JP2017189241A - Magnetic resonance imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a magnetic resonance imaging apparatus capable of tracking a specific region of a subject and performing noise cancellation and sound collection.SOLUTION: A magnetic resonance imaging apparatus includes: a sequence control part for controlling execution of a series of protocol groups related to the same subject including a first protocol for acquiring a first image by imaging the subject, and a second protocol executed after the first protocol for acquiring a second image; a display part for acquiring the first image; an input part for receiving input of a feature region of the subject on the first image displayed in the display part before the execution of the second protocol; a sound acquisition part for acquiring a noise canceling sound transmitted to the feature region based on at least one of a pulse sequence and position information on the feature region; and a speaker 111 for transmitting the noise canceling sound to the feature region during the execution of the second protocol.SELECTED DRAWING: Figure 1

Description

  Embodiments described herein relate generally to a magnetic resonance imaging apparatus.

  Magnetic Resonance Imaging (MRI) magnetically excites a subject's nuclear spin placed in a static magnetic field with a Larmor frequency RF (Radio Frequency) pulse, and is generated along with this excitation. This is an imaging method for generating an image from magnetic resonance signal data.

  Incidentally, the subject and the operator may communicate through conversation or the like during the examination. However, during the inspection by the MRI apparatus, air vibrations are generated due to vibrations of the coil unit or the like in the MRI apparatus, and noise is generated. This noise may interfere with communication between the subject and the operator. Taking such a case as an example, it is desired to improve the acoustic environment around the subject in the MRI apparatus.

JP 2005-152420 A

  The problem to be solved by the present invention is to provide a magnetic resonance imaging apparatus capable of improving the acoustic environment around the subject in the MRI apparatus.

  The magnetic resonance imaging apparatus according to the embodiment executes a first protocol for acquiring a first image by imaging a subject, and a second protocol that is executed after the first protocol and acquires a second image. Including a sequence control unit that controls execution of a series of protocol groups relating to the same subject, a display unit that acquires a first image, and a first unit that is displayed on the display unit prior to execution of the second protocol. Audio acquisition for acquiring a noise canceling sound to be transmitted to a feature part based on at least one of an input unit that receives an input of a feature part of the subject on the image and a pulse sequence and position information of the feature part And a speaker for transmitting a noise canceling sound to the characteristic part during execution of the second protocol.

1 is a block diagram showing a schematic configuration of a magnetic resonance imaging apparatus according to a first embodiment. The figure which shows an example of the attachment position of the speaker which concerns on 1st Embodiment. The figure which shows an example of the attachment position of the speaker in the head coil which concerns on 1st Embodiment. The figure which shows an example of the positioning image of the auditory part which concerns on 1st Embodiment. The figure which shows an example of the body movement correction | amendment which concerns on 1st Embodiment. The figure which shows an example of the imaging sequence for the body movement correction | amendment which concerns on 1st Embodiment. The flowchart which shows the flow of a series of processes of 1st Embodiment. The flowchart which shows the flow of the noise cancellation in 1st Embodiment. The figure which shows an example of the noise canceling method in the tracking position of the auditory part which concerns on 1st Embodiment. The block diagram which shows schematic structure of the magnetic resonance imaging apparatus which concerns on 2nd Embodiment. The figure which shows an example of the attachment position of the microphone which concerns on 2nd Embodiment. The flowchart which shows the flow of a series of processes which concern on 2nd Embodiment. The figure which shows an example of the positioning image of the vocalization part which concerns on 2nd Embodiment. The flowchart which shows the flow of extraction of the voice of the subject by the array microphone which concerns on 2nd Embodiment. The block diagram which shows schematic structure of the magnetic resonance imaging apparatus which concerns on 3rd Embodiment. The figure which shows an example of the attachment position of the speaker and microphone which concern on 3rd Embodiment. The block diagram which shows the structure of the processing circuit which concerns on 4th Embodiment.

  Hereinafter, a magnetic resonance imaging apparatus (hereinafter referred to as an MRI apparatus 100: Magnetic Resonance Imaging) according to an embodiment will be described with reference to the drawings. Note that the embodiments are not limited to the following embodiments. The contents described in each embodiment can be applied in the same manner to other embodiments in principle.

(First embodiment)
The MRI apparatus 100 often performs a series of scan groups in one examination. This “scan” is to acquire a desired MR signal by executing a pulse sequence in which imaging parameters such as TR (Replication Time), TE (Echo Time), and FA (Flip Angle) are set. is there. A unit that divides a series of scan groups executed in one examination for convenience is called a “protocol”. Typically, one scan corresponds to one protocol, but a single protocol may include a plurality of scans. Protocol groups corresponding to a series of scan groups can be classified into protocols corresponding to “imaging scans” for collecting diagnostic images (also referred to as “imaging protocols”) and protocols other than imaging scans. Protocols other than imaging scans include, for example, sensitivity map scans that collect RF coil reception sensitivity maps, shimming scans that collect data for uniform correction of static magnetic field strength, and labeling and imaging regions for imaging scans. A locator scan that collects a positioning image for setting the value is applicable. In addition, a plurality of “imaging scans” may be included in one examination. The “imaging scan” in the present embodiment corresponds to, for example, a functional image scan or a morphological image scan during an fMRI (functional magnetic resonance imaging) examination. In the imaging scan according to the present embodiment, it is assumed that a plurality of three-dimensional MR data is acquired on the assumption that an fMRI functional image is scanned.

  In the embodiment described in detail below, a position (hereinafter referred to as a characteristic part) that is a focal point of the noise canceling sound is positioned with respect to the auditory part of the subject P. Therefore, of the series of protocols described above, a protocol for positioning a characteristic part is referred to as a “first protocol” for convenience. When the feature portion is positioned, a noise canceling sound is transmitted to the feature portion in a protocol executed after the first protocol. Protocols executed after the first protocol for performing noise canceling are collectively referred to as “second protocol” for convenience. Any of the above protocols may be used as the “first protocol” and the “second protocol”, but the protocol that is performed prior to the imaging scan is selected as the “first protocol”. It is desirable that This is because the noise canceling sound transmission start timing can be advanced by positioning the characteristic part in the initial stage of the inspection.

  In the following embodiment, the description will be given on the assumption that the locator scan is set as the second scan and the protocol after the locator scan is set as the first protocol prior to the imaging scan. To do.

<Constituent Elements> FIG. 1 is a block diagram showing a configuration of the MRI apparatus 100 according to the first embodiment. As shown in FIG. 1, the MRI apparatus 100 includes a static magnetic field magnet 101, a static magnetic field power supply 102, a gradient magnetic field coil 103, a gradient magnetic field power supply 104, a bed apparatus 105, a processing circuit 106, and a transmission coil 107. A transmission circuit 108, a reception coil 109, a reception circuit 110, a speaker 111, a processing circuit 120, an input device 131, a display device 132, a storage circuit 133, a processing circuit 134, and a processing circuit 135. Including. The MRI apparatus 100 does not include a subject P (for example, a human body). Moreover, the structure shown in FIG. 1 is only an example. For example, the components in the processing circuit 120, the processing circuit 134, and the processing circuit 135 may be appropriately integrated or separated. For example, the processing circuit 120. The present embodiment may be implemented by providing one processing circuit having both functions of the processing circuit 134 and the processing circuit 135. Conversely, the processing circuit 135 may be divided into three independent processing circuits, and each may be configured to execute the system control function 135a, the image generation function 135b, and the feature part tracking function 135c.

  The static magnetic field magnet 101 is a magnet formed in a hollow, substantially cylindrical shape (including a magnet whose cross section perpendicular to the central axis of the cylinder is elliptical), and generates a static magnetic field in the internal space. In the following embodiments, a hollow, substantially cylindrical shape includes an elliptical cross section perpendicular to the central axis of the cylinder. The static magnetic field magnet 101 is a superconducting magnet, for example, and is excited by receiving a current supplied from the static magnetic field power source 102. The static magnetic field power supply 102 is a power supply device that supplies a current to the static magnetic field magnet 101. The static magnetic field magnet 101 may be a permanent magnet. In this case, the MRI apparatus 100 may not include the static magnetic field power supply 102. In addition, the static magnetic field power source 102 may be provided separately from the MRI apparatus 100.

  The gradient magnetic field coil 103 is a coil formed in a hollow, substantially cylindrical shape, and is disposed inside the static magnetic field magnet 101. The gradient coil 103 is formed by combining three coils corresponding to the 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 104. Thus, a gradient magnetic field whose magnetic field intensity varies along the X, Y, and Z axes is generated. The gradient magnetic fields of the X, Y, and Z axes generated by the gradient magnetic field coil 103 are, for example, a slice encoding gradient magnetic field Gs, a phase encoding gradient magnetic field Ge, and a readout gradient magnetic field Gr. The gradient magnetic field power supply 104 is a power supply device that supplies a current to the gradient magnetic field coil 103.

  The couch device 105 includes a top plate 105a on which the subject P is placed, and a base and a couch drive device (not shown). The base is a housing having a motor or an actuator that can move the top plate 105a in the vertical direction (direction perpendicular to the body axis direction of the subject P) by the bed driving device. The couch driving device is a motor or an actuator that inserts and removes the top plate 105 a on which the subject P is placed into the imaging port of the MRI apparatus 100. The top plate 105a is a plate-like member on which the subject P that can be moved in the body axis direction of the subject P and the direction orthogonal to the body axis direction by the bed driving device is placed.

  The processing circuit 106 (processing unit) has a bed control function 106a (bed control unit). For example, the processing circuit 106 is realized by a processor. The couch control function 106 a is connected to the couch device 105, and controls the operation of the couch device 105 by outputting a control electric signal to the couch device 105. For example, the bed control function 106a receives an instruction from the operator to move the top plate 105a in the longitudinal direction, the vertical direction, or the horizontal direction via the input device 131, and moves the top plate 105a according to the received instruction signal. The drive mechanism of the top board 105a which the bed apparatus 105 has is operated.

  The transmission coil 107 is a coil formed in a hollow, substantially cylindrical shape, is disposed inside the gradient magnetic field coil 103, receives an RF pulse from the transmission circuit 108, and generates a high-frequency magnetic field. The transmission circuit 108 supplies an RF pulse corresponding to the Larmor frequency determined by the type of target atom and the magnetic field strength to the transmission coil.

  The receiving coil 109 is a coil that is disposed inside the gradient magnetic field coil 103 and receives a magnetic resonance signal (hereinafter referred to as an MR signal) emitted from the subject P due to the influence of a high-frequency magnetic field. When receiving the MR signal, the receiving coil 109 outputs the received MR signal to the receiving circuit 110.

  Note that the configurations of the transmission coil 107 and the reception coil 109 described above are merely examples. What is necessary is just to comprise by combining one or more among the coil provided only with the transmission function, the coil provided only with the reception function, or the coil provided with the transmission / reception function.

  The receiving circuit 110 (receiving unit) detects the MR signal output from the receiving coil 109, and generates MR data from the detected MR signal. Specifically, the receiving circuit 110 generates MR data by digitally converting the MR signal output from the receiving coil 109.

  The speaker 111 is a device that generates sound by converting an electrical signal into physical vibration. The speaker 111 is disposed in an imaging port inside the transmission coil 107, transmits a noise canceling sound for reducing noise generated by the MRI apparatus 100, and noise perceived by the subject P in the imaging port during MR imaging. It has the function to reduce. The sound wave of the noise canceling sound has a phase opposite to that of the noise sound wave generated by the MRI apparatus 100. In the vicinity of the ear of the subject P, the sound wave of the noise generated by the MRI apparatus 100 and the sound wave of the noise canceling sound sent from the speaker 111 are substantially perceived by the subject P. The volume of noise will be reduced. A signal corresponding to the noise canceling sound transmitted by the speaker 111 is acquired by the sound acquisition function 134a. Since the speaker 111 in this embodiment is used in the MRI apparatus 100, it is preferable that the speaker 111 does not include a magnetic material. For example, instead of a magnetic material normally used in a speaker vibrator, PZT (lead zirconate titanate) It is preferable to use a piezoelectric speaker using a piezoelectric vibrator such as The speaker 111 is connected to a processing circuit 134 to be described later by wiring or the like, and executes transmission of a noise canceling sound generated by the sound acquisition function 134a of the processing circuit 134.

  FIG. 2 is a diagram illustrating an example of an attachment position of the speaker 111 in the MRI apparatus 100. The speaker 111 is arranged on the circumference over a plurality of locations in the imaging port of the MRI apparatus 100. Further, the arrangement of the speakers 111 is not limited to the arrangement shown in FIG. 2, and the speakers 111 may have a configuration that is attached to the top plate 105 a. Further, the speaker 111 may be mounted in a head coil 109b which is a form of the receiving coil 109.

  Further, as shown in FIG. 2, apart from the speaker 111 for sending a noise canceling sound to the subject P, a speaker 111b is disposed on the top plate 105a, for example. Similarly to the speaker 111, the speaker 111b is a device that generates sound by converting an electrical signal into a physical signal. The speaker 111b has a function of transmitting sound from an operator or the like to the subject P. The speaker 111b may send music or the like to the subject P. Thereby, the effect of relieving the tension of the subject P during the examination can be expected. Further, the speaker 111 may be disposed not in the imaging opening of the MRI apparatus 100 but in the reception coil 109.

  FIG. 3 is a diagram illustrating an example of an attachment position of the speaker 111 in the head coil 109b. For example, a plurality of speakers 111 are arranged inside the head coil 109b. The mounting position of the speaker 111 in the head coil 109b is not limited to the arrangement shown in FIG. For example, a plurality of speakers 111 may be arranged in the vicinity of the ear of the subject P while the subject P is attached to the head coil 109b. The speaker 111 in the head coil 109b is connected to the processing circuit 134 by a wiring 141. Further, the above-described speaker 111b may also be disposed in the head coil 109b instead of the top plate 105a.

  The processing circuit 120 (processing unit) has a sequence control function 120a (sequence control unit). For example, the processing circuit 120 is realized by a processor. The sequence control function 120a executes various pulse sequences. Specifically, the sequence control function 120a reads the sequence execution data output from the processing circuit 135 and drives the gradient magnetic field power source 104, the transmission circuit 108, and the reception circuit 110 to execute various pulse sequences.

  Here, the sequence execution data is information defining a pulse sequence indicating a procedure for collecting MR data. Specifically, the sequence execution data includes the timing at which the gradient magnetic field power supply 104 supplies current to the gradient coil 103 and the strength of the supplied current, the strength of the RF pulse current supplied to the transmission coil 107 by the transmission circuit 108, and the like. This is information defining supply timing, detection timing at which the receiving circuit 110 detects an MR signal, and the like.

  The sequence control function 120a (sequence control unit) receives MR signals from the reception circuit 110 as a result of executing various pulse sequences, and stores the received MR signals in the storage circuit 133. A set of MR signals received by the sequence control function 120a is transferred to the image generation function 135b of the processing circuit 135.

  The input device 131 (input unit) receives various instructions and information input from the operator. The input device 131 is, for example, a pointing device such as a mouse or a trackball, a selection device such as a mode change switch, or an input device such as a keyboard.

  The display device 132 (display unit) is generated by a GUI (Graphical User Interface) for receiving an input of imaging conditions under the control of the system control function 135a of the processing circuit 135 and the image generation function 135b of the processing circuit 135. Display images and so on. The display device 132 is configured by a liquid crystal display, for example.

  The storage circuit 133 (storage unit) stores various data. For example, the storage circuit 133 stores MR signals and MR data for each subject P. For example, the storage circuit 133 is realized by a semiconductor memory device such as a RAM (Random Access Memory) and a flash memory, a hard disk, an optical disk, and the like.

  The processing circuit 134 (processing unit) has an audio acquisition function 134a (audio acquisition unit). For example, the processing circuit 134 is realized by a processor. First, the voice acquisition function 134a reads the sequence execution data output from the processing circuit 135, and reads the noise canceling sound corresponding to the noise generated by the MRI apparatus 100 when executing various pulse sequences from the storage circuit 133. At the same time as the execution of the pulse sequence is started, the noise canceling sound is output toward the auditory part of the subject P via the speaker 111. The noise canceling sound is a sound having the same frequency, the same amplitude, and an opposite phase as the target noise, and the noise canceling sound corresponding to each pulse sequence is stored in the storage circuit 133 in advance. The auditory part of the subject P can be designated on the MR image by an operator from organs responsible for hearing such as pinna, ear canal, eardrum, middle ear, and the like. The auditory part is a position that becomes the focal point of the noise canceling sound transmitted from each speaker 111, and the noise and the noise canceling sound cancel each other out at this position. The operator designates an appropriate position each time depending on the individual difference of the subject P, the imaging part of the MR image to be captured, and the acquired cross section. In the present embodiment, the noise canceling sound corresponding to various pulse sequences is read from the storage circuit 133 and output to the subject P via the speaker 111. However, for example, when the scan parameter changes, etc. The noise canceling sound may be adjusted appropriately. The voice acquisition function 134a reads the position of the auditory part after body movement calculated by the feature part tracking function 135c described later, and adjusts the phase of the noise canceling sound. The noise canceling sound adjusted according to the position after the body movement is output via the speaker 111. Thereby, the phase of the noise canceling sound is adjusted according to the position after the body movement, and the noise canceling sound can be transmitted to the auditory part after the body movement. Further, the body movement in the present embodiment is assumed to be a minute body movement of the subject P accompanying breathing or the like, or a body movement caused by nodding or swinging the subject P.

  The processing circuit 135 (processing unit) includes a system control function 135a, an image generation function 135b, and a feature part tracking function 135c. For example, the processing circuit 135 is realized by a processor.

  The system control function 135a (system control unit) performs overall control of the MRI apparatus 100 by controlling each component included in the MRI apparatus 100. For example, the system control function 135a receives input of various parameters related to the pulse sequence from the operator via the input device 131, reads the received parameters, and generates sequence execution data. Then, the system control function 135a executes various pulse sequences by transmitting the generated sequence execution data to the processing circuit 120. In addition, the system control function 135 a reads the MR image requested by the operator from the storage circuit 133 and outputs the read image to the display device 132.

  The image generation function 135b (image generation unit) generates an MR image from the MR signal stored in the storage circuit 133. Specifically, the image generation function 135b reads the MR signal stored in the storage circuit 133 by the sequence control function 120a, and performs post-processing, that is, reconstruction processing such as Fourier transform, on the read MR signal. Generate. The image generation function 135 b stores the generated MR image in the storage circuit 133.

  The image generation function 135b is an example of a first image acquisition unit that acquires an image for designating a feature part to be described later and a second image acquisition unit that acquires an image for correcting misalignment.

  The feature part follow-up function 135c, for example, displays the spatial position information of the feature part such as the auditory part designated by the operator on the MR image (first image) by the operator during the execution of the first protocol. It has a function to update and follow the MR image (second image) during execution of the protocol. More specifically, first, the feature part tracking function 135 c reads the first image from the storage circuit 133 and displays it on the display device 132. Next, the feature part tracking function 135c receives the position information of the feature part designated by the operator with reference to the display device 132 via the input device 131. The first image displayed at this time may be an MR image in which a part including a characteristic part is captured. For example, an MPR image generated by performing reconstruction processing from three-dimensional MR data of the head of the subject P (Multi-Planer-Reconstruction), a multi-slice MR image that is a set of a plurality of MR images, and the like. The feature part tracking function 135c receives the position information of the feature part, and performs tracking of the position after movement due to body movement or the like of the subject P during imaging of the second image. In the following description, a case where a characteristic part is specified using an MPR image acquired at the time of locator scanning will be described as an example. The feature part tracking function 135c is an example of a calculation unit that calculates a positional shift of the feature part before and after body movement. The first image is not limited to the one obtained by the locator scan, and an image obtained by executing any protocol may be used.

  FIG. 4 is a diagram illustrating an example of a display screen of the display device 132 for setting the auditory region. In FIG. 4, as an example of the first image, a coronal plane image including an organ such as the inner ear is displayed in the MPR image generated from the three-dimensional MR data of the head. For example, the operator refers to an image of the coronal surface of the head of the subject P via the input device 131 and sets the auditory part of the subject P. When the auditory part is set, spatial coordinate information of the auditory part is calculated by the feature part tracking function 135c. The calculated spatial coordinate information of the auditory part is stored in the storage circuit 133. For example, as shown in FIG. 4, the auditory part is selected by the operator from the auricle 11, the external auditory canal 12, the eardrum 13, the middle ear 14, and the like. As described above, the auditory part does not necessarily designate each organ itself of the subject P. For example, as shown in FIG. It may be specified above.

  The feature part follow-up function 135c follows the position after movement due to body movement of the subject P during MR image capturing during execution of the second protocol after positioning of the feature part designated by the operator. In the first embodiment, the feature part tracking function 135c detects the body movement of the subject P, estimates the movement of the auditory part in real time, and transmits the noise canceling sound to the auditory part after the movement. Deviation correction is performed. As described above, the second protocol according to the present embodiment is described assuming an imaging scan for acquiring an fMRI functional image. Therefore, the second protocol will be described assuming that a plurality of three-dimensional MR data having different time phases are acquired. However, as described above, any protocol can be applied to the second protocol.

  FIG. 5 is a diagram illustrating an example of a method of following the auditory part N in the first embodiment. At the time of acquiring each second image, the spatial position before and after the body movement of the auditory part designated by the operator is calculated, and the spatial position of the auditory part before the body movement is calculated from the spatial position of the auditory part after the body movement. The auditory part is calculated by calculating the difference. Here, since the head including the auditory part is a rigid body (rigid body part), deformation can be ignored. Therefore, it is possible to calculate the difference between the position of the head before and after the movement by acquiring three-dimensional MR data of the imaging region including the head as the second image a plurality of times and comparing the respective three-dimensional MR data. Is possible.

  More specifically, the three-dimensional MR data 31 of the subject P is collected when the first three-dimensional MR data is acquired (Volume 1) in the second protocol. At this time, the spatial coordinates (x, y, z) of the auditory part N in the three-dimensional MR data 31 are calculated. Next, the 3D MR data 32 of the subject P is collected at the time of the second acquisition of 3D MR data (Volume 2). In addition, the subject P moves between Volume1 and Volume2, and the spatial coordinates of the auditory part N change from coordinates (x, y, z) to coordinates (x + x ′, y + y ′, z + z ′). The feature part tracking function 135c reads the changed spatial coordinate difference and calculates the positional deviation amount (x ′, y ′, z ′) of the auditory part N. Similarly, three-dimensional MR data 33 of the subject P is collected at the time of the third MR data acquisition (Volume 3). Similarly, the spatial coordinates of the auditory part N change from coordinates (x, y, z) to coordinates (x + x ′ + x ″, y + y ′ + y ″, z + z ′ + z ″) between Volume 3 and Volume 2. . At this time, the positional deviation amount of the auditory part N may be calculated by calculating a difference between the three-dimensional MR data 33 and the three-dimensional MR data 32 having the closest photographing time. Alternatively, the difference between the three-dimensional MR data 31 photographed may be calculated and calculated. In this way, the position of the auditory part N can be tracked by updating the spatial coordinates of the auditory part N every time MR data is acquired. Here, the case where a plurality of three-dimensional MR data is acquired has been described. However, the acquisition of the three-dimensional MR data described in the present embodiment may be performed in place of acquisition of a slice image of the subject P. good. In addition, when a plurality of protocols are executed in succession, the spatial coordinates of the auditory part N are also updated at the timing of shifting from the n-th protocol (Protocoln) to the (n + 1) -th protocol (Protocol (n + 1)). Thus, the position of the auditory part N may be further followed. For example, if the feature part has already been positioned using the protocol before the locator scan, noise canceling is performed during the locator scan execution, and the position of the feature part is further updated when the next shimming scan is executed. Subsequently, noise canceling may be performed on the same auditory part N.

  In FIG. 5, the auditory part N is described as being included in the imaging region when the second protocol is executed, but the auditory part N is not necessarily included in the imaging region. For example, three-dimensional MR data of an arbitrary imaging region in the head can be acquired a plurality of times in the same manner as described above, and the difference in head position can be calculated by comparing the three-dimensional MR data. The feature part following function 135c can read the difference as the movement amount of the auditory part N. For example, when the eardrum 13 is designated by the operator as the auditory part in the first protocol and the head above the eardrum 13 and does not include the eardrum 13 is imaged as the imaging region in the second protocol, The imaging region in this protocol does not include the eardrum. At this time, the feature part following function 135c can follow the movement of the eardrum 13 which is an auditory part by calculating the movement amount of the head. Further, the MR image used for calculating the positional displacement after the body movement acquired when the second protocol described above is executed is an example of the second image.

  In addition, the tracking method in the present embodiment is not limited to the above-described method. A reference scan is performed before acquiring MR data during execution of the second protocol, and a reference scan before acquiring each three-dimensional MR data. From this, it is also possible to detect the body movement by calculating the amount of movement of the characteristic part.

  FIG. 6 is a diagram illustrating the execution timing of the reference scan during the execution of the second protocol. The reference can is executed before acquiring MR data. For example, it is possible to calculate the positional shift of the auditory part due to body movement by calculating the difference between the spatial positions of the auditory part during the first reference scan and the second reference scan. The reference scan does not necessarily have to be executed before acquiring MR data, and may be executed a predetermined number of times. The reference scan is an imaging method in which MR images with imaging conditions that do not interfere with the T1 relaxation time are collected in a short time. Examples of the reference scan include 2D single shot spiral scan, low flip angle scan, and orthogonal three-section scan.

<Operation>
FIG. 7 is a flowchart showing a processing procedure according to the first embodiment. In the present embodiment, as described at the beginning, the first protocol is described as an imaging scan assuming a locator scan and the second protocol is assumed to be an fMRI functional image scan.

  First, the system control function 135a accepts an imaging condition input from an operator on the GUI via the input device 131, and generates sequence information according to the accepted imaging condition (step S101).

  Next, the receiving coil 109 is mounted on the subject P, the subject P is placed on the top plate 105a of the bed apparatus 105, and the receiving coil 109 is electrically connected to the MRI apparatus 100 (step S102). For example, the receiving coil 109 is a head coil having a plurality of coil elements.

  Next, the couch control function 106a moves the couch device 105 (step S103). Specifically, when the couch control function 106a moves the top board 105a to a predetermined position, light from a projector (not shown) is applied to the subject P. The operator inputs the designation of the position of the imaging region via the input device 131 at the timing when the light from the projector is applied to the imaging region (for example, the head). Thereby, the couch control function 106a moves the top 105a so that the designated imaging part is positioned at the center of the magnetic field.

  Subsequently, the sequence control function 120a executes a locator scan for determining an imaging region during the imaging scan. At this time, since the locator scan is executed as the first protocol, MR data in a range including the auditory part which is a characteristic part is collected (step S104).

  Next, the image generation function 135b generates an MR image using the MR data collected in step S104 (step S105).

  Next, the system control function 135a displays on the display device 132 an MR image for allowing the operator to designate a hearing part. The operator refers to the MR image displayed on the display device 132 and designates the auditory part to be followed by the GUI (step S106).

  Next, the sequence control function 120a executes the second protocol. During the execution of the second protocol, the feature part tracking function 135c detects the positional deviation of the head. From the positional deviation amount of the head, the characteristic part tracking function 135c estimates the position after the movement of the auditory part. The voice acquisition function 134a reads the position of the auditory part after the movement, calculates the distance between the auditory part and each speaker 111, adjusts the sending position of the noise canceling sound, and sends it (step S107).

  The above step S107 will be described in detail with reference to the flowchart of FIG. First, the sound acquisition function 134a reads the imaging conditions set in step S101, and selects a desired pulse sequence (step S81). The voice acquisition function 134a reads the noise canceling sound to be transmitted from the storage circuit 133 in accordance with the read pulse sequence (step S82). Simultaneously with the execution of the second protocol, the voice acquisition function 134a sends the noise canceling sound read from the storage circuit 133 toward the auditory site of the subject P via the speaker 111 (step S83). During the execution of the second protocol, the feature part tracking function 135c estimates the movement of the auditory part due to the body movement of the subject P designated in S106 in real time from the movement amount of the head, for example, Misalignment correction for transmitting noise canceling sound to the auditory part is performed (step S84). The voice acquisition function 134a reads the position of the auditory part after body movement calculated by the feature part tracking function 135c, adjusts the phase of the noise canceling sound, and performs noise corresponding to the position of the auditory part after body movement. A canceling sound is output via the speaker 111. When the pulse sequence is switched, the noise canceling sound corresponding to the pulse sequence after switching is acquired again from the storage circuit 133, and the noise canceling sound is transmitted (step S85). Next, it is determined by the sequence control function 120a whether or not the imaging sequence is completed (step S86). When the imaging sequence is completed, transmission of the noise canceling sound is ended by the sound acquisition function 134a (step S87). If the imaging sequence has not ended, the process returns to S83 and another imaging protocol is executed.

  Thereafter, the image generation function 135b generates an image from the MR data collected by the sequence control function 120a (step S108), and displays the generated MR image on the display device 132. (Step S109)

  In the present embodiment, the description has been made on the assumption that the feature portion is positioned on the MR image acquired in the locator scan, but the embodiment is not limited to the above description. For example, an MR image acquired at the time of an imaging scan may be used for positioning of the characteristic part. More specifically, for example, at the time of fMRI, the characteristic part may be positioned at the time of imaging scan of the morphological image before acquisition of the functional image.

  FIG. 9 is a diagram illustrating an example of a method of transmitting a noise canceling sound during body movement in the first embodiment. FIG. 9A is a schematic diagram showing the head of the subject P at a position before body movement. When the eardrum 13 is set as the auditory region N, the noise canceling sound in the auditory region N is transmitted from each speaker 111 so as to reduce noise generated by the MRI apparatus 100 as shown in FIG. The noise canceling sound is acquired from the storage circuit 133. The adjusted noise canceling sound is superimposed with the noise canceling sound from each speaker 111 so that the noise canceling effect is maximized in the auditory part N. Next, as shown in FIG. 9B, when the auditory part N is moved due to body movement, the characteristic part tracking function 135c reads the positional shift due to the body movement and moves the auditory part N after the body movement. Estimate the position. When the position of the auditory part N after the body movement is estimated, the voice acquisition function 134a again adjusts the noise canceling sound transmitted through the speaker 111, and outputs the noise canceling sound to the auditory part N after the body movement. Send it out. As described above, according to the first embodiment, on the MR image acquired during execution of an arbitrary protocol, the imaging region and the auditory part are designated, and the body part of the designated auditory part is moved. Since the position can be calculated automatically, it is possible to follow the noise canceling position even after body movement.

(Second Embodiment)
In the second embodiment, as a characteristic part of the subject P, the voice of the subject P is selectively picked up by voice collection technology such as an array microphone, following the uttered part such as the mouth, and the operator in the operation room. A case where the voice of the subject P is output from the external audio output device 140 in the operation room will be described with reference to FIGS. 10 to 14.

<Components>
FIG. 10 is a block diagram showing a configuration of the MRI apparatus 100 according to the second embodiment. The MRI apparatus 100 of the second embodiment has a configuration including an array microphone 112 and an external audio output apparatus 140 instead of the speaker 111 of the first embodiment.

  The array microphone 112 is a device that converts a sound such as a voice of the subject P into an electrical signal. The array microphone 112 in the second embodiment picks up the voice of the subject P and converts it into an electrical signal.

  FIG. 11 is a diagram illustrating an example of an attachment position of the array microphone 112 in the MRI apparatus 100. As with the mounting position of the speaker 111 in the first embodiment, a plurality of mounting positions of the array microphone 112 are arranged at both ends of the imaging port in the major axis direction in the imaging port of the MRI apparatus 100. good. Further, similarly to the first embodiment, a plurality of array microphones 112 may be arranged diagonally in the imaging port. Further, the array microphone 112 may be arranged in the head coil 109b, and the arrangement of the array microphone 112 is not limited to the arrangement shown in FIG.

  The external audio output device 140 (external audio output unit) is configured by a speaker or the like normally disposed in the operation room, and has a function of transmitting the voice of the subject P in the MRI apparatus 100 to the operator.

  Further, the processing circuit 134 has a sound adjustment function 134b instead of the sound acquisition function 134a in the first embodiment. The voice adjustment function 134 b (voice adjustment unit) has a function of selectively extracting only the voice of the subject P from the voice of the subject P collected by the array microphone 112 and noise generated by the MRI apparatus 100. More specifically, the voice adjustment function 134b reads the position information of the uttered part grasped by the characteristic part tracking function 135c. As an example of the uttered part of the subject P, there are a lip peripheral area 51, a lip 52, a tongue 53, a vocal cord 54, and the like shown in FIG. The sound adjustment function 134b adjusts the sound transmitted to the operator from the sound acquired by each array microphone 112 and the position information of the uttered part. Specifically, the position information of the utterance part is grasped by the feature part tracking function 135c, and the relative distance between the utterance part and each array microphone 112 is calculated. Only the voice generated from the utterance part of the subject P is emphasized by synthesizing after correcting the phase of the audio signal acquired by each array microphone 112 by using the relative distance between each array microphone 112 and the utterance part. Can be taken out. Further, since the feature part tracking function 135c follows the body movement of the subject P, the relative distance between the array microphone 112 and the utterance part is updated in real time, and the phase of the voice of the subject P is corrected in real time. Even when body movement occurs, only the voice of the subject P can be highlighted in real time.

<Operation>
FIG. 12 is a flowchart showing a processing procedure according to the second embodiment. Hereinafter, a processing procedure in the second embodiment will be described with reference to FIGS. 13 and 14.

  The processing related to step S201 to step S203 is the same as the processing related to step S101 to step S103 in the flowchart of the first embodiment, and thus description thereof is omitted.

  In step S204, the first protocol is executed as in the first embodiment. As in the first embodiment, any protocol can be selected as the first protocol. Using the MR data obtained by executing the first protocol, the image generation function 135b generates an MR image.

  Next, the system control function 135a displays the first image obtained by executing the first protocol on the display device 132. The operator refers to the MR image displayed on the display device 132 and designates the utterance part to be followed by the GUI (step S206).

  FIG. 13 is a diagram illustrating an example of a method for setting a vocal part, which is a characteristic part in the second embodiment. For example, a sagittal plane image including an organ such as the vocal cord 54 in the MPR image generated from the three-dimensional MR data of the head is suitable for setting the uttered part. The operator refers to the image of the sagittal surface of the subject P and sets the utterance part of the subject P.

  Next, the sequence control function 120a executes the second protocol. As in the first embodiment, any protocol can be selected for the second protocol. When the second protocol is executed, the positional deviation of the head is detected by the feature part tracking function 135c. From the amount of positional deviation of the head, the feature part tracking function 135c estimates the position of the uttered part after movement. The voice adjustment function 134b reads the position of the uttered part after the movement, grasps the position of the uttered part, the distance between the uttered part and each array microphone 112, and the voice of the subject P detected by each array microphone 112. By calculating the phase component, it is possible to transmit the synthesized sound by adjusting each phase to the operator (step S207).

  The above step S207 will be described in detail using the flowchart of FIG. First, the voice uttered by the subject P is acquired by the array microphone 112 and transmitted to the voice adjustment function 134b as a voice parameter (step S91). When the voice adjustment function 134b receives the voice parameter related to the voice of the subject P, the voice adjustment function 134b reads the position information of the utterance part as the feature part from the feature part tracking function 135c (step S92). The voice adjustment function 134b temporarily stores the position information of the utterance part before the execution of the second protocol, adjusts the voice parameter of the voice of the subject P, and emphasizes only the voice of the subject P. The extracted voice is output to the operator via the external audio output device 140 (step S93). Next, the second protocol is executed (step S94). At the same time as the second protocol is executed, the feature part tracking function 135c moves the head movement of the uttered part of the subject P designated in S206 in the same manner as in the first embodiment. The position is estimated in real time from the amount, and the position information of the uttered part after movement is output to the sound adjustment function 134b (step S95). The voice adjustment function 134b reads the position of the uttered part after body movement calculated by the feature part tracking function 135c, adjusts the phase of the voice of the subject P, and extracts only the voice of the subject P in an emphasized manner. (Step S96). Next, it is determined by the sequence control function 120a whether or not the imaging sequence is completed (step S97). When the imaging sequence ends, extraction of the voice of the subject P acquired from the array microphone 112 by the audio adjustment function 134b ends. If the imaging sequence has not ended, the process returns to S94 and another protocol is executed.

  In addition, since the processes according to step S208 and step 209 in the flowchart of FIG. 12 are the same as steps S108 and S109 in the first embodiment, the description thereof is omitted.

(Third embodiment)
In the third embodiment, transmission of a noise-cancelling sound for reducing noise in the auditory part of the subject P and tracking the uttered part of the subject P following the auditory part and the utterance part of the subject P. A case will be described in which voice collection is simultaneously performed to facilitate bidirectional communication between the subject P and the operator. In the first embodiment, the noise canceling sound corresponding to the pulse sequence is acquired and the noise canceling sound is transmitted. In the third embodiment, a plurality of array microphones 112 are used. An explanation will be given using a technique for removing noise as an example. However, the third embodiment may be implemented using the method of generating a noise canceling sound from the pulse sequence described in the first embodiment. The array microphone 112 used in the third embodiment may also be used as a microphone for collecting sounds including ambient noise in order to perform noise canceling.

  FIG. 15 is a block diagram showing a configuration of the MRI apparatus 100 according to the third embodiment. In the third embodiment, the speaker 111 arranged in the first embodiment, the array microphone 112 arranged in the second embodiment, and the external audio output device 140 are included. In the third embodiment, the speaker 111 includes a function of transmitting an instruction from an operator in addition to a function of transmitting a noise canceling sound. Further, the array microphone 112 collects noise in the imaging port in order to generate a noise canceling sound by the sound adjustment function 134c. Therefore, it is desirable that the arrangement position of the array microphone 112 in the third embodiment is in the vicinity of the auditory part of the subject P.

  The sound adjustment function 134c according to the third embodiment collects noise in the vicinity of the auditory part of the subject P by the array microphone 112. The sound adjustment function 134c analyzes the sound parameter of noise in the vicinity of the collected subject P. The sound adjustment function 134c adjusts the frequency, amplitude, and phase from the sound parameter information of noise, and generates a noise canceling sound that can cancel the noise in the auditory part of the subject P. The audio adjustment function 134c also has the function of the audio adjustment function 134b in the second embodiment. Therefore, only the voice of the subject P acquired by the array microphone 112 is extracted with emphasis, and the voice of the subject P is output to the operator in the console room via the external audio output device 140. .

  FIG. 16 is a diagram illustrating an example of attachment positions of the speaker 111 and the array microphone 112 in the MRI apparatus 100. The mounting positions of the speakers 111 and the array microphones 112 may be the same as those described in the first and second embodiments. For example, the array microphones 112 may be arranged at a plurality of ends in the imaging port of the MRI apparatus 100. It may be arranged. Moreover, you may decide to arrange | position at the edge part of the top plate 105a. Further, the speaker 111 and the array microphone 112 may be arranged in the head coil 109b.

  In the third embodiment, by tracking the auditory part and the utterance part of the subject P in real time, the subject P moves and the positions of the auditory part and the utterance part are also followed. The noise canceling sound can be transmitted to the auditory part after movement using the speaker 111. The array microphone 112 can collect the voice of the subject P according to the uttered part after movement. As a result, communication between the subject P and the operator during the MR examination can be improved.

(Fourth embodiment)
In the fourth embodiment, a case will be described in which adjustment of the characteristic part of the subject P is manually performed before performing a series of processes related to the entire MR examination. In the first embodiment, the auditory site, which is a characteristic site, is specified on the MR image by the operator during the execution of the first protocol. However, in the fourth embodiment, the noise canceling effect is maximized. It is assumed that the position is set manually by the operator while communicating with the subject P. The fourth embodiment is described as being implemented in addition to the first embodiment, but the fourth embodiment is implemented in addition to the second embodiment and the third embodiment. May be.

  FIG. 17 is a block diagram excerpting the processing circuit 135x according to the fourth embodiment. In the fourth embodiment, the MRI apparatus 100 includes a processing circuit 135x instead of the processing circuit 135 in the first embodiment. The processing circuit 135x (processing unit) has a configuration in which a calibration function 135d is added to the processing circuit 135.

  The calibration function 135d (calibration unit) is performed, for example, immediately before the collection of three-dimensional MR data (execution of the first protocol) in step S104 of the first embodiment. More specifically, when the operator inputs to execute calibration via the input device 131, the calibration function 135d reads the imaging conditions set in step S101, and tilts according to a desired pulse sequence. A magnetic field is generated by the gradient magnetic field coil 103, and noise similar to that during actual imaging is generated. Since it is not always necessary to perform MR imaging at the time of executing the calibration process, the calibration process may be performed in a state where no RF pulse is transmitted. Alternatively, a pulse sequence not including an RF pulse may be separately prepared and the pulse sequence may be executed. In a state where noise is generated by the gradient magnetic field coil 103, the operator sends a noise canceling sound to the subject P, and adjusts the part of the subject P where the noise canceling effect is enhanced and the parameters of the noise canceling sound. Do. At this time, the operator selects an auditory part of the subject P or an arbitrary position in the vicinity thereof as a noise canceling position, and sequentially transmits a noise canceling sound to the noise canceling position via the speaker 111. Go. The operator can extract the noise canceling position where the noise canceling effect is maximized by communicating with the subject P. By performing calibration before MR imaging, it can be expected that the noise canceling effect is enhanced. Moreover, it is expected that the psychological burden and anxiety of the subject P can be reduced by providing an opportunity for the subject P and the operator to communicate before MR imaging.

  In the embodiment described above, the auditory part and the utterance part set by the operator have been described as following the positions on the captured MR image, but the embodiment is not limited to the above form. For example, an optical camera (optical imaging unit) such as a fiberscope camera that does not include a separate magnetic body is disposed in the imaging port of the MRI apparatus 100, and the body movement of the subject P is calculated from the optical image (third image). You may decide to do it. In this case, the part set on the MR image at the time of positioning the characteristic part in the first and second embodiments is used as the auditory part and the voice part of the subject P. The feature part tracking function 135c reads the movement amount of the subject P acquired by the optical camera and corrects the position. At this time, in order to follow the movement of the subject P in each of the three-dimensional directions, it is desirable that the optical camera captures the subject P from two or more directions. In addition, as an example of a position tracking method on the optical image of the subject P, each part of the subject P such as the eyes, nose, and ear is detected as a marker, and the body of the auditory part or the utterance part is determined from the amount of movement of each part. There is a method for estimating the position after movement. When the movement amount of the subject P is read from the optical camera, the feature part tracking function 135c outputs the movement amount of the subject P to the audio adjustment function 134b. In the fourth embodiment, the calibration function 135d has been described as being added to the first embodiment. However, the calibration function 135d may be added to the second embodiment and the third embodiment. In this case, the operator can specify the utterance part of the subject P by using the calibration function 135d, and can also specify the position where the sound collection effect by the array microphone 112 is maximized.

  According to the embodiment described above, even if the subject P is transferred by body movement or the like during imaging of the MR image, the noise canceling sound is transmitted and the sound collection position of the array microphone is adjusted following the position after the movement. Can be performed. Thereby, in a situation where the operator needs to communicate with the subject P, for example, when fMRI imaging is performed, an instruction from the operator can be reliably transmitted to the subject P. In addition, the operator can hear the voice of the subject P more reliably, and the communication between the operator and the subject P can be improved.

  Note that the components described as “units” in this embodiment may be realized by hardware, software, or hardware and software. It may be realized by a combination.

  In addition, the term “processor” used in the above description is, for example, a CPU (central processing unit), a GPU (Graphical Processing Unit), or an application specific integrated circuit (ASIC) or a programmable logic device. (For example, Simple Programmable Logic Device (SPLD), Complex Programmable Logic Device (CPLD), and Field Programmable Gate Array (FPGA). The processor realizes the function by reading and executing the program stored in the storage circuit 133. Instead of storing the program in the storage circuit, the processor is directly incorporated in the circuit of the processor. In this case, the processor realizes the function by reading out and executing the program incorporated in the circuit, and each processor of the present embodiment is configured as a single circuit for each processor. However, the present invention is not limited to such a case, and a plurality of independent circuits may be combined to form a single processor so as to realize the function, and a plurality of components shown in FIG. You may make it implement | achieve the function.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example 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 100 ... MRI apparatus, 101 ... Static magnetic field magnet, 102 ... Static magnetic field power supply, 103 ... Gradient magnetic field coil, 104 ... Gradient magnetic field power supply, 105 ... Bed apparatus, 105a ... Top plate, 107 ... Transmission coil, 108 ... Transmission circuit, 109 DESCRIPTION OF SYMBOLS ... Reception coil, 109b ... Head coil, 110 ... Reception circuit, 111 ... Speaker, 112 ... Array microphone, 120 ... Processing circuit, 120a ... Sequence control function, 131 ... Input device, 132 ... Display device, 133 ... Memory circuit, 134 ... Processing circuit, 134a ... Sound acquisition function, 134b, 134c ... Sound adjustment function, 135 ... Processing circuit, 135x ... Processing circuit, 135a ... System control function, 135b ... Image generation function, 135c ... Feature part tracking function, 135d ... Calibration 140: external audio output device, 141: wiring.

Claims (23)

A first protocol for acquiring a first image by imaging a subject, and a second protocol that is executed after the first protocol and acquires a second image. A sequence controller that controls the execution of a series of protocols;
A display unit for acquiring the first image;
An input unit that receives an input of a characteristic part of the subject on the first image displayed on the display unit before the execution of the second protocol;
Based on at least one of a pulse sequence and position information of the characteristic part, a sound acquisition unit for acquiring a noise canceling sound to be transmitted to the characteristic part;
A speaker for transmitting the noise canceling sound to the characteristic part during execution of the second protocol;
A magnetic resonance imaging apparatus. A calculation unit for calculating the positional deviation amount of the characteristic part by comparing the first image and the second image;
2. The magnetic resonance imaging apparatus according to claim 1, wherein the voice acquisition unit sets the noise canceling sound corresponding to the characteristic part after the positional deviation during execution of the second protocol. A plurality of the second images are acquired during execution of the second protocol,
The calculation unit calculates a positional shift of the characteristic part by comparing each of the plurality of second images,
The magnetic resonance imaging apparatus according to claim 2, wherein the sound acquisition unit sets the noise canceling sound corresponding to the characteristic part after positional deviation. A plurality of the second protocols are executed,
The calculation unit calculates a positional deviation amount of the feature portion between the second protocol executed first and the second protocol executed later in the plurality of second protocols,
The magnetic resonance imaging apparatus according to claim 2, wherein the speaker transmits the noise canceling sound corresponding to the characteristic part in the second protocol executed later in the plurality of second protocols.   The magnetic resonance imaging apparatus according to claim 1, wherein the characteristic part is a part related to hearing of the subject.   5. The magnetic resonance imaging apparatus according to claim 1, wherein the speaker is arranged on a circumference at a plurality of locations in the imaging port. 6. A receiving coil attached to the subject;
The magnetic resonance imaging apparatus according to claim 1, wherein the speaker is disposed in the receiving coil. A microphone for acquiring noise;
5. The at least one of claims 1 to 4, wherein the sound acquisition unit performs setting of the noise canceling sound, which is a sound having an opposite phase, the same amplitude, and the same frequency, with respect to noise acquired by the microphone. Magnetic resonance imaging equipment. A calibration unit for adjusting the position of the destination of the noise canceling sound in the subject;
The calibration unit executes a pulse sequence on the subject, and while the pulse sequence is being executed, causes the noise canceling sound corresponding to noise at a plurality of positions to be transmitted from the speaker, and from the input unit to the operator. 5. The magnetic resonance imaging apparatus according to claim 1, wherein any one of the plurality of positions is received as the characteristic part by receiving input information from.   The magnetic resonance imaging apparatus according to claim 9, wherein the calibration unit accepts adjustment of a position of a transmission destination of the noise canceling sound in a state where an RF pulse is not transmitted to the subject. A first protocol for acquiring a first image by imaging a subject, and a second protocol that is executed after the first protocol and acquires a second image. A sequence controller that controls the execution of a series of protocols;
A display unit for acquiring the first image;
An input unit that receives an input of a characteristic part of the subject on the first image displayed on the display unit before the execution of the second protocol;
A microphone that receives position information of the characteristic part and acquires a sound transmitted from the characteristic part during execution of the second protocol;
An audio adjustment unit for adjusting the sound acquired by the microphone;
A magnetic resonance imaging apparatus. A calculation unit for calculating the positional deviation amount of the characteristic part by comparing the first image and the second image;
12. The sound adjustment unit according to claim 11, wherein during execution of the second protocol, the sound transmitted from the feature part via the microphone is acquired, and the sound is adjusted based on the amount of displacement. Magnetic resonance imaging equipment. A plurality of the second images are acquired during execution of the second protocol,
The calculation unit calculates a positional deviation amount of the characteristic part by comparing each of the plurality of second images,
The magnetic resonance imaging apparatus according to claim 12, wherein the sound adjustment unit acquires a sound transmitted from the feature part via the microphone and adjusts the sound based on the positional deviation amount. A plurality of the second protocols are executed,
The calculation unit calculates a positional deviation amount of the feature portion between the second protocol executed first and the second protocol executed later in the plurality of second protocols,
The microphone acquires a sound transmitted from the characteristic part during execution of a plurality of the second protocols,
The magnetic resonance imaging apparatus according to claim 12, wherein the sound adjustment unit adjusts the sound during execution of a plurality of the second protocols.   The magnetic resonance imaging apparatus according to claim 11, further comprising a speaker that sends the sound adjusted by the sound adjustment unit to an operator.   The magnetic resonance imaging apparatus according to claim 11, wherein the characteristic part is a part related to utterance of the subject.   The magnetic resonance imaging apparatus according to claim 11, wherein the microphone is arranged on a circumference at a plurality of locations in an imaging port. A receiving coil attached to the subject;
The magnetic resonance imaging apparatus according to claim 11, wherein the microphone is disposed in the receiving coil. A calibration unit for adjusting position information regarding the utterance part of the sound from the subject;
The calibration unit performs a pulse sequence on the subject, and the sound acquired by the plurality of microphones during the execution of the pulse sequence is based on the positional deviation amount read from the calculation unit. The sound adjusted corresponding to a plurality of positions is output from the voice adjustment unit, and any one of the plurality of positions is received as the feature portion by receiving operator input information from the input unit. The magnetic resonance imaging apparatus according to at least one of 12 to 14.   The magnetic resonance imaging apparatus according to claim 19, wherein the calibration unit receives adjustment of a position related to a sound uttering portion of the sound from the subject in a state where an RF pulse is not transmitted to the subject.   The magnetic resonance imaging apparatus according to claim 1, wherein the first image is an MPR image generated from three-dimensional MR data of the subject. . An optical imaging unit for acquiring a third image obtained by imaging the subject;
A calculation unit that calculates the positional deviation amount of the characteristic part by comparing the first image and the third image;
A voice acquisition unit that acquires the noise canceling sound corresponding to the characteristic part after the position shift based on the position shift amount calculated by the calculation unit;
The magnetic resonance imaging apparatus according to claim 1, further comprising: An optical imaging unit for acquiring a third image obtained by imaging the subject;
A calculation unit that calculates the positional deviation amount of the characteristic part by comparing the first image and the third image;
A sound adjustment unit that obtains a sound sent from the characteristic part after the position shift based on the position shift amount calculated by the calculation unit, and adjusts the sound based on the position shift amount;
The magnetic resonance imaging apparatus according to claim 11, further comprising: