JP2002062357A - Nuclear medicine diagnostic equipment - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a nuclear medicine diagnostic equipment, having a thin and light-weight camera head which can be used, while being freely passed around in an operating room with attaining a practically full performance, such as resolution or the like. SOLUTION: The nuclear medicine diagnostic equipment is provided with a supporting stand 100 for supporting a radiation detecting part 1, so that a detection face of a semiconductor detecting element constituting the radiation detecting part 1 can be directed in any direction. The apparatus can be set (passed around) freely to a body P to be inspected. In this case, the detecting element and a collimator aperture are preferably held in a one-to-one correspondence or a one-to-an arbitrary integral value correspondence. Besides, the free passing is enabled by a form in which the radiation detecting part 1 and an image display part are constructed into a single body, a form in which the radiation detecting part is of a size which enables operator's hand to hold, etc.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a nuclear medicine diagnostic apparatus.

[0002]

2. Description of the Related Art Conventionally, radioisotopes (hereinafter referred to as "R
(I may be abbreviated as `` I '') is administered into the subject, and the distribution of the RI in the subject is imaged based on the result of detecting and measuring gamma rays emitted from the RI. A nuclear medicine diagnostic apparatus is provided. In particular, as a device or means for capturing the image as a three-dimensional distribution image (tomographic image), SPECT (Sing
le Photon Emission Computed Tomography) device is widely known. With such an image, the user or the operator can check the inside of the subject without using any surgical means.

Incidentally, in the above nuclear medicine diagnostic apparatus, it is essential to mount a "radiation detecting section" in order to detect and measure the gamma ray. The radiation detecting section basically has a function of receiving the incidence of a gamma ray and converting it into an (easy-to-handle) electrical signal while reflecting the incidence position and energy.

Conventionally, as such, a collimator,
A so-called “Anger type” (or scintillation camera) having a configuration mainly including a scintillator (for example, composed of a NaI crystal) and a photomultiplier tube (Photo Multiplier Tube; PMT) is widely used. Was. According to this, a gamma ray incident via a collimator is converted into an optical signal by a scintillator, and this optical signal is converted into an electric signal by a photomultiplier.
In the scintillator, the incident position and the energy of the gamma ray are known, and the electric signal reflects such information. Therefore, if this electric signal is collected as projection data and reconstructed, a tomographic image or the like of the subject can be obtained.

[0005] The collimator in the radiation detecting section has, as is well known, a structure having a plurality of openings formed by partition walls made of lead or the like. The incidence of gamma rays on the scintillator will be limited to some extent by these openings.

On the other hand, separately from the above-mentioned radiation detecting section, the incidence of gamma rays causes generation of electric charge (that is, generation of an electric signal).
A radiation detector called a “semiconductor detector”, which has a configuration in which a plurality of semiconductor detection elements contributing to the above are arranged, for example, two-dimensionally (in a matrix) and discretely, has already been proposed. Incidentally, even in the radiation detecting section using such a semiconductor detecting element, the above-described collimator is still used because the arrival direction of the gamma ray is limited to a certain extent.

[0007]

However, in the above-mentioned radiation detecting section, a thin and lightweight camera head which can be used in an operating room while achieving performances such as practically sufficient resolution is provided. There was a problem that it could not be realized. That is, in the so-called Anger type, as described above, it is necessary to provide a photomultiplier tube, a light guide for connecting the photomultiplier tube to the scintillator, and the like. I have to be done. Accordingly, a relatively large “mount” has also been required as a mechanism for holding such an anger-type camera head. further,
In general, the Anger type has a problem in that the spatial resolution is not sufficient and it is not suitable for performing observation of an anatomically small portion in a small visual field expected during operation.

In this regard, the above-described semiconductor detector can alleviate some of the drawbacks (especially, the size increase) of the Anger type described above. However, even if a thin and lightweight camera head is realized by the semiconductor detector, the following problems will occur. That is, the above-mentioned “use during surgery” is preferably scheduled to be used while freely moving the camera head. However, according to such a method of use, since it is generally assumed that the installation state of the camera head is in an arbitrary direction with respect to the subject, the positional relationship between the obtained image and the subject is accurately determined. Loses sight of what it looks like. In this case, there is a possibility that judgment and diagnosis during the operation may be confused.

In addition, according to the semiconductor detector, the problem of the above-mentioned collimator which is greatly involved in the above-mentioned "achieving performance such as sufficient resolution for practical use" is pointed out. That is, according to the conventional collimator, no special consideration is given to the positional relationship between the semiconductor detection element and the collimator. As shown in FIG. Element 120 may be present. In this case, the spatial sensitivity response is widened, and the center direction of the sensitivity is blurred right and left in the figure. That is, the acquired image contains blur.

In order to cope with such a problem, in order to narrow the spatial response, for example, as shown in FIG.
When the collimator 111 is configured, the total spatial resolution can be recovered, but the sensitivity (collimator efficiency) is reduced. Especially in such a case,
The problem is that the intention to provide a thin and lightweight camera head is hindered by the increase in the thickness of the collimator 111. This is even more evident in view of the fact that the collimator is made of lead or the like, and in the configuration shown in FIG. 23, it is difficult to use it "around" intraoperatively.

[0011] Incidentally, as a method for detecting a gamma ray and observing a small area of a subject even during surgery, a conventional technique disclosed in Japanese Patent Application Laid-Open No. 6-258440 has been disclosed. A position specifying device has been proposed. This is, as shown in FIG. 24, one detector 92 that measures the amount of radiation transmitted through the window 91.
Is attached to the tip of the rod-shaped probe 90, and may be more generally referred to as a “single detector probe”. The detection "surface" 92a relating to the one detector 92 is disposed on the distal end surface of the rod-shaped probe or on a side surface near the distal end (the side surface in the figure).

However, with such a single-detector probe, when it takes a long time to search for an affected part or when there are a plurality of metastatic sites when observing the distribution of cancer cells, some of them are missed. There was danger.

[0013] Further, utilizing the single detector probe,
Conventionally, when a surgical operation is performed by specifying a portion to be resected such as a cancer or tumor, the location of the cancer or tumor is surely removed because there is some indefiniteness in the location. Therefore, surgery to remove a relatively large area (including normal tissue) including the area where the cancer / tumor or the like is present has been performed. However, such an operation has a significant effect on the quality of life (QOL) of the subject after the operation. For example, in the case of breast cancer or the like, the patient generally wants to leave the breast as much as possible, and such a surgery cannot meet such a demand.

The present invention has been made in view of the above circumstances, and an object of the present invention is to achieve a practically sufficient performance such as resolution and the like so that it can be used while freely moving around in an operating room. It is an object of the present invention to provide a nuclear medicine diagnostic apparatus provided with a thin and lightweight camera head.

[0015]

The present invention employs the following means in order to solve the above problems.

That is, in the nuclear medicine diagnostic apparatus according to the first aspect, a radiation detecting means in which a plurality of semiconductor detecting elements are arranged in parallel, and an incident state of radiation emitted from the inside of the subject to the semiconductor detecting elements is determined by an opening. In a nuclear medicine diagnostic apparatus, comprising: a collimator localized by a semiconductor detector; and an image display unit configured to display an image related to the subject created based on a signal output from the semiconductor detection element. It is characterized by comprising a support means for supporting the radiation detection means so that the radiation detection means can be directed in an arbitrary direction.

Particularly, a marking is formed on a predetermined portion of the radiation detecting means, and a mark corresponding to the position where the marking is formed is displayed on the image display means together with the display of the image. (Chart 7).

The nuclear medicine diagnostic apparatus according to claim 9 is
In the apparatus having the same prerequisite configuration as in the above-mentioned claim 1, the radiation detection means and the image display means are integrally formed.

In the case of the integral, the detection surface of the semiconductor detection element constituting the radiation detection means and the image display surface of the image display means may face each other or back to back. In other words, in other words, when the normal of the detection surface and the normal of the image display surface intersect (Claim 12), if a sample such as an organ is placed on the detection surface, the sample In the latter case, when the detection surface is applied to the subject, an image of the “as is” can be confirmed.

According to a fourteenth aspect of the present invention, in order to realize both of the above aspects, the radiation detecting means and the image displaying means are integrally formed by a rotatable connection. is there.

According to a fifteenth aspect of the present invention, in the nuclear medicine diagnostic apparatus having the same prerequisite configuration as in the first aspect, the size of the radiation detecting means may be held by a user of the apparatus. It is characterized by being configured as possible.

In addition, in the nuclear medicine diagnostic apparatus according to claim 17 or 18, each of the semiconductor detecting elements has a one-to-one correspondence with each of the openings of the collimator or a one-to-one correspondence with an arbitrary integer value. It is characterized by having.

Finally, the nuclear medicine diagnostic apparatus according to the nineteenth aspect is characterized in that the radiation detecting means is provided with an image blur removing means for correcting the blur of the image on the image display means. It is.

[0024]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS A first embodiment of the present invention will be described below with reference to the drawings. FIG. 1 is a schematic diagram illustrating a configuration example of the nuclear medicine diagnostic apparatus according to the first embodiment. In FIG. 1, the nuclear medicine diagnostic apparatus includes a radiation detection unit (radiation detection means) 1, a data collection unit 2, a memory 3, an image creation unit 4, an image display unit 5, a control unit 6, and the like.

The radiation detector 1 has a flat plate-like appearance as a whole, and has a two-dimensionally formed collimator 11 and a plurality of semiconductor detectors 12 (discretely arranged in a matrix). Hereinafter, referred to as "detection element")
It is composed of

The collimator 11 is made of a material (for example, lead or the like) capable of shielding gamma rays, and has a form having an opening 11b divided into a plurality of parts by partition walls 11a. The gamma ray emitted from the radioisotope administered to the subject P is limited in its incident mode by the opening 11b, and only the gamma ray passing through the opening 11b reaches the downstream detection element 12.

The detecting element 12 receives the gamma ray arriving via the collimator 11 and directly converts the gamma ray into an electric signal. This electric signal indicates at which position in the radiation detecting section 1 the gamma ray from which the gamma ray originated is detected or counted (in other words,
This information includes position information and count value information (or energy information) representing each of "which" detection element 12 is detected) and what energy the gamma ray has. The detection element 1
2 directly outputs count value information. The above-mentioned position information is calculated based on the output count value information in a position information calculation unit (not shown) attached to the data collection unit 2 described later.

More specifically, as the detection element 12, for example, a compound semiconductor cadmium telluride (CdT
e) etc. can be used. In the present invention, as the detection element 12, the compound semiconductor CdZnT
e may be used, and a material other than the compound semiconductor may be used as the detection element 12 more widely. An electrode is attached to the detection element 12 for extracting the electric signal. The detection element 12 has, for example, a Schottky structure made of platinum and indium. The platinum side is used for a high voltage application electrode, and the indium side is used for signal extraction. Electrodes, etc. Further, an insulating mylar sheet or the like is provided between the plurality of detection elements 12. In addition, each of these detecting elements 12 is provided with a charge amplifier and a waveform shaper, and the above-mentioned electric signal (or the positional information as to which signal of the detecting element 12) passes through them. Output.

According to the radiation detector 1, unlike the Anger type gamma camera (scintillation camera) described in the section of the related art, it is possible to obtain an electric signal directly from a gamma ray. In particular, the fact that the formation of the detection element 12 can be easily reduced in size (that is, it can be highly integrated), and from this, its intrinsic resolution, that is, the so-called “intrinsic (i)
It is possible to enjoy advantages such as increasing the “ntrinsic) resolution”.

The data collecting section 2 receives the electric signal output from the radiation detecting section 1 and collects it as gamma ray data, and the memory 3 stores the collected gamma ray data. The data collection unit 2 includes a circuit for amplifying a signal from the detection element 12, an A / D conversion circuit, and a predetermined condition (for example, “an energy window in which a signal from the detection element 12 is set”. Other circuits such as a circuit for collecting data only for signals that satisfy the condition of “existing in
Further, it is possible to assume that the memory 3 has the same number of addresses as the number of the detection elements 12, for example. That is, the detection element 12 and the address have a one-to-one correspondence, and the gamma ray detection in one detection element 12 is as follows.
It will be stored on the corresponding address.

The image creating section 4 creates a planar image of the subject P or reconstructs a tomographic image based on the collected gamma ray data, and the image display section 5 creates or reconstructs a tomographic image. The displayed planar image or tomographic image is displayed. In addition, the term “image” in the present invention means both a planar image and a tomographic image unless otherwise specified.

The control unit 6 plays a role of harmoniously controlling the operation of the radiation detection unit 1, the data collection unit 2, the image creation unit 4, the image display unit 5 and the entire operation of the nuclear medicine diagnostic apparatus in the first embodiment. Carry. Further, the user of the device can issue a direct command or the like to the control unit 6 via the dialogue unit 7, and thereby can operate each of the above components.

In addition to the input of the above-mentioned commands and the like, the dialog section 7 generally exerts an action corresponding to a man-machine interface between the apparatus and the user of the apparatus. Further, as a specific form of the control unit 6, for example, a personal computer or the like may be adopted. In this case, the central processing unit (CPU) of the personal computer is used for the control unit 6, the keyboard or mouse and various displays are used for the interactive unit 7, the various displays are used for the image display unit 5, and so on. It is possible to consider this.

The radiation detector 1 in the first embodiment is characterized in that it has the following configuration.

The first is a mechanism for supporting the radiation detecting section 1 as conceptually shown in FIG. That is, the radiation detection unit 1 is configured to be supported by the support stand 100 at one point (support point) on the outer edge.
In FIG. 2, the support stand 100 includes a base 101 that can be placed beside the subject P and other appropriate places, and a support column 102 that is vertically held by the base 101.
The support pillar 102 is provided with a joint 103 that can be rotated in parallel with the axial direction of the support pillar 102 and about the axis to change its position. 104 are connected. The arm unit 104 includes a first arm 104a, a second arm 104b
And a flexible joint 104c for rotatably connecting these arms 104a and 104b.

As is apparent from such a configuration, the radiation detecting section 1 in the first embodiment can turn its detection surface in an arbitrary direction, or can freely move its position with respect to the subject P. It is possible to change to In particular, since the collimator 11 is made of lead or the like,
Considering that the weight of the radiation detection unit 1 is appropriate, the operation and effect of the support stand 100 are clear.

The supply of control signals and power from the control unit 6 to the radiation detection unit 1 supported by the support stand 100 is performed by the support columns 102 and the arm units 104 constituting the support stand 100. And the like, a signal line or a power supply line may be provided inside.

The components other than the radiation detecting unit 1 and the support stand 100, that is, the data collecting unit 2, the memory 3, the image creating unit 4, the image displaying unit 5, the control unit 6, the dialogue unit 7, etc. As shown in FIG. 2, separately from the unit 1 and the support stand 100, the processing apparatus 20 is integrally formed.

Next, as a second feature, the radiation detector 1
Is to form a marking M as shown in FIG. Specifically, the marking M may be formed by other various methods such as sticking a seal or applying a relief. In addition, an arbitrary position of the radiation detection unit 1 may be basically selected as the formation position. However, in general, FIG.
As shown in the figure, a place where the symmetry of the radiation detection unit 1 is removed,
More specifically, it is preferably formed near the corner.

On the other hand, in the image display section 5, a mark display M 'corresponding to the position of the marking M formed on the radiation detection section 1 just described is made. This is superimposed and displayed together with the above-mentioned planar image and the like.

With such a configuration, the user of the apparatus merely checks the image including the mark display M 'displayed on the image display section 5, and the planar image or the like reflects any position inside the subject. Can be easily determined.

If the point at which the support stand 100 supports the radiation detecting section 1 (support point), that is, the mounting position of the arm section 104 with respect to the detecting section 1 is out of the symmetry of the radiation detecting section 1, , Radiation detector 1
The possibility of erroneous determination regarding the overall orientation is reduced, and the above effect can be enjoyed more reliably.

In some cases, the mounting position of the radiation detecting section 1 and the arm section 104 (the above-mentioned support point) is also indicated by the corresponding mounting position mark and the like together with the planar image on the image display section 5. It is good also as a structure which superimposes and displays. Further, instead of displaying the “attachment position mark”, a portion corresponding to the support point may simply correspond to a predetermined location on the image display unit 5, for example, always at the top of the screen. Good. In such a case, the position of the support point can be specified, for example, by arranging the support stand 100 so that the support point is located between the apparatus user or the operator and the subject P. Fixed. By the way, in the above case, the arm unit 10 with respect to the radiation detection unit 1
It is preferable that the attachment position of 4 is a “corner” of the radiation detection unit 1 as shown in FIG.

The third feature is that the collimator 11 constituting the radiation detecting section 1 or its opening 11
b and the arrangement relationship between the detection elements 12. That is, in the first embodiment, as shown in FIG. 3, the arrangement relationship is such that the pitch of the detection element 12 and the pitch of the partition wall 11a of the collimator 11 are equal, that is, the opening 11b of the collimator 11 and the detection element 12 Satisfies the relationship such that they correspond one-to-one.

According to such a configuration, the partition 11a is
The direction of the sensitivity center of each of the detection elements 12 is located at the boundary between the adjacent detection elements 12 (because the partition wall 11a is not located “above” the detection elements 12). And always facing. In addition, one detecting element 12 does not have sensitivity to the two collimator openings 11b, and there is no detecting element 12 whose center of sensitivity is in an oblique direction. For this reason, in the radiation detection unit 1 according to the first embodiment, the above-described characteristic of high integration or high intrinsic resolution, which is generally expected in a semiconductor detector, is reliably utilized, and the spatial resolution is improved. improves.

Although only the X direction is shown in FIG. 2, the Z direction may be configured to have the same arrangement relationship as the X direction. A configuration may be adopted. Furthermore, the arrangement of the detection elements 12 may be different between the X direction and the Z direction. In this case, the arrangement relationship between the detection element 12 and the collimator 11 will naturally differ between the X direction and the Z direction. In any case, the present invention is not particularly limited in these respects, but it is preferable that the relationship shown in FIG. 3 is satisfied in at least one direction.

The operation and effect of the nuclear medicine diagnostic apparatus having the above configuration will be described below. In the following description,
In surgical operation (breast conserving therapy) to remove breast cancer while trying to preserve the shape of the breast as much as possible,
A specific example in which the nuclear medicine diagnostic apparatus is used will be described. In addition, the "apparatus user" used above,
It should be recognized that the term “operator” used hereinafter is a synonymous term (the term “user of the apparatus” is also used in the following).

First, a drug containing RI is administered to the subject P in advance. Thereby, the radiation detector 1 detects a gamma ray generated from the RI inside the subject P, converts the gamma ray into an electric signal, and outputs the electric signal.
Sent to Then, gamma ray data sequentially transmitted to the data collection unit 2 is sequentially stored in the memory 3.

The storage operation from the data collection unit 2 to the memory 3 is based on the assumption that each detection element 12 is given a number i, and the signal generated from the detection element 12 is
i, if information to be stored in the memory 3 is Mi, M
The operation is such that i = Di or Mi = a · Di. Thereafter, the image creating unit 4 forms an image based on the data Mi thus obtained, and displays the formed image on the image display unit 5.

The data collection and storage thereof are performed based on preset collection conditions such as one or more energy ranges (or energy windows) necessary for imaging, a gamma ray collection time or a collection count, and the like. Done. Further, the end of the collection may be instructed when a predetermined time elapses after the start of the collection is instructed without setting “in advance”. This also applies to the case where the user wants to “end” the collection before the preset collection count is reached. Further, when data collection is currently being performed, if a command to start collection is given again, it is convenient to have a configuration in which data collection is restarted from the beginning.

As a somewhat advanced function, a predetermined command is issued based on gamma ray data that has already been collected, or when an image is to be displayed again after the image has been displayed (for example, dialogue). By pressing a “readout button” (not shown) of the unit 7 or the like, a function capable of redisplaying the image can be mounted.
In addition, in the display during gamma ray data collection, it is possible to select the function of switching the image based on the preset short time acquisition and the previous image (persistent mode) and the function of displaying the accumulated image. It is good also as a structure which is as follows.

It goes without saying that the various settings or commands described above or the manifestation of various functions can be set or commanded by the apparatus user via the dialogue unit 7.

Now, while making these settings or commands,
In the current example of trying to remove breast cancer, one has to look for "Sentinel lymph nodes" in the breast, relying on the RI label (the image displayed based on it). These sentinel lymph nodes play a crucial role in cancer cell metastasis. Since such a matter is not directly related to the technical idea of the present invention, the sentinel lymph node is a path for cancer cell metastasis. It only needs to be recognized to the extent that the organization is a target organization.

In any case, in order to find the sentinel lymph node, the position of the radiation detection unit 1 must be changed freely around the subject P or around the breast. Here, the significance of the radiation detection unit 1 in the first embodiment becomes clear. That is, the radiation detection unit 1 is supported by the support stand 100, and particularly the joint 103 and the first arm 104 a and the second arm 104.
This is because the position can be freely changed by the flexible joint 104c between b (see FIG. 2).
The nuclear medicine diagnostic apparatus according to the first embodiment can also promptly display an image according to the radiation detection unit 1 whose position is freely changed as described above. Therefore, the operator can easily execute the search for the sentry lymph node.

Needless to say, the above-mentioned effect that the radiation detector 1 can be freely arranged is largely due to the fact that the radiation detector 1, the support stand 100, and the processing device 20 are configured separately. No. Further, according to such a separate structure, the processing device 2
0 can be enjoyed at the same time in that the heat generated by the control unit 6 and the like constituting 0 does not adversely affect the image on the detection element 12 and the image display unit 5 constituting the radiation detection unit 1. become.

Further, in such a search for the sentinel lymph node, the operator may be confused about the recognition of the position of the subject P on the image displayed on the image display unit 5. There is nothing. This is the radiation detector 1
The mark M is formed on the mark M and the mark M 'is displayed correspondingly. Therefore, the surgeon can accurately grasp the positional relationship between the visualized RI distribution image and the actual affected part of the subject P. This means that it is possible to accurately and promptly determine a specimen extraction, a pathological examination, and a determination of an extraction range determined based on the result, which are scheduled later. That is, according to the nuclear medicine diagnostic apparatus of the first embodiment, the purpose of the breast “conserving” therapy is achieved without any limitation.

It is to be noted that, as described above, the above-described accurate recognition is possible because the detection elements 12 and the addresses (or maps) on the memory 3 have a one-to-one correspondence, and the radiation detector 1 And the address (or map) of the memory 3 (that is, a part of the image corresponding to the address) can be uniquely determined.

However, in order that this “unique” relationship can be determined, the detection element 12 and the address (or map) do not necessarily have to have a one-to-one correspondence. In fact, such a device configuration (for example, the detection element 12
It is known that the address (or the map) of the memory 3 is smaller than the number of). In this case, an appropriate interpolation process is performed on the memory 3 or in the data collection unit 2 at the subsequent stage. Will be. Even in such a case, the detection element 12 and the address (or map) on the memory 3 are still in a fixed relationship, and thus both are also in a "uniquely" determinable relationship. It may be. That is, even in such a case, it is possible to display the mark display M ′ corresponding to the marking M.

Further, in the first embodiment, the spatial resolution and sensitivity (if necessary) are obtained by adopting a configuration as shown in FIG. 3 with respect to the positional relationship between (the opening 11b of) the collimator 11 and the detecting element 12. , The quality of the image).

In the above description, the arrangement relationship between the collimator 11 (the opening 11b thereof) and the detection element 12 has been described with a specific configuration as shown in FIG. It is not limited to such a form.

By the way, in connection with what has just been described,
Usually, many types of collimators to be used are prepared depending on the application (of course, it may be fixed that only one type of collimator is used).

For example, when it is desired to obtain an image having a higher spatial resolution, usually (especially in the case of a scintillation camera), the pitch of the partition walls 11a of the collimator 11 is reduced. However, in the first embodiment, even in such a case, the detection element 1
It is preferable to maintain the one-to-one synchronization relationship between the collimator 11 and the collimator 11 as shown in FIG.

Therefore, in such a case,
As shown in FIG. 4, the “thickness” is large (see FIG. 3,
It is better to use a collimator 11 '. However, in this case, the “thickness” of the entire radiation detection unit 1 increases, and accordingly, the weight thereof increases accordingly.
There are some problems. That is, in view of the fact that the gist of the present invention intends to provide a thin and lightweight radiation detection unit that can be easily handled, it cannot be said that this is a positively preferable method.

As another example having such a problem, for example, as shown in FIG.
For economic reasons, such as suppressing the cost of manufacturing, there is a case where it is desired to adopt a material having a large size. In such a case, if the same spatial resolution and sensitivity as those shown in FIG. 3 are to be maintained, the form of the collimator 11 ″ is changed as shown in FIG. 5 according to the size of the detection element 12 ′. Large dimensions. By doing so, one detection element 12 '
The radiation acceptance angle (indicated by θ in FIG. 5) is equivalent when comparing FIG. 3 with FIG. 5, so that it is possible to certainly maintain sensitivity and the like.
The intention to provide a thin and lightweight radiation detection unit that can be easily handled is hindered.

Regarding these problems, first,
If proper consideration is given to the strength and the like of the support stand 100, the problem can be solved. It is also effective to use the following means as another more aggressive solution. That is, in the case of using a detection element 12 ′ having a large size as shown in FIG. 5, it is preferable that a plurality of partition walls 11 Pa of the collimator 11 P are arranged for one of the detection elements 12. For example, in FIG. 6, the partition 11Pa is arranged such that two openings 11Pb correspond to one of the detection elements 12. In this case, the acceptance angle θ becomes equal to that shown in FIG. 3, so that the spatial resolution and sensitivity of the collimator 11P can maintain the same performance as that shown in FIG. 3 and can be a thin collimator.

In the present invention, the relationship as shown in FIG. 6, that is, the relationship between the detection element 12 and the opening 11Pb is not limited to a one-to-two relationship. ". In such a case, one detection element 12 is covered by the openings 11Pb of the plurality of collimators 11P. However, the total sensitivity direction of the detection elements 12 is common to all the detection elements 12 and the front direction is the same. There is no problem because it is against.

By the way, contrary to the case shown in FIG. 4, the synchronous collimator in the case where the sensitivity is given priority over the spatial resolution has a small "thickness"("thin") as shown in FIG. What is necessary is just to use the collimator 11 ''''. It is clear that this problem does not occur.

Hereinafter, a specific example in which the nuclear medicine diagnostic apparatus having the above configuration example is used in an operation other than the above-mentioned “breast conserving therapy” will be described. This relates to the case where the nuclear medicine diagnostic apparatus according to the first embodiment is used when measuring the blood flow in the affected area of the subject P in the operating room.

In such a case, for example, the following procedure may be used. First, a certain nuclide A is administered to the subject P in advance, and the accumulation state of the nuclide A is imaged. On the left side of FIG. 8, the region of interest (Region of
An example in which two interests (ROIs) are set is shown.

Next, another nuclide B (having different energy from nuclide A) is administered, and the distribution state of the nuclide B is imaged for each time. Incidentally, since the energy resolution of the detection element 12 (semiconductor detection element) as in the first embodiment is excellent, it is easy to discriminate the nuclide B from the nuclide A. On the right side of FIG. 8, an example is shown in which the distribution state of nuclide B is plotted at each time t. Note that this plot may be performed in real time. As described above, the blood flow state of the ROI can be determined.

Even in such a case, in the nuclear medicine diagnostic apparatus according to the first embodiment, the significance that the radiation detector 1 can be freely operated and the image reflects any part of the subject P The non-confusing significance of the determination of whether or not it is the case is clearly recognizable, given that the blood flow measurement is also performed "in operation", similar to the "breast conserving therapy" described above. .

Apart from the above-mentioned method, the administration of nuclide A is omitted, and the distribution of nuclide B at each time is simply imaged.
ROI from those images or from their total image
May be designated, and the image value of the ROI may be plotted for each time.

Hereinafter, a modified example of the first embodiment will be described. In this modification, the joint 103 and the flexible joint
4c is characterized in that a rotation angle sensor (not shown) is provided. If this rotation angle sensor is used, the identification of which part of the subject P the image on the image display unit 5 reflects can be more reliable.

That is, when the joint 103 and the flexible joint 104c are in an arbitrary state, the apparatus user inputs an arbitrary reference axis direction via the dialogue unit 7. That is, the user of the apparatus can determine information such as which direction the reference axis direction is with respect to the base 101 or which direction the image is in the image,
In other words, the reference axis direction at this time or in the initial state is
Make settings for what it looks like. FIG. 9 illustrates a case where the body axis direction (Z-axis direction) of the subject P corresponds to the direction of the reference axis BA.

After the above setting, no matter how the radiation detector 1 is moved thereafter, the reference axis B according to the setting is obtained from the position information output from the rotation angle sensor.
It is possible to know how much the direction of A is shifted with respect to the image, and it is possible to superimpose and display the image BA ′ of the “shifted” reference axis on the image display unit 5.

As is apparent from the above, according to such a configuration, it is possible to more easily determine what part of the subject P reflects the image currently displayed on the image display unit 5. It can be accurately identified. Also, according to this, by utilizing the fact that the image BA ′ of the reference axis is displayed, the right side and the left side of the subject P are distinguished by “R” and “R” on the image of the image display unit 5. By superimposing and displaying “L” or the like, the accurate identification can be further ensured.

In the first embodiment, the arm section 104 includes the first arm 104a and the second arm 10a.
4b, but the present invention
It is not limited to such a form. That is,
In general, the arm section 104 may be configured by a plurality of arms and a flexible joint that rotatably connects each of the plurality of arms.

Hereinafter, a second embodiment of the present invention will be described. The second embodiment is characterized in that, as shown in FIG. 10, the configuration corresponding to the above-described radiation detection unit 1 and image display unit 5 is integrally configured. Hereinafter, an integrated configuration of the radiation detection unit and the image display unit will be referred to as a direct monitor unit 15.

As the image display section 51 in such a direct monitor section 15, it is desirable to use a thin and low heat generation apparatus such as a liquid crystal display.
Further, components other than the integrated radiation detection unit 1 and image display unit 51, namely, the data collection unit 2, the memory 3,
The image creating unit 4, the control unit 6, the dialogue unit 7, and the like are constructed as a processing device 21 as shown in FIG. 10 in a part different from the direct monitor unit 15, similarly to the processing device 20 of the first embodiment. It is supposed to be.

According to such a configuration, the radiation detection unit 1 (the detection surface of the detection element 12) of the direct monitor unit 15 is simply applied to the subject P, and the image display unit 51 located on the back surface thereof is Since the image of “appropriate” is displayed, the diagnosis of the subject P by the operator is
Obviously, it will be better implemented.

Therefore, in such a case, the marking M and the mark display M 'on the image display section 5 as described in the first embodiment are not necessarily required. This is because according to the second embodiment, it is no longer possible for the operator to be confused about which part of the subject P reflects the displayed image. .

Further, in the second embodiment, since the processing unit 21 including the direct monitor unit 15 and the control unit 6 is a separate component, the radiation The detection element 12 and the image on the image display unit 51 constituting the detection unit 1 are not adversely affected by the heat generated by the control unit 6 and the like.

Considering that the functions of the control unit 6, the data collection unit 2, the image creation unit 4 and the like constituting the processing unit 21 can be expected to be realized by a personal computer in substantially the same manner, As 21, a configuration that employs the personal computer may be adopted. In this case, an image similar to that of the image display unit 51 may be displayed on a display or the like attached to the personal computer.

Further, the arrangement of the dialogue unit 7 may be any of a form provided alongside the direct monitor unit 15 or a form provided on the processing device 21. In the case where the former form is adopted, the image display unit 51 constituting the direct monitor unit 15 is replaced with a known L.
The CD touch panel system may be used so that the operator can issue various instructions by touching various icons and the like on the dialogue screen displayed on the screen with the finger (the image display unit 51 and the image display unit 51). Dual-purpose form of the dialogue unit 7).

In addition to the dual use of the image display unit 51 and the dialogue unit 7, the dialogue unit 7 may be provided separately from the processing device 21 and the direct monitor unit 15. Since such forms are related to a modification of the third embodiment of the present invention described below, they will be described again in detail.

Hereinafter, a third embodiment of the present invention will be described. The third embodiment relates to a modification of the nuclear medicine diagnostic apparatus in the first embodiment. That is, in the first embodiment, the radiation detection unit 1 is held by the support stand 100, which allows free operation. Instead, in the third embodiment, the radiation detection unit 1 Is characterized in that it can be grasped, or that it can be handled by the operator "by hand". In the following, the remaining control unit 6
The detailed description of the same components as those of the first embodiment and the second embodiment is omitted.

FIGS. 11 and 12 show a configuration example of a nuclear medicine diagnostic apparatus according to the third embodiment. In these drawings, the outer shape of the radiation detecting section 1 ′ is substantially square (FIG. 11A) or substantially circular (FIG. 11A).
(B)). Then, a gamma ray detection surface (gamma ray incidence surface) 1 in such a radiation detector 1 '.
The shape of 'a is also substantially square or substantially circular as shown in FIG. 12 (a) or (b).

The specific size is now shown in FIG.
And a substantially square radiation detecting unit 1 shown in FIG.
As an example, it is assumed that one of the detection elements 12 including the electrode having the above-described Schottky structure has, for example, 1.35 mm × 1.35 mm × 5 mm. Further, as for the detection surface, for example, it is assumed that 32 detection elements 12 are arranged and fixed vertically and horizontally, and the size (the size of the effective visual field) is determined by including the insulating sheet between the detection elements 12 described above.
For example, 50.8 mm × 50.8 mm.

Further, the size of the housing 1'b surrounding the radiation detecting section 1 shown in FIG. 13 is, for example, 60 mm × 60 mm × 10 mm. In addition,
On one surface of the housing 1'b, the detection surface is installed so as to be in a parallel relationship with the detection surface. An ASIC (Application Specif.) Is provided in the internal space of the housing 1'b.
ic IC; houses a circuit unit that has been made into an application specific IC. The power supply / signal cable is connected to the housing 1'b.
Pull out from the side.

According to such a configuration, the surgeon can carry out a diagnosis by a technique such as introducing the radiation detecting section 1 'into the abdominal cavity of the subject P while holding the radiation detecting section 1' in the palm. Thus, more agile handling or diagnosis becomes possible.

Although the thickness of the radiation detecting section 1 'is set to "5 mm" according to the above-described example, the thickness can be appropriately adjusted according to the band of the gamma ray energy to be detected.
For example, as a tentative reference, it is preferable that the thickness be 5 mm or less if the gamma ray energy mainly used is 140 keV, and 5 mm or more if it is more than that.

In the case where the radiation detecting section 1 ′ is introduced into the abdominal cavity to make a diagnosis, it is preferable to make the radiation detecting section 1 ′ as small as possible. That is, in some cases, it is preferable to configure the radiation detection unit 1 ′ to be smaller than the above specific numerical example.
Also, in some cases, the feeling of grasping in the palm,
In some cases, it may be preferable to make the configuration larger than the specific numerical example described above for reasons such as handling.

[0093] Further, although the above description has been made with particular reference to the substantially square or substantially circular form, it goes without saying that the present invention is not limited to these forms. For example, a form such as a substantially rectangular shape and a substantially elliptical shape can be adopted.

In short, the specific numerical values or specific shapes described above are merely preferred examples of the present invention, and the present invention may take various other forms.

Further, in the radiation detecting section 1 'in the third embodiment, as described in the first embodiment, a marking M is formed at a predetermined location of the detecting section 1', and It is needless to say that it is more preferable that the mark display M ′ corresponding to the above is displayed on the image display unit 5.

Hereinafter, a modification of the third embodiment will be described. In the above-described radiation detection unit 1 'which can be handled by the operator's hand, as shown in FIGS. 14A and 14B, the radiation detection unit 1' starts and ends gamma ray data collection. A button (hereinafter, referred to as a “data collection command button”) can be added.

In FIG. 14A, the radiation detector 1
The structure provided with the data collection command button 1'c is shown on the side of (the housing 1'b). In FIG. 14B, instead of a simple cable as shown in FIGS. 11 and 12 connected to the radiation detection unit 1 ', a grip unit 1'd provided with a data collection button 1'c.
Are connected. Gripper 1
As' d, a flexible arm or the like whose posture can be fixed can be employed.

In any case, it is obvious that such a configuration contributes to more prompt diagnosis and the like.

As another modification, as shown in FIG. 15, an access device in which an image display unit 5 and a dialogue unit 7 are integrated with a radiation detection unit 1 'in the third embodiment. It is also possible to adopt a form in which 57 is connected via a cable 571 (the combined use of the image display unit 5 and the dialogue unit 7 described in the second embodiment).

In FIG. 15, the access device 57 has a configuration in which the image display unit 5 is arranged on the left side of the figure and the input unit 8 is arranged on the right side. The user of the device can input various settings or commands as described in the first embodiment, for example, setting one or more energy ranges (or energy windows) necessary for imaging via the input unit 8, It is possible to set acquisition conditions such as a gamma ray acquisition time or an acquisition count, or to issue an instruction to start or end an acquisition, an instruction to restart an acquisition, an instruction to redisplay an image, an instruction to switch between a persistent mode and an accumulated image, and the like. . Also,
The display of the screen used for the setting, the display of the confirmation screen of the setting content, and the like can be performed on the image display unit 5 of the access device 57 (the above description clearly shows that the “dialogue unit” is configured). ). If the specific configuration of the input unit 8 is specialized for each function such as these various settings or commands, it is convenient for intraoperative operation.

Further, as is apparent from the configuration shown in FIG. 14, a radiation detector 1 'different from the one shown in the drawing can be easily connected to the access device 57, and a plurality of radiation detectors 1' can be provided. In such a case, based on the signals sent from the plurality of radiation detection units 1 ′, these may be displayed separately or simultaneously.
The input unit 8 can be provided with specialized buttons for such functions. In addition, each of the plurality of radiation detection units 1 ′ can be prepared, for example, as a unit in which a collimator (see FIGS. 3 to 7) which is separately formed is installed (related to the radiation detection unit 1 ″). See also below).

It is clear that such a configuration contributes to an agile diagnosis of the operator.

Hereinafter, a fourth embodiment of the present invention will be described. The fourth embodiment relates to a modification of the nuclear medicine diagnostic apparatus according to the second embodiment. That is, in the second embodiment, the radiation detector 1
And the image display unit 5 is configured so as to be back-to-back (that is, the normal line of the detection surface of the detection element 12 is opposite to that of the image display surface (or both are parallel)). In the fourth embodiment, as shown in FIG. 16, the radiation detection unit and the image display unit face each other (so-called “intersection” between the normal of the detection surface and that of the image surface).
The feature is that the configuration is such that In addition,
Such a configuration is hereinafter referred to as “direct monitor unit 1”.
5 '".

In FIG. 16, the direct monitor 15
The radiation detecting section 1 '' constituting the 'has a configuration in which the mounting surface 1''e, which can be mounted at an appropriate location, faces downward in the figure and its detection surface faces upward in the figure. . According to such a radiation detection unit 1 '', an organ or the like resected by a surgical procedure can be placed on the detection surface 1''a. In addition, as a specific size of the detection surface 1''a, for example, assuming that a liver is placed, etc.,
It may be "A4 size" or the like.

It should be noted that the image display unit 5 in FIG. 16 is provided in addition to the access device 57 in the third embodiment, that is, the image display unit 5 is “facing” each other because the radiation detection unit 1 ″ and the access device 57 Are particularly indicated. Further, as shown in FIG. 16, the radiation device 1 'may be separately connected to the access device 57, as in the third embodiment. It is needless to say that such a form is an example of a form in which a plurality of radiation detection units described above are provided as modifications of the third embodiment. Further, the present invention is not particularly limited with respect to the “size” of the above-described radiation detection unit 1 ″, but the size of the detection surface is
Generally, it is configured to be larger than the detection surface of the radiation detection unit 1 '.

According to such a configuration, in a certain kind of operation, it is possible to easily confirm the RI distribution of the organ, which is sometimes necessary after the removal of the organ. Also,
As shown in FIG. 16, it is clear that the form having both the radiation detection units 1 ″ and 1 ′ further increases the degree of freedom of use.

In the fourth embodiment, a rotatable hinge (connecting portion) is provided at a portion where the connection between the radiation detecting portion 1 '' and the image display portion 5 (the access device 57 in FIG. 16) is established. 17), an appropriate configuration of the second embodiment and the fourth embodiment can be achieved simultaneously, as shown in FIG. In other words, when the radiation detection unit 1 ″ is back-to-back with the image display unit 5 by the hinge 151 (in the direction of the arrow α in FIG. 17), use as in the second embodiment (the direct monitor unit 15) is performed. In the case where the two are faced to each other (as indicated by the arrow β in FIG. 17) as shown in FIG. 17, the use as in the fourth embodiment (the direct monitor unit 15 ′) is possible.

In some cases, the radiation detecting section 1 ″ used for the above purpose is connected to the image display section 5 by a cable (not shown), and only the radiation detecting section 1 ″ is free. You may comprise so that it may be able to manage to. According to this, it is possible to acquire the RI distribution image by pressing the radiation detection unit 1 ″ against a relatively large organ, tissue, diseased part, or the like that has been resected by a surgical procedure. In addition, a configuration in which such a radiation detection unit 1 ″ is attached to the support stand 100 as in the first embodiment is of course also effective.

Hereinafter, a modification of the fourth embodiment will be described. In the radiation detection unit 1 '' capable of acquiring an image of an organ or the like resected by the above-described surgical procedure, as shown in FIG. It is possible to use an arc-shaped one having a specific curvature and mount the fan beam collimator 11F on the detection surface of the radiation detection unit 1 ''. According to this, the sensitivity of the measurement of the gamma dose is improved, and a one-dimensional enlarged image can be obtained. In order to obtain the image, the focus of the fan beam is located outside the organ O or the like.

In connection with the above, a “cone beam collimator” can be used similarly. In this case, a two-dimensional enlarged image can be obtained. Note that, in order to obtain the image, the focal point of the cone beam is located outside the organ or the like as described above.

As still another modification, as shown in FIG. 19, on the collimator 11 of the radiation detector 1 '',
It is possible to provide a tray 9 on which an organ O or the like that can be controlled to move along the detection surface is placed. According to the tray 9, the image resolution can be improved by the above-described control or moving method.

That is, for example, the number N of times the tray 9 is moved (shifted) per detecting element 12 is input by the dialogue unit 7 before the start of the collection of gamma ray data. Next, gamma ray data collection is started in a state where the detection element 12 and the tray 9 are at the initial position, and the collection ends when a preset data collection time or collection count is reached. Thereafter, the same gamma ray data collection as described above is performed while shifting the tray 9 on the collimator 11 by 1 / N pitch in the X direction (right direction in the figure). When the collection of N times of gamma ray data in the X direction is completed, the tray 9 is moved (shifted) by 1 / N pitch in the Z direction (vertical direction in the drawing). Thereafter, collection of gamma ray data similar to the above is repeated in the direction opposite to the X direction. According to such a method, if the moving position of the organ O and the like (the tray 9 on which the organ O is placed) is read by appropriate means for each collection, the data for each collection is obtained by dividing the detection element 12 into N points. And the resolution can be improved.

In the following, supplementary items relating to the present invention or the above embodiments will be described. First, the setting of the “ROI” described in the first embodiment or the setting of the energy range (or energy window) described several times above is common to all the embodiments regardless of the present invention or the above embodiments. Can be implemented.

More specifically, the “ROI” can be set on a setting screen as shown in FIG. 20, for example. One or a plurality of “ROIs” can be set for an area in which gamma ray data is to be collected, and this can be confirmed on the image display unit 5. Then, it is naturally possible to display the count number for each area on the image display unit 5.

On the other hand, the energy range (or energy window) can be set, for example, on a setting screen as shown in FIG. In particular, when a plurality of collected energy ranges as shown in FIG. 21 are set, the sum of gamma ray data for each energy range and the count number for each energy range are displayed.

All other information such as the image data based on the gamma ray data, the ROI, the energy range, and the like can be stored in a storage device (not shown) by pressing a “save button” (not shown) provided in the dialogue section 7. And that the image can be re-displayed on the display unit by the “read button”, that the image can be enlarged or reduced, and the like. can do.

Further, the nuclear medicine diagnostic apparatus according to each of the above-described embodiments is provided with an externally connected printer and the like in addition to the image display section 5, and can output the obtained images and the like to the apparatus.

In addition, a battery can be used as a power supply for driving the nuclear medicine diagnostic apparatus according to each of the above embodiments. This is, for example, the processing device 20 described above.
And 21, and in some cases, the direct monitor unit 15 in the second embodiment.
It is possible to provide a device in which a power cable or the like does not interfere during the operation. According to this, movement to the outside of the operating room is also possible.

In addition, since the radiation detector in each of the above-described embodiments is basically “manageable”, the peripheral corners of the radiation detector may cause unnecessary damage to the subject P or the like. So that there is no such thing as
It is preferable to perform edge removal processing. That is, for example,
Although the radiation detection unit 1 in the first embodiment has a substantially rectangular parallelepiped shape as shown in FIG. 2, the respective surfaces constituting the substantially rectangular parallelepiped do not intersect at right angles, but have an appropriate curvature. It is better to apply "rounding" so that they intersect. In this regard, the radiation detector 1 'having a substantially circular shape as shown in FIG. 11B described as the third embodiment can be said to be excellent. However, as is apparent from FIG. 11B and the like, the outer shape of the radiation detection unit 1 ′ is “substantially cylindrical shape”.
It is preferable that the portion where the circular bottom surface and the cylindrical side surface intersect is subjected to the above-mentioned rounding.

Further, it should be further noted that the above “management is possible”. When an image is actually acquired by performing such an operation, a “blur” is displayed on the image on the image display unit 5. May occur. Therefore, it is preferable that the radiation detection unit in each of the above embodiments is provided with an appropriate “image blur removal unit”. As the "image blur removing means", for example, a device mainly including a piezoelectric conversion element (piezo element) can be considered. In this case, one or a plurality of the piezoelectric conversion elements are mounted on predetermined positions of the various radiation detection units, and a change in load (a change in acceleration) generated when the radiation detection unit is routed is measured. It is configured to be detected by the piezoelectric conversion element and emit an electric signal corresponding thereto. By using this electric signal as correction data at the time of creating a planar image or reconstructing a tomographic image in the image creating section 4, it is possible to appropriately remove image blur.

Further, in the radiation detecting section in each of the above-described embodiments, the detection surface may be washed with water or the like according to an appropriate number of uses so that accurate detection can always be performed. This water washing can be easily carried out because the radiation detection unit in each of the above embodiments can be handled.

Further, some of the control sections 6 and the like constituting the processing apparatus 20 in the first embodiment may be provided on the radiation detecting section 1 side if possible. The same applies to the direct monitor unit 15 or 15 'in the second or fourth embodiment, and the access device 57 in the modification of the third embodiment.

Further, the direct monitor unit 15 in the second embodiment, the hinge 1 described in the fourth embodiment,
Regarding the direct monitor unit 15 ′ including the support stand 51, considering that these are directly applied to the subject P and used, the support stand 10 ′ described in the first embodiment is used.
It would be preferable to have a configuration that can be attached to zero. Of course, if possible, it may be handled by the operator's hand.

Finally, as a special use of the nuclear medicine diagnostic apparatus according to each of the above embodiments, for example, the radiation detecting section 1 attached to the support stand 100 in the first embodiment, the radiation detecting section in the third embodiment, 1 ′, or (the radiation detection unit 1 or 1 ″ of the direct monitor unit 15 or 15 ′ in the second or fourth embodiment)
Can be used to identify the contaminated area by applying it to an arbitrary place such as a wall in an operating room which is considered to be contaminated by a radioisotope. In this case, since the energy resolution of the radiation detection unit 1 and the like is high, it is possible to select contaminated nuclides, and it is possible to visualize the contaminated region by the image display unit 5 and the like.

[0125]

As described above, according to the nuclear medicine diagnostic apparatus of the present invention, it is possible to use the apparatus while operating freely in the operating room while achieving practically sufficient performance such as resolution.
For this reason, the device according to the present invention is extremely effective especially in “breast conserving therapy” and the like.

[Brief description of the drawings]

FIG. 1 is a schematic diagram illustrating a configuration example of a nuclear medicine diagnostic apparatus according to a first embodiment of the present invention.

FIG. 2 is a schematic view showing a support stand constituting the nuclear medicine diagnostic apparatus shown in FIG.

FIG. 3 is a schematic diagram showing a configuration example of a radiation detection unit which is a main part of the nuclear medicine diagnostic apparatus shown in FIG.

FIG. 4 is a schematic diagram illustrating a configuration example of a radiation detection unit different from FIG. 2, in which a collimator is “thickened”;

FIG. 5 is a schematic diagram illustrating a configuration example of a radiation detection unit different from FIGS. 2 and 3, in which the size of the detection element 12 is increased.

6 is a schematic diagram illustrating a configuration example of a radiation detection unit different from FIGS. 3, 4, and 5, in which a plurality of collimator partitions are arranged for one detection element 12. FIG.

FIG. 7 is a schematic diagram illustrating a configuration example of a radiation detection unit different from FIG. 2, in which a collimator is “thinned”;

FIG. 8 is an explanatory diagram illustrating an example in which the nuclear medicine diagnostic apparatus according to the first embodiment is applied to measurement of a blood flow rate in an affected part of a subject.

FIG. 9 is a schematic diagram showing a configuration example according to a modification of the nuclear medicine diagnostic apparatus shown in FIG. 2 and a support stand constituting the apparatus.

FIG. 10 is a schematic diagram showing a configuration example of a direct monitor unit and the like constituting a nuclear medicine diagnostic apparatus according to a second embodiment of the present invention.

FIGS. 11A and 11B are schematic diagrams illustrating a configuration example of a radiation detection unit included in the nuclear medicine diagnostic apparatus according to the third embodiment of the present invention, wherein FIG. 11A is a substantially square shape, and FIG. It is a figure which shows what becomes a circular shape, respectively.

12 is a schematic diagram showing an example of a detection surface configuration of the radiation detection unit shown in FIG. 11, wherein (a) has a substantially square shape;
(B) is a figure which shows what becomes a substantially circular shape, respectively.

13 is a schematic diagram illustrating a configuration example of a housing of the radiation detection unit illustrated in FIG.

14A and 14B are schematic diagrams illustrating a modified example of the radiation detection unit illustrated in FIG. 11, wherein FIG. 14A illustrates a mode in which a data collection command button is provided on a side surface of a housing, FIG. FIG.

FIG. 15 is a schematic diagram showing a modified example of the radiation detecting section shown in FIG. 11, and shows an example of a configuration in which an image display section and a dialog section are integrally formed.

FIG. 16 is a schematic diagram illustrating a configuration example of a direct monitor unit included in a nuclear medicine diagnostic apparatus according to a fourth embodiment of the present invention.

FIG. 17 illustrates a form in which a rotatable hinge is provided at a connection point between the radiation detection and the image display unit in the radiation detection unit illustrated in FIG. 16;

FIG. 18 is a schematic diagram showing a modified example of the radiation detection unit shown in FIG. 16 and shows an example of a configuration employing a fan beam collimator.

FIG. 19 is a schematic diagram showing a modified example of the radiation detection unit shown in FIG. 16, showing a form in which a tray movable on a collimator and along a detection surface is installed.

FIG. 20 is an explanatory diagram illustrating a display example of an ROI setting screen.

FIG. 21 is an explanatory diagram showing a display example of an energy range setting screen.

FIG. 22 is a schematic diagram illustrating a configuration example of a conventional radiation detection unit (semiconductor detector).

FIG. 23 is a schematic diagram illustrating a configuration example of a conventional radiation detection unit (semiconductor detector).

FIG. 24 is a schematic diagram showing a configuration example of a conventionally used single detector probe.

[Explanation of symbols]

1 ', 1''Radiation detection unit 1'a, 1''a Detection surface 1'b Housing 1'c Data collection command button 1'd Gripping unit 11, 11', 11 '', 11 ''', 11P Collimator 11F Fan beam collimator 11a, 11Pa Partition 11b, 11Pb Opening 12, 12 'Semiconductor detection element 2 Data collection unit 3 Memory 4 Image creation unit 5, 51 Image display unit 6 Control unit 7 Dialogue unit 8 Input unit 9 Tray 20, 21 Processing Device 15, 15 'Direct Monitor Unit (Form Having Both Radiation Detection Unit and Image Display Unit) 151 Hinge 57 Access Device (Form Having Both Image Display Unit and Dialogue Unit) 100 Support Stand 101 Base 102 Support Column 103 Joint 104 Arm Part 104a first arm 104b second arm 104c flexible joint P subject O organ Vessel θ acceptance angle

Continued on front page F term (reference) 2G088 EE02 FF04 GG21 JJ22 JJ23 KK32 4M118 AA10 AB01 BA05 CA06 CB05 GA09 GA10 5F088 AB09 BA15 BB07 EA04 JA20 LA07

Claims (19)

[Claims] 1. A radiation detecting means in which a plurality of semiconductor detecting elements are arranged side by side, a collimator for restricting an incident mode of radiation emitted from inside a subject to the semiconductor detecting elements by an opening thereof, and In a nuclear medicine diagnostic apparatus comprising: an image display unit configured to display an image related to the subject created based on an output signal, such that a detection surface of the semiconductor detection element can be directed to an arbitrary direction. A nuclear medicine diagnostic apparatus, comprising: support means for supporting the radiation detection means. 2. The nuclear medicine diagnostic apparatus according to claim 1, wherein a support point at which the support unit supports the radiation detection unit is a point where symmetry of the radiation detection unit is removed. 3. The support stand is arranged such that a position of the support point is specified from a positional relationship between the subject and a user of the apparatus, and a portion corresponding to the support point in the image display. 3. The nuclear medicine diagnostic apparatus according to claim 2, wherein the apparatus corresponds to a predetermined location on the means. 4. The support means includes a base, a support column held perpendicular to the base, and a position that can be changed by rotating the support column in a direction parallel to an axial direction of the support column. The nuclear medicine diagnostic apparatus according to claim 2, further comprising a joint and an arm connected to the joint, wherein the support point is a connection point between the radiation detection unit and the arm. 5. The arm unit according to claim 4, wherein the arm unit includes a plurality of arms and a flexible joint that rotatably connects each of the plurality of arms.
A nuclear medicine diagnostic apparatus according to claim 1. 6. The nuclear medicine diagnostic apparatus according to claim 5, wherein a rotation angle sensor is provided at the joint and / or the flexible joint. 7. A marking is formed at a predetermined portion of the radiation detecting means, and a mark corresponding to a position at which the marking is formed is displayed on the image display means together with the display of the image. The nuclear medicine diagnostic apparatus according to claim 1, wherein: 8. The nuclear medicine diagnostic apparatus according to claim 7, wherein the predetermined location where the marking is formed is a location where the symmetry of the radiation detecting means is removed. 9. A radiation detecting means in which a plurality of semiconductor detecting elements are arranged side by side, a collimator for restricting an incident mode of radiation emitted from inside a subject to the semiconductor detecting elements by an opening thereof, and A nuclear medicine diagnostic apparatus comprising: an image display unit configured to display an image of the subject created based on the output signal; wherein the radiation detection unit and the image display unit are integrally configured. Nuclear medicine diagnostic device characterized. 10. The nuclear medicine diagnostic apparatus according to claim 9, wherein said image display means is provided with a dialogue section capable of performing settings, instructions and the like relating to said apparatus. 11. The image display device according to claim 10, wherein said image display means is an image display device of an LCD touch panel type.
A nuclear medicine diagnostic apparatus according to claim 1. 12. The method according to claim 1, wherein a normal line of a detection surface of the semiconductor detection element constituting the radiation detection unit and a normal line of an image display surface of the image display unit can be set to cross each other. The nuclear medicine diagnostic apparatus according to claim 9, wherein 13. The nuclear medicine diagnostic apparatus according to claim 12, further comprising a tray on which the specimen can be placed and which can be controlled to move on the collimator and along the detection surface. 14. The radiation detection means and the image display means are integrally formed by a connecting portion which is rotatable so that the detection surface and the image display surface face to each other or back to back. The nuclear medicine diagnostic apparatus according to claim 12, wherein 15. A radiation detecting means in which a plurality of semiconductor detecting elements are juxtaposed, a collimator for restricting an incident mode of radiation emitted from inside a subject to the semiconductor detecting element by an opening thereof, and A nuclear medicine diagnostic apparatus comprising: an image display unit configured to display an image of the subject created based on the output signal. A nuclear medicine diagnostic apparatus characterized by being configured as described above. 16. The nuclear medicine diagnostic apparatus according to claim 15, wherein said radiation detecting means has a housing having a size of 60 mm × 60 mm × 10 mm. 17. The nuclear medicine diagnostic apparatus according to claim 1, wherein each of the semiconductor detection elements has a one-to-one correspondence with each of the openings of the collimator. 18. The nuclear medicine diagnosis according to claim 1, wherein each of the semiconductor detection elements has a pair of arbitrary integer values corresponding to each of the openings of the collimator. apparatus. 19. The apparatus according to claim 1, wherein said radiation detecting means includes an image blur removing means for correcting a blur of said image on said image display means.
Nuclear medicine diagnostic apparatus according to any one of the above.