JP4750922B2 - Radiation diagnostic equipment - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to a radiation diagnostic apparatus, and more particularly to a radiation diagnostic apparatus that facilitates puncture of a puncture needle for tissue collection or the like on a subject.
[0002]
[Prior art]
Conventionally, a method has been implemented in which a tomographic image of a subject is acquired by an X-ray CT apparatus and a puncture needle for tissue collection or the like is punctured based on the tomographic image. This is because the tomographic image of the subject appearing on the screen (particularly, the image of the target site such as the affected part) and the image of the puncture needle are confirmed at the same time, and the actual subject while grasping the positional relationship between them. This is a kind of surgery for performing a puncture operation of a puncture needle. At this time, in particular, the tomographic image screen is used so that the tip of the puncture needle definitely reaches the target site in the subject.
[0003]
Specifically, it is performed according to the following procedure. First, an X-ray tomographic image of a subject is acquired in advance, and an image of an affected part or the like that is a target site in the tomographic image is registered. Next, the puncture start position on the body surface that will reach the affected area is determined by appropriate means, and puncture of the puncture needle is started here. Then, while confirming the positional relationship between the affected part and the tip of the puncture needle based on the tomographic image of the subject and the image of the puncture needle projected therewith, the entry direction or angle of the puncture needle, the degree of entry, etc. Puncturing work is performed while adjusting.
[0004]
[Problems to be solved by the invention]
However, the conventional puncturing operation as described above has the following problems. First, an image to be displayed is fixed to a predetermined size at the time of tomographic image acquisition, and the puncturing operation has to be performed while using the image of that size thereafter. In other words, since the displayed image was the same size from the start of puncture of the puncture needle until it reached the affected area, it was not possible to respond in detail depending on the size of the affected area and the progress of the puncture work.
[0005]
More specifically, when the image is the same size and the affected part W is small, as shown in FIG. 8, whether the puncture needle S has reached the affected part W or the like accurately as shown in FIG. This is extremely difficult to understand. In order to eliminate such harmful effects, if an image is enlarged and displayed in advance and a measure is taken so that a small affected part W or the like can be seen large, this time, as shown in FIG. It becomes impossible to confirm the puncture start position for the specimen. That is, in such a case, as shown by the dotted line in the figure, the image of the body surface of the subject protrudes from the screen and does not appear on the screen.
[0006]
The present invention has been made in view of the above circumstances, and an object of the present invention relates to a puncture operation of a puncture needle using a tomographic image, and grasps a positional relationship between a puncture needle and a target site in a subject, etc. It is an object of the present invention to provide a radiodiagnostic apparatus capable of always performing an accurate puncturing operation appropriately.
[0007]
[Means for Solving the Problems]
The present invention takes the following means in order to solve the above problems.
[0008]
That is, the radiation diagnostic apparatus according to claim 1 is a radiation diagnostic apparatus that reconstructs a tomographic image of the subject based on a result of detection of radiation emitted from a radiation generation source by the radiation detector through the subject. In monitoring the operation of puncturing the puncture needle with respect to the predetermined target site in the subject using the screen on which the tomographic image is displayed, during the operation, the predetermined target site and the puncture needle Tip Before An image recognition unit for obtaining coordinate values on the tomographic image; The tip of the puncture needle and the target site Based on the coordinate value Finding the distance on the tomographic image between the tip of the puncture needle and the target site, based on the distance The tip of the puncture needle and the target site are constantly monitored on the screen by adjusting the magnification of the tomographic image and the projection positions of the tip of the puncture needle and the target site on the screen. An image adjusting means for holding in a possible state is provided.
[0009]
The radiation diagnostic apparatus according to claim 2 Using a screen on which the tomographic image is displayed in a radiation diagnostic apparatus for reconstructing a tomographic image relating to the subject based on a result of detection of radiation emitted from a radiation source through the subject by a radiation detector In monitoring the operation of puncturing a puncture needle with respect to a predetermined target site in the subject, coordinate values on the tomographic image of the predetermined target site and the tip of the puncture needle are obtained during the operation. Based on the image recognition unit and the coordinate value of the tip of the puncture needle, an approach speed of the tip of the puncture needle to the subject is obtained, and based on the approach speed, the enlargement rate of the tomographic image and the puncture Image adjusting means for adjusting the projection position of the tip of the needle and the target site on the screen so that the tip of the puncture needle and the target site are constantly monitored on the screen. Preparation It is It is characterized by that.
[0011]
Claim 3 The radiation diagnostic apparatus according to claim 1. Or 2 In the above-described apparatus, the image adjustment unit adjusts the enlargement factor and the projection position based on a voice uttered by an operator who performs the work.
[0013]
DETAILED DESCRIPTION OF THE INVENTION
Hereinafter, embodiments of the present invention will be described with reference to the drawings. FIG. 1 is a schematic diagram showing a configuration example of an X-ray CT apparatus (radiation diagnostic apparatus) according to an embodiment of the present invention. In this figure, the X-ray CT apparatus includes an X-ray tube (radiation source) 1 and an X-ray detector (radiation detector) 2. These are arranged opposite to each other as shown in the figure, and both rotate as shown by arrows in the figure. That is, the X-ray tube 1 and the X-ray detector 2 are arranged so as to sandwich the subject P when X-ray exposure is performed on the subject P, which is a normal state of use of the present apparatus.
[0014]
The subject P is placed (laid down) on the top 3 configured to be movable in the direction perpendicular to the plane of FIG. The top plate 3 is provided on a couch (not shown), and can be moved in the body axis direction (perpendicular to the plane of FIG. 1) on the couch. The subject P is in the state in which the top 3 is present on the far side (or near side) in FIG. 1, that is, in the state where the X-ray tube 1 and the X-ray detector 2 are drawn out from the facing part. When the X-ray exposure is performed in advance on the plate 3, the subject P is inserted into the front side (or back side) of FIG. 1 together with the top plate 3, and the X-ray tube 1 and the X-ray detector 2 are inserted. It will be arranged between.
[0015]
The X-ray tube 1 is connected to an X-ray generator 1a including a high voltage power source and the like. Further, the X-ray detector 2 is configured, for example, by arranging a large number of detection elements in the CH direction (for example, 500 to 1000 ch). The X-rays emitted from the X-ray tube 1 are exposed in a fan shape to the subject P as shown by the dotted line in FIG. In this case, a “slice position” for the subject P is defined as a portion where the fan shape and the subject P intersect (or a position where the fan shape “cuts” the subject P, so to speak).
[0016]
The X-ray that has passed through the subject P has a large amount of absorption due to the presence / absence of an organ or the like, and this causes an intensity distribution for the transmitted X-ray. In the X-ray detector 2, X-ray information having such an intensity distribution, that is, X-ray information including information inside the subject P is detected and acquired.
[0017]
Then, as described above, the X-ray tube 1 and the X-ray detector 2 rotate around the subject P, so that the X-ray information is acquired in multiple directions with respect to the slice position. Then, the electrical signal is sent to the image processing unit 4 via the data collection unit 8 and the preprocessing unit 9.
[0018]
The data collection unit 8 is connected to the X-ray detector 2 and receives the electrical signal from the X-ray detector 2. In the data collecting unit 8, the output signal, which is an electrical signal, is amplified by an amplifier, and the amplified signal is serially sent out by a multiplexer in units of channels determined for the detection elements. It is converted into a digital signal by the D converter.
[0019]
Then, as shown in the block diagram of FIG. 2, the digital signal is converted into “raw projection data” (hereinafter simply referred to as “projection data”) by an appropriate calibration process in the preprocessing unit 9, and then stored in the memory. It is sent to the image processing unit 4 via M.
[0020]
The image processing unit 4 reconstructs a tomographic image related to the subject P based on the projection data received in this way. The reconstructed tomographic image is displayed on a monitor (screen) 5a constituting the image display unit 5 connected to the image processing unit 4 (see FIG. 3).
[0021]
On the other hand, the X-ray tube 1 and the X-ray detector 2 described above are electrically connected via a slip ring (not shown), whereby the X-ray tube 1 and the X-ray detector 2 are While continuously rotating around the subject P, multi-directional X-ray information relating to the subject P required for reconstruction of one tomographic image can be continuously collected. The data collection unit 8 is connected to the X-ray detector 2 via the slip ring.
[0022]
According to such continuous rotation, for example, the projection data at the same slice position can be continuously acquired, and the tomographic image can be continuously displayed on the image display unit 5. According to the continuous display of the tomographic image, for example, it is possible to trace the change of the tomographic image due to the inflow or outflow of the contrast agent administered to the subject P from time to time. In particular, according to this method, when the puncture operation according to the present invention is performed, it is also possible to track the progress of the puncture needle in the subject P from time to time. Such a method is known as a so-called “dynamic scan”.
[0023]
As another example, by moving the top 3 in synchronization with the continuous rotation of the X-ray tube 1 and the X-ray detector 2, the slice position with respect to the subject P is changed to a spiral shape. It is also possible to obtain the tomographic image of the subject P over a wide range (with respect to the body axis direction) by acquiring the projection data. Such a method is known as a so-called “helical scan”.
[0024]
In the X-ray CT apparatus according to the present embodiment, the case where the above-described “dynamic scan” or the like is performed is referred to as operation or operation in the “fluoroscopic mode”. On the other hand, for example, a case where the X-ray tube 1 and the X-ray detector 2 are rotated at least (usually once) to reconstruct a tomographic image is referred to as an “imaging mode”. In this “imaging mode”, the change in the tomographic image that changes from moment to moment as described above is not tracked, but it is possible to obtain a tomographic image with higher spatial resolution, that is, a more precise and finer image.
[0025]
In addition, the acquisition and display of the tomographic image that changes every moment in the “perspective mode” is specifically performed as follows, for example. That is, during continuous rotation of the X-ray tube 1 and the X-ray detector 2, projection data sequentially sent from the data acquisition unit 8 and the preprocessing unit 9 are stored in the memory M, and the memory M In this case, every time the projection data necessary for constructing at least one tomographic image is sequentially accumulated, it is sent to the image processing unit 4 (or read from the memory M). Acquisition and display (confirmation) of a real-time tomographic image related to the subject P can be performed.
[0026]
In other words, in this case, the tomographic image reconstruction and its display are performed as soon as the projection data necessary for constructing at least one tomographic image is accumulated in the memory M, and in parallel with this, Since acquisition of X-ray information, data collection and preprocessing, and accumulation in the memory M are continuously performed in the line detector 2, a so-called “cine video” -like image ( Tomograms) are continuously displayed.
[0027]
In such a case, it is needless to say that the reconstruction processing in the image processing unit 4 is preferably as fast as possible. In order to realize this high-speed processing, for example, the image processing unit 4 is constituted by a plurality of processors and processed in parallel, or the “number of views” to be reconstructed is reduced or reconstructed. Processing such as selecting the detection elements as appropriate and thinning them out may be performed. Here, the “number of views” is the number of projection data collected per rotation by the X-ray tube 1 and the X-ray detector 2 and is, for example, 900 views / rotation. Further, for example, when the detection element to be reconfigured is “thinned out” as described above, the thinned portion may be appropriately interpolated at the time of display.
[0028]
In addition, regarding the “reconstruction rate”, which is the rate at which tomographic images are reconstructed with respect to the number of rotations (or time required for one rotation) of the X-ray tube 1 and the X-ray detector 2, For example, one tomographic image may be reconstructed per rotation of the X-ray tube 1 and the X-ray detector 2.
[0029]
Further, in such a “perspective mode”, the number of continuous rotations of the X-ray tube 1 and the X-ray detector 2 is set to a number of times, or the projection “necessary for constructing at least one tomographic image”. How to define the data is basically free in the present invention. For example, the continuous rotation speed is “50 times”, and projection data constituting one tomographic image is “all angles (0 to 360 °) with respect to the subject P” or “half angle (0 to 180 °)”. The projection data acquired for “” may be used.
[0030]
However, the “continuous rotation speed” has a generally preferable upper limit because of the heat resistance performance of the X-ray tube 1 and the request to reduce the exposure dose to the subject P as much as possible.
[0031]
Incidentally, an image recognition unit Q is attached to the image processing unit 4. The image recognition unit Q is based on the information of each pixel constituting the tomographic image 50 as shown in FIG. 3 reconstructed by the image processing unit 4, and by using a known image recognition method, the affected part W and the puncture needle The leading end Y of S is automatically recognized as it. Simultaneously with this recognition, coordinate values on the tomographic image 50 relating to the affected part W and the tip Y of the puncture needle S are also obtained.
[0032]
Further, the image recognition unit Q is provided with an image adjusting means 6. Generally speaking, when the puncture needle S is punctured with respect to the subject P, the image adjusting means 6 is such that the affected part W, which is the target site of the puncture, and the distal end Y of the puncture needle S are On the tomographic image 50 screen reconstructed based on the X-ray information detected by the X-ray detector 2, the enlargement ratio of the tomographic image 50, the affected area W, and the affected area It has a function of adjusting the projection position of the image of the tip Y of the puncture needle S on the monitor 5a. In order to achieve such adjustment of the enlargement ratio and the projection position, the image adjusting means 6 has a function specifically described below.
[0033]
First, based on the “distance” on the tomographic image 50 between the affected part W and the puncture needle tip Y (see reference numeral D in FIG. 3), the function of adjusting the magnification and projection position described above. . Note that the distance D is obtained from coordinate values related to the affected part W and the distal end part Y of the puncture needle S obtained by the image recognition unit Q.
[0034]
Here, the calculation of the enlargement ratio or the like from the distance D is specifically performed, for example, when the distance D between the image of the affected area W and the image of the distal end portion Y of the puncture needle S is large, the enlargement ratio is reduced. When the distance is small, adjustment such as increasing the enlargement ratio is performed, and in each case, the image of the affected part W and the puncture needle S (and its tip Y) is monitored in accordance with the change in the enlargement ratio. The projection position on 5a is adjusted. Further, the correspondence between the distance D and the enlargement ratio may be set so as to have, for example, a proportional relationship or an exponential function relationship. By doing so, the affected part W and the distal end Y of the puncture needle S always appear on the monitor 5a and are always placed in a monitorable state, and the operator confirms that. The puncture operation can be performed while doing so.
[0035]
The second function is to adjust the magnification and projection position described above based on the voice of the surgeon performing the puncturing operation of the puncture needle S. In this case, as shown in FIG. 2, the voice input means 7 attached to the image adjusting means 6 is used. The voice input means 7 is composed of elements necessary for discriminating human voice, such as a microphone 7a and a voice recognition device 7b. The voice input from the microphone 7a is classified into a plurality of types by the voice recognition device 7b on the basis of the discrimination ability of the voice recognition device 7b. This is performed for the adjusting means 6. Based on this output, the image adjustment means 6 changes the magnification and projection position as appropriate.
[0036]
For example, when the voice recognition device 7b is configured to discriminate between two classifications of “large” voice and “small” voice uttered by the surgeon, a signal corresponding to the former classification is displayed as an image. When received by the adjusting means 6, the enlargement ratio of the tomographic image 50 is increased by a predetermined amount, and the projection position on the monitor 5a of the affected area W and the puncture needle tip Y is automatically adjusted as the enlargement ratio increases. In other words, when the image adjustment means 6 receives a signal corresponding to the latter classification, the reverse operation is performed. According to such means, the affected part W and the tip Y of the puncture needle can always be monitored and the operator's desired screen can be displayed as described above.
[0037]
As a matter of course, the present invention is not limited to the above-mentioned form with respect to the voice input means 7, and various other variations can be assumed. For example, it is specified that the surgeon should utter “zoom” instead of “large” as described above, or perform voice recognition such as “make the affected area display a little to the right” more directly and finely. Based on this, the tomographic image 50 may be adjusted so as to realize the audio content generated by the image adjusting means 6.
[0038]
Hereinafter, the operation and effect of the X-ray CT apparatus having the above configuration will be described along an example of a work procedure.
[0039]
First, the subject P is set on the top plate 3 drawn out of the facing portions of the X-ray tube 1 and the X-ray detector 2, and the top plate 3 on which the subject P has been set is placed on the top plate 3 described above. It is inserted and arranged between the tube 1 and the X-ray detector 2. Then, the apparatus is operated or operated in the above-described “fluoroscopic mode”, and the tomographic image 50 relating to the subject P is acquired while rotating the X-ray tube 1 and the X-ray detector 2 together.
[0040]
Next, based on the acquired tomographic image 50, the surgeon confirms an image of the affected area W in the subject P in order to insert another puncture needle S for tissue collection or drug injection. Subsequently, the puncture start position is specified on the surface of the subject P body so that the puncture needle S reaches the image of the affected part W, and the puncture of the puncture needle S is started from this position.
[0041]
At this time, due to the continuous rotation of the X-ray tube 1 and the X-ray detector 2, projection data is continuously stored in the memory M, and projection data necessary for constructing at least one tomographic image is present. Each time it is accumulated, it is reconstructed as a tomographic image in the image processing unit 4, and the tomographic image is displayed on the monitor 5 a of the image display unit 5. The image recognizing unit Q recognizes the image of the affected part W and the tip Y of the puncture needle S with respect to the tomographic image 50 that is sequentially reconstructed and displayed, and obtains coordinate values on the tomographic image 50 of both of them. The distance D between the affected part W image and the tip Y image of the puncture needle is obtained from the coordinate values.
[0042]
Next, based on the distance D obtained as described above, the image adjusting unit 6 appropriately displays the image of the affected part W on the tomographic image 50 and the tip Y of the puncture needle S on the monitor 5a of the image display unit 5. The enlargement ratio of the tomographic image 50 and the projection positions of the two are adjusted so that they fall within the range. Such adjustment work is repeatedly executed during the puncture work in the first embodiment. That is, the distance D between the affected part W image and the tip Y image of the puncture needle S is regularly and automatically monitored based on the tomographic images 50 sequentially reconstructed and displayed as described above. Based on the distance D, the enlargement ratio and the projection position are changed.
[0043]
Here, “periodically” is used. However, in some cases, the configuration may be changed “as needed”, and the image of the affected area W and the image of the tip Y of the puncture needle S may be changed. A configuration may be adopted in which when the change rate of the distance D exceeds a certain predetermined limit, the enlargement rate and the projection position are changed.
[0044]
Specifically, for example, it is as follows. First, at the beginning of the puncture of the puncture needle S, the affected part W and the puncture needle tip Y are in a relatively separated state, that is, a state in which the distance D between the two images is large, as shown in FIG. The enlargement ratio is set to a small value, and the entire field of view is configured such that the puncture start position A and the affected area W can be accommodated on the entire screen of the monitor 5a. On the other hand, when the puncture needle S enters the subject P one step further than in FIG. 4 and the distance D between the affected area W and the puncture needle tip Y becomes smaller than the above, FIG. As shown in FIG. 3, the display is changed to an image display in which the enlargement ratio of the tomographic image 50 is large. Along with this, adjustments regarding these projection positions are also performed so that both the affected part W and the puncture needle tip Y are projected on the monitor 5a.
[0045]
Further, when the puncture needle S further advances compared to FIG. 5 and the diseased part W and the puncture needle tip Y are almost in contact with each other, as shown in FIG. Is large, and the affected part W and the puncture needle tip Y are displayed on the full screen of the monitor 5a of the image display unit 5.
[0046]
However, the correspondence relationship between the recognized distance D and the enlargement ratio is basically arbitrary in the present invention. Therefore, according to the distance D between the affected part W and the puncture needle tip Y, which changes from time to time, the enlargement factor at which the tomographic image 50 is displayed depends on the distance D and the enlargement factor. The pre-adjustment or user setting value of the image adjustment means 6 relating to the correspondence is left to the user. Therefore, the display examples as shown in FIGS. 4, 5, and 6 are merely examples in the first embodiment, and for example, the affected part W and the puncture needle tip Y are only in contact with each other. However, the extreme display as shown in FIG. 6 is not necessarily performed, and it is needless to say that a certain degree of visual field regarding the surroundings may be secured.
[0047]
In general, during the operation, in a situation where the puncture needle S is “inserting” into the subject P, in other words, in a situation where the puncture needle S is “moving”, the puncture needle S is attached to the subject P. It may be more preferable for an operator or an operator to confirm how the body surface is punctured or the position of the puncture needle S in the entire tomographic image of the subject P.
[0048]
In consideration of such circumstances, it is preferable to perform the following processing. That is, when the puncture needle S is in the above-described situation (moving situation), as shown in FIG. 4, automatically, regardless of the distance D between the affected part W and the puncture needle tip Y, the subject P What is necessary is just to make it display an image with the expansion ratio and projection position which the whole tomographic image 50 appears on the monitor 5a full screen. When the movement of the puncture needle S stops, the distance D between the affected part W and the distal end Y of the puncture needle S at that time is calculated, and based on this, an appropriate enlargement ratio and projection position are obtained. Similar image display control is performed. This will contribute to more accurate puncturing work.
[0049]
Furthermore, in the first embodiment, the following processing can be performed at any time in parallel with the processing related to the distance D described above. That is, by using the voice input means 7, the operator can arbitrarily perform enlargement / reduction of the tomographic image 50 at any time. For example, in the case shown in FIG. 6, when the operator wishes to secure a slightly wider field of view and confirm the surrounding situation, the predetermined sound, “small” according to the example described above, etc. By producing sound, it is possible to reduce the magnification of the tomographic image 50 and obtain a tomographic image 50 having a slightly wider field of view as compared to FIG.
[0050]
In this case, the same argument as the distance D and the enlargement ratio described above applies to the correspondence between the utterance of “small” and the accompanying reduction degree of the enlargement ratio. That is, the “degree of reduction” is arbitrary, and how much reduction effect is brought about with respect to the enlargement ratio by uttering “small” is determined in advance by the image adjustment means 6 or a user set value. It is entangled. However, in the present invention, the voice recognition unit Q may be configured to recognize a utterance such as “30% expansion”. In this case, in this case, the tomographic image 50 is used to realize the utterance content. Also, the processing related to “30% expansion” may be performed.
[0051]
Below, 2nd embodiment of this invention is described. In the second embodiment, in the image adjusting means 6 in the first embodiment, the enlargement ratio of the tomographic image 50 and the projection positions of the affected part W and the tip Y of the puncture needle are set as the affected part W and the puncture needle tip Y. Instead of this, the function of adjusting the enlargement ratio and the projection position based on the “entry speed” of the tip Y of the puncture needle S with respect to the subject P instead of this function. It is different in that it is provided.
[0052]
By providing such a function, in the second embodiment, for example, if the entry speed of the puncture needle is high, the rate of change of the magnification rate with respect to the tomographic image 50 with respect to time varies with the progress of the puncture needle S. The enlargement rate is gradually increased so as to increase, and conversely, if the speed is low, the same change is made so that the change rate of the enlargement rate becomes small.
[0053]
Even in such a case, as in the case of the first embodiment described above, it is clear that the affected part W and the puncture needle tip Y are always placed in a monitorable state on the monitor 5a screen.
[0054]
Below, 3rd embodiment of this invention is described. In the third embodiment, the audio input means 7 is attached to the image adjustment means 6 in the first embodiment. Instead, as shown in FIG. The difference is that a means 7 'is provided.
[0055]
As described above, the input means 7 'includes various press buttons (not shown), for example, an "enlarge button", a "reducing button", or an "arrow button" that indicates the four directions, and presses these buttons. By doing so, it is possible to directly perform enlargement / reduction of the tomographic image, vertical / left / right projection position adjustment, and the like. In other words, it has a function of adjusting the magnification of the tomographic image 50 and the projection position of the affected part W and the puncture needle tip Y based on information input via the input unit 7 ′. It is clear that the affected part W and the puncture needle tip Y can always be monitored even if such means are used.
[0056]
In the present invention, the input means 7 'is not limited to the above-described form. For example, in addition to or in combination with the above-described configuration, a numeric keypad type input unit is provided, and by directly inputting a numerical adjustment value, the affected part W and the puncture needle S projected on the monitor 5a A mode of changing the position of the tip Y so as to correspond to the adjustment value can be considered, and the tomographic image 50 is enlarged using a mouse and a pointer (not shown) displayed on the monitor 5a. It is also possible to easily consider a form in which the projection position is changed.
[0057]
As described above, in any of the first, second, and third embodiments, if the X-ray CT apparatus is used, the affected area W and the distal end Y of the puncture needle S are always monitored. Since it appears on the screen 5a, the puncture operation of the puncture needle S can be performed while accurately checking the relationship between the two at any time.
[0058]
Further, according to the voice input means 7 in the first embodiment or the input means 7 ′ in the third embodiment, when the operator desires, the enlargement or reduction of the tomographic image 50 can be appropriately performed. The puncture operation can be performed while more accurately grasping the positional relationship between the affected part W and the puncture needle S.
[0059]
In the above description, the embodiment related to the present invention has been described in three parts for convenience. However, the present invention is not limited to such a form. For example, it is possible to adopt a form in which the changing function such as the enlargement ratio of the tomographic image 50 based on the “entry speed” of the puncture needle S described in the second embodiment is combined in the first embodiment. That is, with respect to the image adjusting means 6, such a change function such as an enlargement rate based on the “entry speed” and an enlargement based on the distance D between the affected part W and the puncture needle tip Y as described in the first embodiment. It may be configured to have a change function such as a rate. In such a case, for example, the degree of influence on the change in the enlargement ratio is changed by the change in the “approach speed” and the change in the distance D, and either the “approach speed” or the “distance” D is changed. It is possible to consider a configuration in which it is left up to the operator to change the enlargement ratio or the like.
[0060]
Similarly, a mode in which the voice input means 7 in the first embodiment and the input means 7 ′ in the third embodiment are combined is naturally within the scope of the present invention. In such a case, direct enlargement / reduction of the tomographic image 50 or change of the projection position in the vertical / left / right directions is appropriately performed according to the progress of the puncture operation or according to the preference of the surgeon. do it.
[0061]
Furthermore, the recognition of the distance D in the first embodiment is not automatically performed by the image recognition unit Q, but the image of the affected part W and the tip Y of the puncture needle S directly by the input means 7 ′ described above. The position D may be input to give coordinate values, the distance D may be obtained based on these values, and the enlargement ratio and projection position may be further adjusted therefrom.
[0062]
【The invention's effect】
As described above, according to the radiological diagnostic apparatus of the present invention, the tomographic image magnification and the projection position on the screen from the start of puncture of the puncture needle to the subject to the arrival of the target site in the subject are By adjusting according to the distance between the needle and the target site and / or according to the approach speed of the puncture needle to the subject, the puncture needle and the target site always appear on the screen. Therefore, an operator or an operator can accurately confirm the positional relationship between the puncture needle and the target site, and can perform the puncture operation more accurately.
[Brief description of the drawings]
FIG. 1 is a schematic diagram showing a configuration example of an X-ray CT apparatus according to an embodiment of the present invention.
FIG. 2 is a block diagram showing a configuration example of an X-ray CT apparatus according to the first embodiment of the present invention.
FIG. 3 is an explanatory diagram showing a display example of a tomographic image screen in the X-ray CT apparatus shown in FIG. 1;
4 is an explanatory diagram showing a tomographic image display example at the start of puncture of a subject with a puncture needle in the X-ray CT apparatus shown in FIG. 1; FIG.
FIG. 5 is an explanatory diagram showing a tomographic image display example in a state in which the puncture needle enters the subject one step further than FIG. 4;
FIG. 6 is an explanatory view showing a tomographic image display example in a state where the entry of the puncture needle into the subject is further advanced as compared with FIG. 5, and the tip of the puncture needle and the affected part are almost in contact with each other.
FIG. 7 is a block diagram showing a configuration example of an X-ray CT apparatus according to a second embodiment of the present invention.
FIG. 8 is an explanatory view showing a state of a tomographic image screen with a fixed size in a conventional X-ray CT apparatus, and as a result of copying the entire tomographic image, the positional relationship between the tip of the puncture needle and the affected part can be grasped. It is a figure which shows a difficult situation.
FIG. 9 is an explanatory diagram showing a state of a tomographic image screen with a fixed size in a conventional X-ray CT apparatus, and as a result of enlarging the tomographic image, grasping the puncture start position of the puncture needle with respect to the subject It is a figure which shows a difficult situation.
[Explanation of symbols]
1 X-ray tube (radiation source)
1a X-ray generator
2 X-ray detector (radiation detector)
3 Top plate
4 Image processing section
Q Image recognition unit
5 Image display section
6 Image adjustment means
7 Voice input means
7a microphone
7b Voice recognition device
7 'input means
50 Tomographic image
C Central control unit
P subject
S puncture needle
Y puncture needle tip
W affected area

Claims (3)

In the radiation diagnostic apparatus for reconstructing a tomographic image relating to the subject based on the result of detection of radiation emitted from the radiation source by the radiation detector via the subject,
When monitoring the operation of puncturing a puncture needle with respect to a predetermined target site in the subject using a screen on which the tomographic image is displayed,
During the work, and an image recognition unit for obtaining the coordinate values on the previous SL tomogram of the tip portion of the predetermined target site and the puncture needle,
Based on the coordinate values of the tip of the puncture needle and the target site, the distance between the tip of the puncture needle and the target site on the tomographic image is obtained, and based on the distance, the enlargement ratio of the tomographic image In addition, by adjusting the projection position of the distal end portion of the puncture needle and the target portion on the screen, the image that keeps the distal end portion of the puncture needle and the target portion in a state that can always be monitored on the screen. A radiation diagnostic apparatus comprising an adjusting means. In the radiation diagnostic apparatus for reconstructing a tomographic image relating to the subject based on the result of detection of radiation emitted from the radiation source by the radiation detector via the subject,
When monitoring the operation of puncturing a puncture needle with respect to a predetermined target site in the subject using a screen on which the tomographic image is displayed,
During the work, an image recognition unit for obtaining a coordinate value on the tomographic image of the predetermined target site and the tip of the puncture needle;
Based on the coordinate value of the tip of the puncture needle, the approach speed of the tip of the puncture needle to the subject is obtained, and based on the approach speed, the magnification of the tomographic image, the tip of the puncture needle, and Image adjustment means is provided for adjusting the projection position of the target part on the screen so that the tip of the puncture needle and the target part are always monitored on the screen. A radiation diagnostic apparatus characterized by the above. The image adjusting means includes
Based on the speech the operator issues to hold a ceremony the working, radiation diagnostic apparatus according to claim 1 or 2, characterized in that adjusting the magnification and the projection position.

Images