that requires correction of rotational deviation is selected in the short-axis slice from the base to the apex (step 201). The degree of rotation necessary for correction is set for each time phase of the short-axis fault, and the number of each time phase is registered in the RAM 26c (steps 202 to 204).

  Then, when the rotation deviation correction is instructed by the operation of the operation unit 12 (step 205), the rotation deviation correction based on the degree of rotation corresponding to each time phase is executed according to the registered number of each time phase, and at the same time. The rotational deviation correction is executed linearly in accordance with the degree of rotation registered for the time phase not selected (step 206). As shown in FIG. 4, an arbitrary cardiac phase image B is corrected to the position of the end diastole A and re-stored as a cardiac phase image B '(step 207). Although the degree of rotation is specified only for the registered time phase, rotation may be specified for all necessary time phases.

  The maximum value synthesis process shown in FIGS. 12 and 5 will be described. As described above, since the myocardial contraction may be delayed at the end systole in the infarcted region, it is necessary to synthesize a local maximum value from a plurality of time phases. For the end systolic image, for example, when the time phase is set to 200 msec to 300 msec from the end diastole image (first image from the R wave), the highest count is obtained in the next time phase (300 msec to 400 msec) in a part of the infarcted myocardium. (See infarct portion 83 in FIG. 6). In such a case, there is a risk of misdiagnosis of some myocardial viability evaluations. In order to remove this risk, the time phase of the end systole image is set to an arbitrary period (between a plurality of time phases), and the maximum value synthesis of each local area is made possible. As the accuracy of time resolution improves, the highest value synthesis will be indispensable.

  The procedure for setting the maximum value composition will be described with reference to FIG. The maximum value synthesis is performed after the process for determining whether or not to select the rotation correction. An arbitrary plurality of time phases, for example, 32a and 32b are selected by the operation of the operation unit 12. For example, the time phase of the end systolic image can be set to 200 msec to 400 msec as described above (step 301). Of course, it can be arbitrarily set such as 200 to 500 msec or 300 to 700 msec. In accordance with the selected time phase, the highest count is searched for each local area of each short-axis slice from the base to the apex (steps 302 and 303). The short-axis tomographic data detected in this way is registered as an end systolic image 32.

FIG. 13 is a flowchart showing image processing for cardiac function. First, the count of local myocardium that needs to be evaluated is detected from the short-distance tomographic data at the end diastole and the end systole as an arbitrary cardiac time phase from the tomographic data storage unit 14 (steps 401 to 402). Then, an increase rate of the count (referred to as a functional score “FS”) is calculated by the following equation (step 403). That is,
F. S. = {(ES-ED) / ED} × 100 (%)
ED: end diastole count,
ES: End systolic count.

  The processing in steps 401 to 403 is performed for each tomographic plane from the base of the short axis to the apex (step 404), and when the processing of all the regions is completed, polar coordinate processing by counting and color bars is selected. (Step 405). As shown in FIG. 1, the color display unit 22 displays the end-diastolic and end-systolic myocardial images 31 and 32 and the functional image 33 on the display screen 22a, and at the same time, the color bars C1 and C2. Display is made.

  Next, the color distribution process shown in FIG. 14 will be described. The maximum count of Tc in the end diastole data is searched, and the color distribution range of the color bar C1 as shown in FIGS. 1 to 3 is set based on this maximum count. The color bar C1 is displayed uniformly or arbitrarily distributed with the maximum count being 100%, and a color bar C2 including a high level distribution can be added. The color bar C1 is used at the end diastole and the color bar C2 is used at the end systole. Note that the cardiac function is not compared with the end diastole, but the rate of change is visualized, so that it can be set to a different level (step 501). The count of an arbitrary cardiac phase is evaluated based on the maximum count, and the color distribution of each myocardial image in the end diastole and the arbitrary cardiac phase is created (steps 502 to 503). Further, the color distribution of the functional image is created by the above-described calculation formula (step 503).

  As described above, according to the second embodiment, the unified reference method, the tomographic time phase arrangement method, the rotation correction method, the maximum value synthesis method, the count change rate method, and the count change rate time differentiation method are embodied and processed. Therefore, it is possible to provide a myocardial tomographic image processing apparatus that accurately evaluates myocardial viability and cardiac function.

It is explanatory drawing which shows an example which displayed the myocardial viability evaluation method which concerns on the related invention of this invention on the polar coordinate. It is explanatory drawing which shows an example which displayed the expanded view the evaluation method of the myocardial viability which concerns on the related invention of this invention. It is explanatory drawing which shows an example which displayed the evaluation method of the myocardial viability which concerns on the related invention of this invention based on the tomographic temporal phase arrangement method. It is explanatory drawing which shows an example of rotation shift correction | amendment of the evaluation method of the myocardial viability which concerns on the related invention of this invention. It is explanatory drawing which shows an example of the highest value synthesis | combination of the evaluation method of the myocardial viability which concerns on this invention. It is a graph which shows an example of the count change rate of the evaluation method of myocardial viability concerning the present invention. It is a graph which shows an example of the count change rate time differentiation method of the evaluation method of myocardial viability according to the present invention. 1 is a block diagram showing a schematic configuration of a myocardial tomographic image processing apparatus according to the present invention. It is a flowchart explaining the image processing procedure by the myocardial tomographic image processing apparatus according to the present invention. It is a flowchart explaining the image processing procedure by the myocardial tomographic image processing apparatus concerning this invention following FIG. It is a flowchart explaining the procedure of the rotation shift correction by the myocardial tomographic image processing apparatus according to the present invention. It is a flowchart explaining the synthetic | combination procedure of the highest count by the myocardial tomographic image processing apparatus concerning this invention. It is a flowchart explaining the image processing procedure of the cardiac function by the myocardial tomographic image processing apparatus according to the present invention. It is a flowchart explaining the color distribution processing procedure by the myocardial tomographic image processing apparatus according to the present invention.

Explanation of symbols

10 tomographic data input unit 12 operation unit 14 tomographic data storage unit 16 image processing unit 18 display storage unit 22 color display unit 24 color printing unit 26 control unit 26a CPU
26b ROM
26c RAM
28 Bus 31, 31 'End diastole image 32, 32' End systole image 33, 33 'Functional image (cardiac function image)
C1, C2 color bar

Claims (6)

  In the evaluation method of myocardial viability to analyze the behavior of administered radiopharmaceuticals, when evaluating any tomographic data at any cardiac time phase, the highest local count between time phases was synthesized from multiple time phases. A method for evaluating myocardial viability characterized by the above.   2. The myocardial viability evaluation method according to claim 1, wherein polar coordinates or a developed view are created from a short-axis fault.   3. The method for evaluating myocardial viability according to claim 2, wherein polar coordinates or a development view at the end systole are created. In the evaluation method of myocardial viability that analyzes the behavior of administered radiopharmaceuticals, the local cardiac function for each patient is displayed using the rate of change of the count expressed by the following formula. Evaluation methods.
[In any local myocardium, {(count of myocardial tomographic data at any cardiac phase-count myocardial tomographic data at other cardiac phases)
/ Count of myocardial tomographic data of other cardiac phases}] × 100%   5. The myocardial viability evaluation method according to claim 4, wherein the count of the myocardial tomographic data of another cardiac phase is the count of the myocardial tomographic data at the end diastole.   6. The myocardial viability evaluation method according to claim 4, wherein the change rate of the count can be changed and displayed based on an arbitrary distribution.

Images