JP2016042887A - Magnetic resonance imaging apparatus and image processing apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a magnetic resonance imaging apparatus capable of generating a joined image in which images are continuously joined to each other even if cross sections of a plurality of non-coplanar cross-sectional images do not intersect with each other.SOLUTION: The magnetic resonance imaging apparatus 10 comprises: a static magnetic field generation unit for generating a static magnetic field; a gradient magnetic field generation unit for generating a gradient magnetic field; a transmission coil for applying a high frequency pulse to a subject; original-image generation means 43 for generating a plurality of non-coplanar cross-sectional images on the basis of a signal corresponding to the high frequency pulse; joined-cross section setting means 44 for setting a new cross section different from any of the cross sections of the plurality of cross-sectional images and for setting a joined cross section on the basis of at least one of the cross sections of the plurality of cross-sectional images and the new cross section; joining-target image generation means 45 for generating cross-sectional images relating to the cross sections comprising the joined cross section; and joined-image generation means 46 for generating a joined image by applying join processing to the cross-sectional images relating to the joined cross section.SELECTED DRAWING: Figure 2

Description

  Embodiments as one aspect of the present invention relate to a magnetic resonance imaging (MRI) apparatus and an image processing apparatus that perform joint processing based on a plurality of cross-sectional images.

  An MRI apparatus magnetically excites a nuclear spin of a subject placed in a static magnetic field with a radio frequency (RF) pulse of a Larmor frequency, and a nuclear magnetic resonance (NMR) generated by the excitation. (resonance) signal to reconstruct the image.

  When an image diagnostic apparatus such as an MRI apparatus obtains an image of an imaging region over a wider area than a collection region (FOV: field of view), it applies each of the collection regions to a plurality of portions of the imaging region. Take an image. The diagnostic imaging apparatus performs a stitching process on the first cross-sectional image obtained by imaging the first acquisition region and the second cross-sectional image obtained by imaging the second acquisition region. Then, the diagnostic imaging apparatus performs one combining process on the first slice image and the second slice image, thereby generating one combined image related to the imaging region over a wide range.

  By displaying the combined image by the diagnostic imaging apparatus, the diagnostician can observe the imaging region on one image, so that the whole image can be easily recognized.

  As a conventional technique related to the present invention, there is disclosed a technique for smoothly connecting between an overlapping area and a non-overlapping area in an image obtained by joining two input images that are on the same plane and have an overlapping area. (For example, refer to Patent Document 1).

JP 2013-16164 A

  The first cross section of the first cross-sectional image obtained by imaging the first collection area and the second cross-section of the second cross-sectional image obtained by imaging of the second collection area are not on the same plane, When the first cross section of the first cross section image and the second cross section of the second cross section image do not intersect, there is no image related to the cross section between the first cross section and the second cross section. Therefore, a combined image in which a portion between the first cross-sectional image and the second cross-sectional image is missing is generated by the combining process, and the combined image becomes discontinuous.

  In order to solve the above-described problem, the MRI apparatus according to the present embodiment includes a static magnetic field generation unit that generates a static magnetic field, a gradient magnetic field generation unit that generates a gradient magnetic field, and a transmission coil that applies a high-frequency pulse to a subject. And an original image generating means for generating a plurality of cross-sectional images that are not on the same plane based on a signal corresponding to the high-frequency pulse, and setting a cross-section different from any cross-section of the plurality of cross-sectional images, A combined cross-section setting means for setting a combined cross-section based on at least one of the cross-sections of the cross-sectional image and the different cross-sections, a combining target image generating means for generating a cross-sectional image relating to each cross-section constituting the combined cross-section, Combined image generation means for generating a combined image by performing a combining process on each cross-sectional image related to the combined cross section.

  In order to solve the above-described problem, the image processing apparatus according to the present embodiment includes an original image acquisition unit that acquires a plurality of cross-sectional images that are not on the same plane from the storage unit, and any cross-section of the plurality of cross-sectional images. A cross-section setting unit that sets a different cross-section, sets a cross-section based on at least one of the cross-sections of the plurality of cross-sectional images and the different cross-sections, and cross-sectional images related to each cross-section constituting the combined cross-section A combining target image generating unit that generates the combined image, and a combined image generating unit that generates a combined image by performing a combining process on each cross-sectional image related to the combined cross section;

Schematic which shows the hardware constitutions of the MRI apparatus which concerns on this embodiment. The block diagram which shows the function of the MRI apparatus which concerns on this embodiment. The figure which shows the example of the 1st cross section which is not on the same plane, and a 2nd cross section. The figure which shows the example of the 1st cross section which is not on the same plane, and a 2nd cross section. The figure for demonstrating the production | generation method of the combined image using a prior art. The figure for demonstrating the production | generation method of the combined image using a prior art. The figure which shows the joint image based on the 1st cross-section image which concerns on the 1st cross section shown in FIG. 6, and the 2nd cross-section image which concerns on a 2nd cross section. (A), (B) is a figure for demonstrating the 1st setting method of a joint cross section. (A), (B) The figure for demonstrating the 2nd setting method of a joint cross section. (A), (B) The figure for demonstrating the 3rd setting method of a joint cross section. FIG. 9 is a diagram illustrating an example of a combined image based on the first setting method of the combined cross section illustrated in FIGS. FIG. 10 is a diagram illustrating an example of a combined image based on the second setting method of the combined cross section illustrated in FIGS. The figure which shows the example of the combined image based on the 3rd setting method of a joint cross section shown to FIG. 10 (A), (B). The figure for demonstrating the method of selecting an appropriate new cross section from several new cross sections. The figure for demonstrating the method of selecting an appropriate new cross section from several new cross sections for every part which performs a joint process. (A) thru | or (D) is a figure for demonstrating the method of selecting an appropriate method from the several setting method of a coupling cross section. The figure which shows the example of a display when a cursor is set to 1 among three new cross sections in FIG.16 (C). 1 is a schematic diagram showing a hardware configuration of an image processing apparatus according to the present embodiment. FIG. 2 is a block diagram illustrating functions of the image processing apparatus according to the present embodiment.

  An MRI apparatus and an image processing apparatus according to this embodiment will be described with reference to the accompanying drawings.

(MRI apparatus according to this embodiment)
FIG. 1 is a schematic diagram illustrating a hardware configuration of the MRI apparatus according to the present embodiment.

  FIG. 1 shows an MRI apparatus 10 according to this embodiment that performs imaging on an imaging region of a subject (patient) P. The MRI apparatus 10 mainly includes an imaging system 11 and a control system 12.

  The imaging system 11 includes a static magnetic field magnet 21, a gradient magnetic field coil 22, a gradient magnetic field power supply device 23, a bed 24, a bed control unit 25, a transmission coil (RF coil for transmission) 26, a transmission unit 27, and a reception coil (reception). RF coils) 28a to 28e, a receiving unit 29, and a sequencer (sequence controller) 30.

  The static magnetic field magnet 21 is formed in a hollow cylindrical shape at the outermost part of a gantry (not shown), and is a static magnetic field generation unit that generates a uniform static magnetic field in the internal space. As the static magnetic field magnet 21, for example, a permanent magnet, a normal conducting magnet, a superconducting magnet, or the like is used.

  The gradient magnetic field coil 22 is formed in a hollow cylindrical shape, is disposed inside the static magnetic field magnet 21, and is a gradient magnetic field generation unit that generates a gradient magnetic field in the internal space. The gradient coil 22 is formed by combining three coils corresponding to X, Y, and Z axes orthogonal to each other, and these three coils are individually supplied with current from the gradient magnetic field power supply device 23. Thus, a gradient magnetic field whose magnetic field intensity changes along the X, Y, and Z axes is generated. The Z-axis direction is the same direction as the static magnetic field.

  Here, the gradient magnetic fields of the X, Y, and Z axes generated by the gradient magnetic field coil 22 respectively correspond to, for example, a readout gradient magnetic field Gr, a phase encoding gradient magnetic field Ge, and a slice selection gradient magnetic field Gs. doing. The readout gradient magnetic field Gr is used to change the frequency of an NMR (nuclear magnetic resonance) signal in accordance with the spatial position. The phase encoding gradient magnetic field Ge is used to change the phase of the NMR signal in accordance with the spatial position. The slice selection gradient magnetic field Gs is used to arbitrarily determine an imaging section.

  The gradient magnetic field power supply device 23 supplies current to the gradient magnetic field coil 22 based on the pulse sequence execution data sent from the sequencer 30.

  The bed 24 includes a top plate 24a on which the subject P is placed. The couch 24 inserts the couchtop 24a into the cavity (imaging port) of the gradient magnetic field coil 22 with the subject P placed under the control of the couch controller 25 described later. Usually, the bed 24 is installed such that the longitudinal direction is parallel to the central axis of the static magnetic field magnet 21.

  The couch controller 25 drives the couch 24 under the control of the sequencer 30 to move the couchtop 24a in the longitudinal direction and the vertical direction.

  The transmission coil 26 is disposed inside the gradient magnetic field coil 22, receives an RF pulse signal from the transmission unit 27, and generates an RF pulse.

  The transmission unit 27 transmits an RF pulse signal corresponding to the Larmor frequency to the transmission coil 26 based on the pulse sequence execution data transmitted from the sequencer 30.

  The receiving coils 28a to 28e are arranged inside the gradient magnetic field coil 22 and receive NMR signals radiated from the imaging region of the subject P due to the influence of the high frequency magnetic field. Here, the receiving coils 28a to 28e are array coils each having a plurality of element coils that respectively receive NMR signals emitted from the imaging region of the subject P, and the NMR signals are received by the element coils. The received NMR signal is output to the receiving unit 29.

  The receiving coil 28a is a head coil that is attached to the head of the subject P. The receiving coils 28b and 28c are spinal coils arranged between the back of the subject P and the top plate 24a, respectively. The receiving coils 28d and 28e are abdominal coils mounted on the ventral side of the subject P, respectively.

  The receiving unit 29 generates an NMR signal based on the NMR signal output from the receiving coils 28 a to 28 e based on the pulse sequence execution data sent from the sequencer 30. In addition, when generating the NMR signal, the receiving unit 29 transmits the NMR signal to the control system 12 via the sequencer 30.

  The receiving unit 29 has a plurality of receiving channels for receiving NMR signals output from a plurality of element coils included in the receiving coils 28a to 28e. And when the element coil used for imaging is notified from the control system 12, the receiving unit 29 receives the notified element coil so that the NMR signal output from the notified element coil is received. Assign a receive channel.

  The sequencer 30 is connected to the gradient magnetic field power supply device 23, the bed control unit 25, the transmission unit 27, the reception unit 29, and the control system 12. The sequencer 30 includes control information necessary for driving the gradient magnetic field power supply device 23, the bed control unit 25, the transmission unit 27, and the reception unit 29, for example, the intensity and application time of the pulse current to be applied to the gradient magnetic field power supply device 23. The sequence information describing the operation control information such as the application timing is stored.

  In addition, the sequencer 30 drives the bed control unit 25 according to the stored predetermined sequence, thereby moving the table 24a forward and backward in the Z direction with respect to the gantry. Further, the sequencer 30 drives the gradient magnetic field power supply device 23, the transmission unit 27, and the reception unit 29 in accordance with the stored predetermined sequence, so that the X-axis gradient magnetic field Gx, the Y-axis gradient magnetic field Gy, and the Z-axis gradient are placed in the gantry. A magnetic field Gz and an RF pulse signal are generated.

  The control system 12 performs overall control of the MRI apparatus 10, data collection, image reconstruction, and the like. The control system 12 includes a control unit 31, an input unit 32, a display unit 33, a communication unit 34, a storage unit 35, an interface unit 36, a data collection unit 37, and a data processing unit 38.

  The control unit 31 includes a CPU (central processing unit) or an MPU (micro processor unit), a memory, and the like (not shown). The control unit 31 reads out various control programs stored in the storage unit 35 and performs various calculations, and comprehensively controls processing operations in the respective units 52 to 55 of the imaging system 11 and the control system 12.

  The input unit 32 is configured with a keyboard, a mouse, and the like. When the input unit 32 is operated by the operator, the input unit 32 generates an operation signal corresponding to the operation and outputs the operation signal to the control unit 31. The MRI apparatus 10 may include a touch panel in which the input unit 32 is configured integrally with the display in the display unit 33.

  The display unit 33 is configured by an LCD (Liquid Crystal Display) or the like. The display unit 33 displays various operation screens and various display information such as image data on the LCD in response to an instruction from the control unit 31.

  The communication unit 34 is configured by a connector that conforms to a parallel connection specification or a serial connection specification. The communication unit 34 transmits / receives information to / from an external device on the network. For example, the communication unit 34 performs communication operation with an external device by transmitting image data generated by the MRI apparatus 10 to a server or an interpretation terminal (not shown).

  The storage unit 35 is configured by a memory, an HDD (hard disk drive), or the like. The storage unit 35 stores data necessary for the execution of each program in addition to the control program used in the control unit 31 and various processing programs such as coupling processing. The storage unit 35 stores image data generated by the MRI apparatus 10.

  The interface unit 36 is connected to the gradient magnetic field power supply device 23, the bed control unit 25, the transmission unit 27, and the reception unit 29 through the sequencer 30, and is exchanged between these connected units and the control system 12. Control the input and output of the generated signals.

  The data collection unit 37 collects NMR signals transmitted from the reception unit 29 via the interface unit 36. When collecting the NMR signal, the data collecting unit 37 stores the collected NMR signal in the storage unit 35.

  The data processing unit 38 performs post-processing, that is, reconstruction processing such as Fourier transform, on the NMR signal stored in the storage unit 35, thereby obtaining spectrum data of desired nuclear spins within the imaging region of the subject P. Alternatively, image data is generated. In addition, when the positioning image is captured, the data processing unit 38 determines the NMR signal in the arrangement direction of the element coils based on the NMR signals received by the plurality of element coils included in the reception coils 28a to 28e. Is generated for each element coil. The data processing unit 38 stores the generated various data in the storage unit 35.

  FIG. 2 is a block diagram showing functions of the MRI apparatus 10 according to the present embodiment.

  When the control unit 31 (or the sequencer 30) executes the program, as shown in FIG. 2, the MRI apparatus 10 includes an operation support unit 41, an imaging execution unit 42, an original image generation unit 43, a stitching section setting. It functions as a means 44, a combination target image generation means 45, and a combined image generation means 46. In addition, although it demonstrates as the case where the component 41 thru | or 46 of the MRI apparatus 10 function as software, the case where a part or all of the component 41 thru | or 46 is provided in the MRI apparatus 10 as a circuit may be sufficient.

  The operation support means 41 is an interface such as a GUI (Graphical User Interface) that mediates the components 41 to 46, the input unit 32, and the display unit 33.

  The imaging execution means 42 executes imaging for diagnosis by controlling the operation of the imaging system 11 in accordance with the imaging conditions at the imaging site (imaging position). The imaging execution unit 42 performs pre-imaging (imaging for setting parameters of imaging conditions for the main imaging) on the set imaging region prior to the main imaging, and generates a cross-sectional image regarding the imaging region. To do. Then, the imaging execution unit 42 sets imaging conditions (including the collection area) based on the cross-sectional image.

  When obtaining an image of an imaging region that covers a wider area than the collection region (FOV), the imaging execution unit 42 applies the plurality of collection regions to a plurality of portions of the imaging region in setting the imaging conditions. Then, the imaging execution unit 42 executes imaging for each collection area.

  The original image generation unit 43 controls the data collection unit 37 and the data processing unit 38 to perform predetermined image reconstruction processing such as two-dimensional or three-dimensional Fourier transform processing and maximum value projection processing on the k-space data. As a result, a plurality of cross-sectional images that are original images are generated for a plurality of cross-sections (slices) that are not on the same plane. For example, the original image generation unit 43 generates a first cross-sectional image related to a first cross section that is not on the same plane and a second cross-sectional image related to a second cross section.

  3 and 4 are diagrams showing examples of a first cross section and a second cross section that are not on the same plane.

  FIG. 3 shows two collection areas a1 and a2, a first cross section s1 among a plurality of cross sections belonging to the first collection area a1, and a second cross section s2 among a plurality of cross sections belonging to the second collection area a2. FIG. 4 shows two collection areas A1 and A2, a first cross section S1 among a plurality of cross sections belonging to the first collection area A1, and a second cross section S2 among a plurality of cross sections belonging to the second collection area A2. Here, the first cross section s1 and the second cross section s2 shown in FIG. 3 are not on the same plane, and the first cross section S1 and the second cross section S2 shown in FIG. 4 are not on the same plane.

  Returning to the description of FIG. 2, the combined cross-section setting unit 44 sets a new cross-section different from any cross-section of the plurality of cross-sectional images generated by the original image generation unit 43. When the first cross-sectional image related to the first cross-section and the second cross-sectional image related to the second cross-section are generated by the original image generating unit 43, the combined cross-section setting unit 44 sets the first cross-section of the first cross-sectional image, One new cross section different from any cross section with the second cross section of the two cross section image is set.

  The combined cross-section setting unit 44 sets a combined cross-section based on at least one of the cross-sections of the plurality of cross-sectional images generated by the original image generating unit 43 and the new cross-section. When there are a plurality of setting methods for the bonding cross section, the bonding cross section setting unit 44 may set the bonding cross section using any one of the plurality of setting methods.

  The combination target image generation unit 45 generates a cross-sectional image relating to each cross section constituting the combined cross section set by the combined cross section setting unit 44.

  5 and 6 are diagrams for explaining a combined image generation method using a conventional technique.

  FIG. 5 shows the first cross section s1 and the second cross section s2 that do not intersect with each other as shown in FIG. The first cross section s1 and the second cross section s2 are not on the same plane, but intersect with a straight line L (a straight line extending in the X direction).

  FIG. 6 shows the first cross section S1 and the second cross section S2 shown in FIG. The first cross section S1 and the second cross section S2 are not on the same plane and do not intersect. In this case, when the combining process is performed on the first cross-sectional image related to the first cross-section S1 and the second cross-sectional image related to the second cross-section S2, a combined image in which the images are continuous is not generated.

  FIG. 7 is a diagram showing a combined image based on the first cross-sectional image related to the first cross-section S1 shown in FIG. 6 and the second cross-sectional image related to the second cross-section S2.

  In the case where the first cross section S1 and the second cross section S2 shown in FIG. 6 do not intersect with each other, no image exists in the portion O shown in FIG. 7, so the combined image shown in FIG.

  FIGS. 8A and 8B are diagrams for explaining a first method for setting a coupling cross section.

  FIG. 8A shows the first cross section S1 and the second cross section S2 that do not intersect with each other, the first collection area A1 to which the first cross section S1 belongs, and the second collection area A2 to which the second cross section S2 belongs, as shown in FIG. Show. In this case, intersecting lines C and D (straight lines extending in the X direction) between the first cross section S1 and the second cross section S2 and the overlapping area A12 of the first collection areas A1 and A2 are obtained. Then, a new section SS formed by the intersection lines C and D is set.

  8B shows the first partial cross section S1 ′ cut out from the first cross section S1 based on the cross line C shown in FIG. 8A, the new cross section SS, and the cross line shown in FIG. 8A. A second partial cross section S2 ′ cut out from the second cross section S2 based on D is shown. FIG. 8B shows a coupling cross section S formed by the first partial cross section S1 ′, the new cross section SS, and the second partial cross section S2 ′.

  Then, when the combined cross section S is set, the first partial cross-sectional image related to the first partial cross-section S1 ′ is cut out from the first cross-sectional image, and the second related to the second partial cross-section S2 ′ is extracted from the second cross-sectional image. A partial cross-sectional image is cut out. Further, an interpolated cross-sectional image related to the new cross-section SS is generated based on cross-sectional images related to the other cross-sections T1 and U1 belonging to the first acquisition area A1, and related to other cross-sections T2 and U2 belonging to the second acquisition area A2. Based on the cross-sectional image, an interpolated cross-sectional image related to the new cross-section SS is generated. By combining (blending) the two interpolated cross-sectional images, a new cross-sectional image related to the new cross-section SS is generated.

  Since the first cross section S1 and the second cross section S2 shown in FIG. 8A are not on the same plane, the first cross section S1 and the second cross section S2 are naturally different cross sections. Further, since the new cross section SS shown in FIG. 8A is not on the same plane as the first cross section S1 and the second cross section S2, the new cross section SS is naturally different from the first cross section S1 and the second cross section S2. It is a different cross section.

  FIGS. 9A and 9B are diagrams for explaining a second method for setting the coupling cross section.

  9A and 9B show the first and second cross sections S1 and S2 that do not intersect, the first collection region A1 to which the first cross section S1 belongs, and the second collection to which the second cross section S2 belongs. Region A2 is shown. In this case, a termination line E (straight line extending in the X direction) of the first cross section S1 is obtained, and an intersection line F (straight line extending in the X direction) between the plane where the first cross section S1 exists and the second cross section S2 is obtained. . Then, a new cross section SS formed by the end line E and the intersection line F is set.

  9B shows a second partial cross section cut out from the second cross section S2 based on the first cross section S1 shown in FIG. 9A, the new cross section SS, and the intersection line F shown in FIG. 9A. S2 '. FIG. 9B shows a combined cross section S formed by the first cross section S1, the new cross section SS, and the second partial cross section S2 ′. Here, the first cross section S1 and the new cross section SS are on the same plane.

  When the combined cross section S is set, the second partial cross-sectional image related to the second partial cross-section S2 ′ is cut out from the second cross-sectional image. Further, a new cross-sectional image related to the new cross-section SS is generated based on the cross-sectional images related to the other cross-sections T2 and U2 belonging to the second collection area A2.

  Since the first cross section S1 and the second cross section S2 shown in FIG. 9A are not on the same plane, the first cross section S1 and the second cross section S2 are naturally different cross sections. Further, since the new section SS shown in FIG. 9A is not on the same plane as the second section S2, the new section SS is naturally a section different from the second section S2. Further, the new cross section SS shown in FIG. 9A is on the same plane as the first cross section S1, but the new cross section SS is a cross section different from the first cross section S1.

  FIGS. 10A and 10B are views for explaining a third method for setting the coupling cross section.

  FIGS. 10A and 10B show the first and second cross sections S1 and S2 that do not intersect as shown in FIG. 3, the first collection area A1 to which the first cross section S1 belongs, and the second collection to which the second cross section S2 belongs. Region A2 is shown. In this case, another new section SS that belongs to the second collection area A2 and intersects the first section S1 is set. In FIG. 10A, the first cross section S1 and the new cross section SS intersect at an intersection line G (a straight line extending in the X direction).

  FIG. 10B shows a first partial cross section S1 ′ cut out from the first cross section S1 based on the intersection line G shown in FIG. 10A, and a new cross section SS. FIG. 10B shows a combined cross section S formed by the first partial cross section S1 ′ and the new cross section SS.

  When the combined cross section S is set, the first partial cross-sectional image related to the first partial cross-section S1 ′ is cut out from the first cross-sectional image. Further, a new cross-sectional image related to the new cross-section SS is generated based on cross-sectional images related to other cross-sections belonging to the second collection area A2.

  Since the first cross section S1 and the second cross section S2 shown in FIG. 10A are not on the same plane, the first cross section S1 and the second cross section S2 are naturally different cross sections. Further, since the new section SS shown in FIG. 10A is not on the same plane as the first section S1 and the second section S2, the new section SS is naturally different from the first section S1 and the second section S2. It is a different cross section.

  Returning to the description of FIG. 2, the combined image generating unit 46 performs a combining process by performing a stitching process on the cross-sectional images generated by the combining target image generating unit 45 and relating to each cross section constituting the combined cross section. Generate an image. The combined image generation unit 46 generates a single combined image with continuous images regarding an imaging region over a wide range.

  The combined image generated by the combined image generating unit 46 is displayed on the display unit 33 or stored in the storage unit 35 via the operation support unit 41.

  Here, the combined cross-section setting means 44 has a first cross-section of the first cross-sectional image obtained by imaging the first acquisition area and a second cross-section of the second cross-section image obtained by imaging the second acquisition area. It may be determined whether or not to intersect, and whether or not to set a coupling cross section based on the result may be switched. In that case, when the combined cross-section setting unit 44 determines that the first cross section s1 and the second cross section s2 intersect as shown in FIG. 5, the combined image generating unit 46 does not set the combined cross section, and the related art. In accordance with the above, a combining process is performed on the first cross-sectional image related to the first cross-section s1 and the second cross-sectional image related to the second cross-section s2.

  On the other hand, when the combined cross section setting means 44 determines that the first cross section S1 and the second cross section S2 do not intersect as shown in FIG. 6, the combined cross section setting means 44 will be described with reference to FIGS. The combined cross section S is set using the method described above, and the combining target image generation unit 45 generates each cross-sectional image related to the combined cross section S. Then, the combined image generation unit 46 performs a combining process on each cross-sectional image related to the combined cross-section S.

  FIG. 11 is a diagram showing an example of a combined image based on the first setting method of the combined cross section shown in FIGS. 8 (A) and 8 (B).

  FIG. 11 shows a combined image according to the combined cross section S shown in FIG. As shown in FIG. 11, the combined image includes a first partial cross-sectional image related to the first partial cross-section S1 ′, a new cross-sectional image related to the new cross-section SS, and a second partial cross-sectional image related to the second partial cross-section S2 ′. This is the result of the join process performed on.

  FIG. 12 is a diagram showing an example of a combined image based on the second setting method of the combined cross section shown in FIGS. 9 (A) and 9 (B).

  FIG. 12 shows a combined image according to the combined cross section S shown in FIG. As shown in FIG. 12, the combined image is based on the first cross-sectional image related to the first cross-section S1, the new cross-sectional image related to the new cross-section SS, and the second partial cross-sectional image related to the second partial cross-section S2 ′. This is the result of the join process.

  FIG. 13 is a diagram illustrating an example of a combined image based on the third setting method of the combined cross section illustrated in FIGS. 10 (A) and 10 (B).

  FIG. 13 shows a combined image according to the combined cross section S shown in FIG. As illustrated in FIG. 13, the combined image is a result of the combining process performed on the first partial cross-sectional image related to the first partial cross-section S1 ′ and the new cross-sectional image related to the new cross-section SS.

(First modification)
The coupling section setting means 44 shown in FIG. 2 is set appropriately after setting a plurality of coupling sections using a plurality (two or more) of the coupling section setting methods described with reference to FIGS. A method may be selected.

  FIG. 14 is a diagram for explaining a method of selecting an appropriate new cross section from a plurality of new cross sections. FIG. 14 is based on the new cross-sectional image related to the new cross-section SS generated using the second method for generating a new cross-section described with reference to FIG.

  FIG. 14 shows a coupling section SS shown in FIG. 9B in an arbitrary YZ plane (yz plane when Y = y, Z = z). That is, in the yz plane, the coupling section SS is shown as a coupling line SSyz. FIG. 14 shows a first collection region A1 to which the first cross section S1 belongs and a second collection region A2 to which the second cross section S2 belongs in the yz plane. That is, in the yz plane, the first collection region A1 and the second collection region A2 are shown as a first partial cross section A1yz and a second partial cross section A2yz, respectively.

  FIG. 14 shows a spinal region R as an imaging region extracted from the first collection region A1 and the second collection region A2 using a segmentation process or the like on the yz plane. That is, the region of the spine is shown as a spinal section Ryz in the yz plane.

  Then, an orthogonal line V [n] (n = 1, 2,..., N) orthogonal to the coupling line SSyz is set. Of the intersections H [n] and I [n] between the orthogonal line V [n] and the contour of the spinal section Ryz, a distance d to a point far from the orthogonal line V [n] is obtained. Then, the mean square difference is obtained for N distances d. In addition, what is necessary is just to exclude from the calculation part of the distance d about the part through which the joint cross section SSyz passes the spine cross section Ryz.

  As described above, the coupling section setting unit 44 obtains the mean square difference using the coupling line SSyz. Similarly, in the connection cross section setting method shown in FIGS. 8 and 10, the connection cross section setting means 44 determines the mean square difference. Then, the combined cross-section setting unit 44 compares the three mean square differences and selects a combined cross-section setting method in the case of the smallest mean square difference, and the combining target image generating unit 45 selects the combined cross-section in that case. Are generated and supplied to the combined image generating means 46.

(Second modification)
The combined cross-section setting means 44 shown in FIG. 2 selects a combined cross-section setting method for each part to be combined when three or more cross-sectional images that do not intersect are to be combined.

  FIG. 15 is a diagram for explaining a method of selecting an appropriate setting method of the coupling cross section for each part to be coupled. The upper part of FIG. 15 where the joining process is performed is generated by using the second method for setting the joining cross section described with reference to FIGS. 9A and 9B. The lower part of FIG. 15 where the joining process is performed is generated by using the third method for setting the joining cross section described with reference to FIGS. 10 (A) and 10 (B).

  FIG. 15 shows the first cross section S1, the second cross section S2, and the third cross section S3 that do not intersect, the first collection area A1 to which the first cross section S1 belongs, the second collection area A2 to which the second cross section S2 belongs, The third collection region A3 to which the three cross sections S3 belong is shown.

  Further, in the upper part of FIG. 15 where the joining process is performed, the second method for setting the joining cross section described with reference to FIGS. 9A and 9B is selected. Accordingly, when the second setting method of the coupling cross section described with reference to FIGS. 9A and 9B is selected also for the lower part of FIG. 15, the second setting method of the coupling cross section is selected. It is possible that the coupling cross section set by (1) may deviate from the region of the spine as the imaging region.

  Therefore, when three or more cross-sectional images that do not intersect each other are to be combined, an appropriate setting method for the combined cross-section is selected for each portion to be combined. For example, unlike the portion for performing the upper joint processing in FIG. 15 in the portion for performing the lower joint processing in FIG. 15, the third method for setting the joint cross section described with reference to FIGS. Is selected.

(Third Modification)
The coupling section setting means 44 shown in FIG. 2 may be one manually selected from the coupling section setting methods described with reference to FIGS. 8 to 10.

  FIGS. 16A to 16D are diagrams for explaining a method of selecting an appropriate method from a plurality of setting methods of the coupling cross section.

  FIG. 16A is displayed via the display unit 33 (shown in FIG. 2), and the first cross section S1 and the second cross section S2 that are not intersected as shown in FIG. 3 and the first collection area A1 to which the first cross section S1 belongs. And the second collection region A2 to which the second cross section S2 belongs. In this case, intersecting lines C and D (straight lines extending in the X direction) between the first cross section S1 and the second cross section S2 and the overlapping area A12 of the first collection areas A1 and A2 are also displayed. When the cursor on the screen is aligned with the intersection line C via the input unit 32, as shown in FIG. 16 (B), three new sections (shown in the figure) set by the setting method of FIGS. (Dashed line) is displayed.

  Here, the three new cross sections shown in FIGS. 16B and 16C are changed from the left to the new cross section based on the third setting method (shown in FIG. 10) and the second setting method (shown in FIG. 9). A new cross section based on the first setting method (shown in FIG. 8). The new section based on the third setting method is based on the intersection line G.

  Further, the cursor on the screen is set to one of the three new sections via the input unit 32 (FIG. 16C), and when the user clicks on one of the three new sections, three cursors are displayed. One of the new cross sections is selected (FIG. 16D).

  FIG. 17 is a diagram showing a display example when the cursor is set to 1 of the three new sections in FIG.

  When the cursor is set to one of the three new sections in FIG. 16C, a combined image shown on the left side of FIG. 17 is generated that is generated using the combined image related to the combined section corresponding to the new section. Is done. Further, in FIG. 16C, when the cursor is switched from one to three of the three new sections, the combined image shown on the left side of FIG. 17 also changes as shown on the right side of FIG.

  16A to 16D, the operator selects an appropriate setting method for the coupling cross section while observing the display of the combined images related to the three coupling cross sections. can do.

  According to the MRI apparatus 10 according to the present embodiment, a combined image in which images are continuous can be generated even when cross sections of a plurality of cross-sectional images that are not on the same plane do not intersect.

(Image processing apparatus according to this embodiment)
FIG. 18 is a schematic diagram illustrating a hardware configuration of the image processing apparatus according to the present embodiment.

  FIG. 18 shows an image processing apparatus 50 according to this embodiment. Note that the image processing apparatus 50 is a network for various devices such as a server for storing and managing medical images and an interpretation terminal for obtaining medical images stored on the server and displaying them on a display means in order to attach to a doctor. It may be provided in a medical image system connected through the network. In this embodiment, an example in which the image processing apparatus 50 alone implements the present invention will be described. However, the entire medical image system implements the present invention by distributing the functions of the image processing apparatus 50 to each component of the medical image system. You may make it do.

  The image processing device 50 includes a control unit 51, an input unit 52, a display unit 53, a communication unit 54, and a storage unit 55.

  The control unit 51 has the same configuration as the control unit 31 shown in FIG. The control unit 51 reads out various control programs stored in the storage unit 55 and performs various calculations, and comprehensively controls processing operations in the units 52 to 55.

  The input unit 52 has the same configuration as the input unit 32 shown in FIG. When the input unit 52 is operated by the operator, the input unit 52 generates an operation signal corresponding to the operation and outputs the operation signal to the control unit 51. Note that the image processing apparatus 50 may include a touch panel in which the input unit 52 is configured integrally with the display in the display unit 53.

  The display unit 53 has the same configuration as the display unit 33 shown in FIG. The display unit 53 displays various operation screens and various display information such as image data on the LCD according to instructions from the control unit 51.

  The communication unit 54 has the same configuration as the communication unit 34 shown in FIG. The communication unit 54 transmits / receives information to / from an external device on the network. For example, the communication unit 54 receives image data obtained by imaging by an image diagnostic apparatus (not shown) from an image diagnostic apparatus, a server (not shown), or the like, or receives image data generated by the image processing apparatus 50 as a server. Or to a radiogram interpretation terminal (not shown) to communicate with an external device.

  The storage unit 55 has the same configuration as the storage unit 35 shown in FIG. The storage unit 55 stores data necessary for execution of each program in addition to the control program used in the control unit 51 and various processing programs such as coupling processing. Further, the storage unit 55 stores image data received from an image diagnostic apparatus, a server (not shown), or the like via the communication unit 54.

  FIG. 19 is a block diagram illustrating functions of the image processing apparatus 50 according to the present embodiment.

  When the control unit 51 executes the program, as illustrated in FIG. 19, the image processing apparatus 50 includes an operation support unit 41, a combined section setting unit 44, a combined target image generating unit 45, a combined image generating unit 46, and an original image. It functions as image acquisition (reading) means 47. In addition, although it demonstrates as the case where the component 41, 44 thru | or 47 of the image processing apparatus 50 is functioned as software, it is a case where a part or all of the component 41, 44 thru | or 47 is provided in the image processing apparatus 50 as a circuit. Also good.

  In FIG. 19, the same members as those shown in FIG.

  The original image acquisition unit 47 acquires, from the storage unit 55, a plurality of cross-sectional images that are original images for a plurality of cross-sections (slices) that are not on the same plane. For example, the original image acquisition unit 47 acquires a first cross-sectional image related to a first cross section that is not on the same plane and a second cross-sectional image related to a second cross section. Then, the original image acquisition unit 47 supplies the acquired cross sections of the first and second cross-sectional images to the combined cross-section setting unit 44.

  Examples of the plurality of cross-sectional images acquired by the original image acquisition unit 47 include an image obtained by an MRI apparatus, an image obtained by an X-ray CT (computed tomography) apparatus, and the like.

  According to the image processing apparatus 50 according to the present embodiment, a combined image in which images are continuous can be generated even when the cross-sections of a plurality of cross-sectional images that are not on the same plane do not intersect.

  Although several embodiments of the present invention have been described above, these embodiments are presented as examples and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 10 MRI apparatus 11 Imaging system 12 Control system 21 Static magnetic field magnet 22 Gradient magnetic field coil 26 Transmission coil 31,51 Control part 35,55 Memory | storage part 41 Operation support means 42 Imaging execution means 43 Original image generation means 44 Coupling cross-section setting means 45 Combined image generation means 46 Combined image generation means 47 Original image acquisition (readout) means 50 Image processing apparatus

Claims (10)

A static magnetic field generator for generating a static magnetic field;
A gradient magnetic field generator for generating a gradient magnetic field;
A transmission coil for applying a high frequency pulse to the subject;
Based on a signal corresponding to the high-frequency pulse, original image generating means for generating a plurality of cross-sectional images not on the same plane;
A combined cross-section setting means for setting a cross-section different from any cross-section of the plurality of cross-sectional images, and setting a combined cross-section based on at least one of the cross-sections of the plurality of cross-sectional images and the different cross-sections;
A joining target image generating means for generating a cross-sectional image related to each cross-section constituting the combined cross-section;
A combined image generating means for generating a combined image by performing a combining process on each cross-sectional image related to the combined cross section;
A magnetic resonance imaging apparatus. Original image acquisition means for acquiring a plurality of cross-sectional images not on the same plane from the storage unit;
A combined cross-section setting means for setting a cross-section different from any cross-section of the plurality of cross-sectional images, and setting a combined cross-section based on at least one of the cross-sections of the plurality of cross-sectional images and the different cross-sections;
A joining target image generating means for generating a cross-sectional image related to each cross-section constituting the combined cross-section;
A combined image generating means for generating a combined image by performing a combining process on each cross-sectional image related to the combined cross section;
An image processing apparatus.   The image processing apparatus according to claim 2, wherein the combined cross-section setting unit sets the combined cross-section when determining that cross sections of the plurality of cross-sectional images do not intersect. The original image acquisition means acquires a first cross-sectional image and a second cross-sectional image as the plurality of cross-sectional images,
The combined cross-section setting means includes a first acquisition region to which a cross-section of the first cross-sectional image belongs, an overlapping region of a second acquisition region to which a cross-section of the second cross-sectional image belongs, and a cross-section of the first cross-sectional image. A first intersection line and a second intersection line between the overlap region and a section of the second slice image are obtained, the different section formed by the first and second intersection lines is set, and the first section The combined cross section formed by the first partial cross section based on the cross section of the image and the first intersection line, the different cross section, and the second partial cross section based on the cross section of the second cross section image and the second intersection line. The image processing apparatus according to claim 2, wherein the image processing apparatus is set. The original image acquisition means acquires a first cross-sectional image and a second cross-sectional image as the plurality of cross-sectional images,
The combined cross-section setting means obtains a terminal end line of the cross section of the first cross-sectional image, and calculates an intersection line between a plane where the cross-section of the first cross-sectional image exists and a cross section of the first cross-sectional image among the plurality of cross-sectional images. Determining and setting the different cross-sections formed by the terminal line and the intersection line, the cross-section of the first cross-sectional image, the different cross-section, and the second portion based on the cross-section of the second cross-sectional image and the cross line The image processing apparatus according to claim 2, wherein the combined cross section formed by a cross section is set. The original image acquisition means acquires a first cross-sectional image and a second cross-sectional image as the plurality of cross-sectional images,
The combined cross-section setting means sets another cross-section that belongs to the second acquisition region to which the cross-section of the second cross-sectional image belongs and intersects the cross-section of the first cross-sectional image as the different cross section, and the cross section of the first cross-sectional image The image processing apparatus according to claim 2, wherein the combined cross section formed by the different cross sections is set.   The coupling section setting means sets a plurality of coupling sections by the plurality of setting methods and sets one coupling section from the plurality of coupling sections when there are a plurality of setting methods of the coupling sections. The image processing apparatus according to claim 2.   The image according to claim 7, wherein the combined cross-section setting unit sets one combined cross-section from the plurality of combined cross-sections based on a region of an imaging part included in a plurality of combined images related to the plurality of combined cross-sections. Processing equipment.   The image processing apparatus according to claim 7, wherein the coupling section setting unit sets one of the coupling sections according to an instruction from an input unit from the plurality of coupling sections.   The combined cross-section setting means sets the combined cross-section for each portion to be combined when the original image generating means generates three or more image cross-sectional images as the plurality of cross-sectional images. The image processing apparatus described.

Images