JP6645897B2 - Magnetic resonance imaging equipment - Google Patents

Description

  Embodiments of the present invention relate to a magnetic resonance imaging apparatus.

  In magnetic resonance imaging (MRI), a nuclear spin of a subject placed in a static magnetic field is magnetically excited by an RF (Radio Frequency) pulse having a Larmor frequency, and the magnetic resonance is generated with the excitation. This is an imaging method for generating an image from data of a magnetic resonance signal to be generated.

  Incidentally, the subject and the operator may communicate with each other during the examination by conversation or the like. However, at the time of inspection by the MRI apparatus, air vibration occurs due to vibration of a coil unit or the like in the MRI apparatus, and noise occurs. In some cases, communication between the subject and the operator is disturbed by the noise. 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

  An object of the present invention is to provide a magnetic resonance imaging apparatus capable of improving an acoustic environment around a subject in an MRI apparatus.

The magnetic resonance imaging apparatus according to the embodiment includes a first protocol for acquiring a first image by imaging a subject, and a second protocol for executing the first protocol after the first protocol and acquiring a second image. A sequence control unit that controls the execution of a series of protocols related to the same subject, a display unit that displays a first image acquired by executing the first protocol, and a display unit that executes a second protocol. And an input unit for receiving an input of a characteristic part of the subject on the first image displayed on the display unit, and supporting the second protocol during execution of the second protocol based on the positional information of the characteristic part. A speaker for transmitting a noise canceling sound to the characteristic portion.

FIG. 1 is a block diagram illustrating a schematic configuration of a magnetic resonance imaging apparatus according to a first embodiment. FIG. 4 is a diagram illustrating an example of a mounting position of the speaker according to the first embodiment. FIG. 4 is a diagram illustrating an example of a mounting position of a speaker in a head coil according to the first embodiment. FIG. 3 is a diagram illustrating an example of a positioning image of a hearing part according to the first embodiment. FIG. 3 is a diagram illustrating an example of body motion correction according to the first embodiment. FIG. 3 is a diagram illustrating an example of an imaging sequence for body movement correction according to the first embodiment. 5 is a flowchart illustrating a flow of a series of processes according to the first embodiment. 5 is a flowchart illustrating a flow of noise canceling according to the first embodiment. FIG. 4 is a diagram illustrating an example of a noise canceling method at a position following a hearing part according to the first embodiment. FIG. 4 is a block diagram illustrating a schematic configuration of a magnetic resonance imaging apparatus according to a second embodiment. FIG. 10 is a diagram illustrating an example of a mounting position of a microphone according to the second embodiment. 9 is a flowchart illustrating a flow of a series of processes according to the second embodiment. The figure which shows an example of the positioning image of the utterance part which concerns on 2nd Embodiment. 9 is a flowchart illustrating a flow of extracting a voice of the subject by the array microphone according to the second embodiment. FIG. 9 is a block diagram illustrating a schematic configuration of a magnetic resonance imaging apparatus according to a third embodiment. The figure which shows an example of the attachment position of the speaker and microphone which concern on 3rd Embodiment. FIG. 13 is a block diagram illustrating a configuration of a processing circuit according to a fourth embodiment.

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

(First embodiment)
The MRI apparatus 100 often executes a series of scans in one examination. The “scan” means that a desired MR signal is acquired by executing a pulse sequence in which imaging parameters such as TR (Repetition Time), TE (Echo Time), and FA (Flip Angle) are set. is there. Also, a unit that divides a series of scan groups executed in one inspection for convenience is called a “protocol”. Typically, one scan corresponds to one protocol, but one protocol may include a plurality of scans. A protocol group corresponding to a series of scan groups can be classified into a protocol corresponding to an “imaging scan” for acquiring a diagnostic image (also referred to as an “imaging protocol”) and a protocol other than the imaging scan. Protocols other than the imaging scan include, for example, a sensitivity map scan for collecting a reception sensitivity map of an RF coil, a shimming scan for collecting data for uniform correction of the static magnetic field intensity, and a labeling area and an imaging area for the imaging scan. A locator scan for acquiring a positioning image for setting the position is applicable. Further, one examination may include a plurality of “imaging scans”. The “imaging scan” in the present embodiment corresponds to, for example, a scan of a functional image or a scan of a morphological image at the time of fMRI (functional Magnetic Resonance Imaging) inspection. In the imaging scan according to the present embodiment, a description will be given assuming that a scan of a functional image of fMRI is performed and a plurality of three-dimensional MR data are acquired.

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

  In the following embodiments, for example, among the protocols performed prior to the imaging scan as the first protocol, a description will be given on the assumption that the locator scan is set to the second scan after the locator scan. Perform

<Components> 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 device 105, a processing circuit 106, 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 subject P (for example, a human body) is not included in the MRI apparatus 100. Further, the configuration shown in FIG. 1 is only an example. For example, each component 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. This embodiment may be implemented by providing one processing circuit having the functions of the processing circuits 134 and 135. Conversely, the processing circuit 135 may be divided into three independent processing circuits, each of which may execute the system control function 135a, the image generation function 135b, and the characteristic part tracking function 135c.

  The static magnetic field magnet 101 is a magnet formed in a hollow substantially cylindrical shape (including a shape having a cross section orthogonal to the center axis of the cylinder having an elliptical shape), and generates a static magnetic field in an internal space. In the following embodiments, a hollow substantially cylindrical shape includes a shape in which a cross section orthogonal to the center axis of the cylinder becomes elliptical. The static magnetic field magnet 101 is, for example, a superconducting magnet, and is supplied with a current from a static magnetic field power supply 102 to be excited. 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. Further, the static magnetic field power supply 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 magnetic field coil 103 is formed by combining three coils corresponding to the X, Y, and Z axes orthogonal to each other. These three coils are individually supplied with current from the gradient magnetic field power supply 104. Thus, a gradient magnetic field whose magnetic field strength changes along each of the X, Y, and Z axes is generated. The gradient magnetic fields of the X, Y, and Z axes generated by the gradient 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 driving device (not shown). The base is a housing having a motor or an actuator capable of moving the top plate 105a in the vertical direction (the direction orthogonal 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 105a on which the subject P is placed from the imaging port of the MRI apparatus 100. The couchtop 105a is a plate-shaped member on which the subject P that can be moved by the couch driving device in the body axis direction of the subject P and in a direction orthogonal to the body axis direction 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 106a is connected to the couch device 105, and controls the operation of the couch device 105 by outputting an electric signal for control to the couch device 105. For example, the couch control function 106a receives an instruction to move the top board 105a in the longitudinal direction, the up / down direction, or the left / right direction from the operator via the input device 131, and moves the top board 105a according to the received instruction signal. The drive mechanism of the top plate 105a of the bed device 105 is operated.

  The transmission coil 107 is a coil formed in a hollow substantially cylindrical shape, is arranged inside the gradient magnetic field coil 103, and receives a supply of an RF pulse from the transmission circuit 108 to generate a high-frequency magnetic field. The transmission circuit 108 supplies an RF pulse corresponding to the Larmor frequency determined by the type of the 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, MR signal) emitted from the subject P under 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. It may be configured by combining one or more of a coil having only a transmitting function, a coil having only a receiving function, or a coil having a transmitting and receiving function.

  The receiving circuit 110 (receiving unit) detects an 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 electric signal into physical vibration. The speaker 111 is disposed inside the imaging opening inside the transmission coil 107, transmits noise canceling sound for reducing noise generated by the MRI apparatus 100, and detects noise that the subject P perceives in the imaging opening during MR imaging. Has the function of reducing The sound wave of the noise canceling sound has an opposite phase to the sound wave of the noise 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 transmitted from the speaker 111 cancel each other, so that the sound is substantially perceived by the subject P. The volume of the noise is reduced. A signal corresponding to the noise canceling sound transmitted by the speaker 111 is acquired by the audio acquisition function 134a. Since the speaker 111 in the present embodiment is used in the MRI apparatus 100, it is preferable that the speaker 111 does not include a magnetic material. For example, PZT (lead zirconate titanate) may be used instead of a magnetic material normally used for a speaker vibrator. It is preferable to use a piezoelectric speaker or the like using a piezoelectric vibrator such as the above. The speaker 111 is connected to a processing circuit 134 to be described later by wiring or the like, and transmits the noise canceling sound generated by the sound acquisition function 134a of the processing circuit 134.

  FIG. 2 is a diagram illustrating an example of a mounting position of the speaker 111 in the MRI apparatus 100. The speakers 111 are arranged on the circumference of the MRI apparatus 100 at a plurality of positions inside the imaging opening. 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 in which the speakers 111 are attached to the top plate 105a. 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, a speaker 111b is arranged on, for example, a top plate 105a separately from the speaker 111 for transmitting the noise canceling sound to the subject P. The speaker 111b is a device that generates sound by converting an electric signal into a physical signal in the same manner as the speaker 111. The speaker 111b has a function of transmitting voice from the operator or the like to the subject P. The speaker 111b may transmit music or the like to the subject P. Thereby, an effect of alleviating the tension of the subject P during the examination can be expected. Further, the speaker 111 may be arranged in the receiving coil 109, not in the imaging opening of the MRI apparatus 100.

  FIG. 3 is a diagram illustrating an example of a mounting position of the speaker 111 on 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 near the ear of the subject P with the head coil 109b mounted on the subject P. 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 be arranged 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 executes the various pulse sequences by reading the sequence execution data output from the processing circuit 135 and driving the gradient magnetic field power supply 104, the transmission circuit 108, and the reception circuit 110.

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

  Further, the sequence control function 120a (sequence control unit) receives the MR signal from the receiving circuit 110 as a result of the execution of the various pulse sequences, and stores the received MR signal in the storage circuit 133. The 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 an 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 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 an imaging condition and an image generation function 135b of the processing circuit 135 under the control of the system control function 135a of the processing circuit 135. Display an image or the like. The display device 132 is composed of, for example, a liquid crystal display.

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

  The processing circuit 134 (processing unit) has a voice acquisition function 134a (voice 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 from the storage circuit 133 a noise canceling sound corresponding to the noise generated by the MRI apparatus 100 when executing various pulse sequences. Simultaneously with the start of the execution of the pulse sequence, the noise canceling sound is output to the auditory site of the subject P via the speaker 111. The noise canceling sound is a sound having the same frequency, the same amplitude, and the 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 site of the subject P can be designated on the MR image by the operator from organs responsible for hearing, such as the pinna, ear canal, eardrum, and middle ear. The auditory region is a position where the noise canceling sound transmitted from each speaker 111 is a focal point, and at this position, the noise and the noise canceling sound cancel each other. An operator designates an appropriate position each time according to individual differences of the subject P, an imaging region of an MR image to be imaged, and an acquired cross section. In this 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, The noise canceling sound may be appropriately adjusted. Further, the voice acquisition function 134a reads the position of the auditory region after body movement calculated by the characteristic region 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. Thus, 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. The body movement in the present embodiment is assumed to be a minute body movement of the subject P due to respiration or the like, or a body movement of the subject P nodding or swinging.

  The processing circuit 135 (processing unit) is configured to include a system control function 135a, an image generation function 135b, and a characteristic 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 the various pulse sequences by transmitting the generated sequence execution data to the processing circuit 120. Further, the system control function 135a 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, thereby forming the MR image. Generate. Further, the image generation function 135b stores the generated MR image in the storage circuit 133.

  In addition, the image generation function 135b is an example of a first image acquisition unit that acquires an image for specifying a characteristic part described later and a second image acquisition unit that acquires an image for correcting positional deviation.

  The feature-following function 135c, for example, stores the spatial position information of a feature such as a hearing part specified by the operator on the MR image (first image) by the operator during execution of the first protocol, in the second mode. It has a function of updating and following the MR image (second image) during execution of the protocol. More specifically, first, the characteristic portion following function 135c reads the first image from the storage circuit 133 and displays the first image on the display device 132. Next, the characteristic part tracking function 135c receives the position information of the characteristic part specified 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 obtained by imaging a part including a characteristic part. For example, an MPR image generated by performing a reconstruction process 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 characteristic part tracking function 135c receives the position information of the characteristic part, and tracks the position of the subject P after the movement due to the body movement or the like during the imaging of the second image. In the following description, an example will be described in which a characteristic part is specified using an MPR image acquired during a locator scan. In addition, the characteristic portion following function 135c is an example of a calculation unit that calculates a positional shift of the characteristic portion before and after the body movement. The first image is not limited to an image 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 a hearing part. FIG. 4 shows, as an example of the first image, an image of a coronal plane including an organ such as the inner ear among MPR images generated from the three-dimensional MR data of the head. The operator refers to, for example, an image of the coronal surface of the head of the subject P via the input device 131 and sets the auditory region of the subject P. When the setting of the auditory region is performed, the spatial coordinate information of the auditory region is calculated by the characteristic region tracking function 135c. The calculated spatial coordinate information of the auditory region is stored in the storage circuit 133. The auditory site is selected by the operator from the pinna 11, the external auditory meatus 12, the eardrum 13, the middle ear 14, and the like, as shown in FIG. As described above, the auditory site does not necessarily need to designate each organ of the subject P. For example, as illustrated in FIG. It may be specified above.

  The characteristic portion tracking function 135c tracks the position of the subject P after movement due to body motion or the like during MR image imaging during execution of the second protocol after positioning of the characteristic portion specified by the operator. In the first embodiment, the characteristic portion following function 135c detects the body movement of the subject P, estimates the movement of the auditory region in real time, and transmits a noise canceling sound to the auditory region after the movement. Perform shift correction. As described above, the second protocol according to the present embodiment will be described assuming an imaging scan for acquiring a functional image of fMRI as an example. Therefore, the description will be made on the assumption that a plurality of three-dimensional MR data having different time phases are acquired in the second protocol. 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 site N according to the first embodiment. At the time of acquisition of each second image, the spatial positions of the auditory region designated by the operator before and after the body movement are calculated, and the spatial positions of the auditory region before the body movement are calculated from the spatial positions of the auditory regions after the body movement. By calculating the difference, the auditory region is calculated. Here, since the head including the auditory region is a rigid body (rigid body), the deformation can be ignored. Therefore, it is possible to acquire the three-dimensional MR data of the imaging region including the head a plurality of times as the second image, and calculate the difference between the positions of the head before and after the movement by comparing the three-dimensional MR data. It is possible.

  More specifically, at the time of acquiring the first three-dimensional MR data in the second protocol (Volume 1), the three-dimensional MR data 31 of the subject P is collected. At this time, the spatial coordinates (x, y, z) of the auditory site N in the three-dimensional MR data 31 are calculated. Next, at the time of obtaining the second three-dimensional MR data (Volume 2), the three-dimensional MR data 32 of the subject P is collected. Further, the subject P moves between Volume 1 and Volume 2, and the spatial coordinates of the auditory region N change from coordinates (x, y, z) to coordinates (x + x ′, y + y ′, z + z ′). The characteristic portion following function 135c reads the difference between the changed spatial coordinates and calculates the displacement (x ', y', z ') of the auditory site N. Similarly, at the time of the third MR data acquisition (Volume 3), the three-dimensional MR data 33 of the subject P is collected. Similarly, the spatial coordinates of the auditory region N change from coordinates (x, y, z) to coordinates (x + x ′ + x ″, y + y ′ + y ″, z + z ′ + z ″) between Volume3 and Volume2. . At this time, the positional shift amount of the auditory region N may be calculated by calculating the difference between the three-dimensional MR data 33 and the three-dimensional MR data 32 whose imaging time is closest, or may be calculated as the difference between the three-dimensional MR data 33 and the first. May be calculated by calculating the difference between the three-dimensional MR data 31 photographed at the time. As described above, the position of the auditory site N can be followed by updating the spatial coordinates of the auditory site N every time the MR data is acquired. Here, a case has been described in which a plurality of three-dimensional MR data is acquired. However, acquisition of three-dimensional MR data described in the present embodiment may be replaced with acquisition of a slice image of the subject P. good. When a plurality of protocols are continuously executed, the spatial coordinates of the auditory region N are updated even at the timing of transition from the n-th protocol (Protocoln) to the (n + 1) -th protocol (Protocol (n + 1)). Thus, the position of the auditory site N may be further followed. For example, if the positioning of the characteristic part has already been performed by the protocol before the locator scan, noise canceling is performed during the locator scan, and the position of the characteristic part is further updated when the next shimming scan is performed. Alternatively, noise canceling may be continuously performed on the same auditory site N.

  FIG. 5 has been described assuming that the auditory region N is included in the imaging region when the second protocol is executed. However, the auditory region N does not necessarily need to be included in the imaging region. For example, a difference in the position of the head can be calculated by acquiring three-dimensional MR data of an arbitrary imaging region in the head a plurality of times in the same manner as described above and comparing the three-dimensional MR data. The characteristic portion following function 135c can read this difference as the movement amount of the auditory site N. For example, when the eardrum 13 is designated by the operator as the auditory site in the first protocol and the head above the eardrum 13 but not including the eardrum 13 is imaged as the imaging region in the second protocol, the second The eardrum is not included in the imaging region in the protocol of (1). At this time, by calculating the amount of movement of the head, the characteristic portion following function 135c can follow the movement of the eardrum 13 which is the auditory portion. Further, the MR image used for calculating the displacement after the body movement acquired at the time of executing the second protocol described above is an example of the second image.

  Further, the tracking method in the present embodiment is not limited to the above-described method, and the reference scan is performed before the MR data is acquired during the execution of the second protocol, and the reference scan before acquiring the three-dimensional MR data is performed. The body movement may be detected by calculating the amount of movement of the characteristic part from.

  FIG. 6 is a diagram showing the execution timing of the reference scan during execution of the second protocol. The reference scan is executed before acquiring MR data. For example, by calculating the difference between the spatial position of the auditory site at the time of the first reference scan and the second reference scan, it is possible to calculate the displacement of the auditory site due to body movement. The reference scan does not necessarily need to be performed before acquiring MR data, but may be performed a predetermined number of times. The reference scan is an imaging method in which MR images under imaging conditions that do not hinder the T1 relaxation time are collected in a short time. Examples of the reference scan include a 2D single-shot spiral scan, a scan with a low flip angle, and a scan of three orthogonal cross sections.

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

  First, the system control function 135a receives an imaging condition input from the operator on the GUI via the input device 131, and generates sequence information according to the received 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 device 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). More specifically, when the couch control function 106a moves the couchtop 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 site via the input device 131 at the timing when the light of the projector is applied to the imaging site (for example, the head). Thereby, the couch control function 106a moves the couchtop 105a so that the designated imaging region is positioned at the center of the magnetic field.

  Subsequently, the sequence control function 120a executes a locator scan for determining an imaging area at the time of 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 prompting the operator to specify the auditory region. The operator refers to the MR image displayed on the display device 132 and specifies the auditory region to be followed by using the GUI (step S106).

  Next, the sequence control function 120a executes the second protocol. During the execution of the second protocol, the characteristic portion following function 135c detects a positional displacement of the head. From the positional displacement amount of the head, the characteristic portion following function 135c estimates the position of the auditory region after moving. The voice acquisition function 134a reads the position of the hearing part after the movement, calculates the distance between the hearing part and each speaker 111, adjusts the transmission position of the noise canceling sound, and transmits the sound (step S107).

  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 according to the read pulse sequence (step S82). Simultaneously with the execution of the second protocol, the voice acquisition function 134a sends out the noise canceling sound read from the storage circuit 133 to the auditory site of the subject P via the speaker 111 (step S83). During the execution of the second protocol, the characteristic site following function 135c estimates the movement of the auditory site due to the body movement of the subject P specified in S106, for example, from the amount of movement of the head in real time. The position shift correction for transmitting the noise canceling sound to the auditory site is performed (step S84). The voice acquisition function 134a reads the position of the auditory part after body movement calculated by the characteristic part tracking function 135c, adjusts the phase of the noise canceling sound, and adjusts the noise corresponding to the position of the auditory part after body movement. The canceling sound is output via the speaker 111. When the pulse sequence has been switched, the noise canceling sound corresponding to the switched pulse sequence is acquired again from the storage circuit 133, and the noise canceling sound is transmitted (step S85). Next, the sequence control function 120a determines whether or not the imaging sequence has ended (step S86). If the imaging sequence has ended, the 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 assuming that the characteristic portion is positioned on the MR image acquired in the locator scan. However, the embodiment is not limited to the above description. For example, the positioning of the characteristic portion may use an MR image acquired during an imaging scan. More specifically, for example, at the time of fMRI, the positioning of the characteristic portion may be performed during the imaging scan of the morphological image before the acquisition of the functional image.

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

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

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

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

  FIG. 11 is a diagram illustrating an example of an attachment position of the array microphone 112 in the MRI apparatus 100. Similar to the mounting position of the speaker 111 in the first embodiment, the mounting positions of the array microphones 112 may be plural in the imaging opening of the MRI apparatus 100 at both ends in the long axis direction of the imaging opening. good. Further, as in the first embodiment, a plurality of array microphones 112 may be arranged diagonally in the imaging opening. 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 sound output device 140 (external sound output unit) is configured by a speaker or the like normally arranged in an operation room, and has a function of transmitting the voice of the subject P in the MRI apparatus 100 to an operator.

  Further, the processing circuit 134 has an audio adjustment function 134b instead of the audio acquisition function 134a in the first embodiment. The voice adjustment function 134b (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 following function 135c. Examples of the uttered part of the subject P include a lip peripheral region 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 based on the sound acquired by each array microphone 112 and the position information of the uttered part. Specifically, position information of the uttered part is grasped by the characteristic part following function 135c, and the relative distance between the uttered part and each array microphone 112 is calculated. By compensating for the phase of the audio signal acquired by each array microphone 112 using the relative distance between each array microphone 112 and the utterance site and synthesizing, only the voice generated from the utterance site of the subject P is emphasized. Can be taken out. In addition, since the characteristic portion following function 135c follows the body motion of the subject P, the relative distance between the array microphone 112 and the uttered portion is updated in real time, and the phase of the voice of the subject P is corrected in real time. Therefore, even when a body movement occurs, only the voice of the subject P can be emphasized and extracted in real time.

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

  The processing from step S201 to step S203 has the same configuration as the processing from step S101 to step S103 in the flowchart of the first embodiment, and a description thereof will be omitted.

  In step S204, the first protocol is executed as in the first embodiment. As in the first embodiment, an arbitrary 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 specifies the utterance part to be followed by using the GUI (step S206).

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

  Next, the sequence control function 120a executes the second protocol. An arbitrary protocol can be selected for the second protocol as in the first embodiment. When the second protocol is executed, the head position shift is detected by the characteristic portion tracking function 135c. From the head displacement, the characteristic portion following function 135c estimates the position of the uttered portion after moving. 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 components, it is possible to transmit a sound synthesized by adjusting each phase to the operator (step S207).

  The step S207 will be described in detail with reference to the flowchart of FIG. First, a voice uttered by the subject P is acquired by the array microphone 112 and transmitted to the voice adjustment function 134b as voice parameters (step S91). When receiving the voice parameter related to the voice of the subject P, the voice adjustment function 134b reads the position information of the uttered part as the characteristic part from the characteristic part following function 135c (Step S92). The voice adjustment function 134b temporarily stores the position information of the uttered part before the execution of the second protocol, adjusts the voice parameters of the voice of the subject P, and emphasizes only the voice of the subject P. The voice of the subject P is extracted and output to the operator via the external voice output device 140 (step S93). Next, the second protocol is executed (Step S94). Simultaneously with the execution of the second protocol, the characteristic portion following function 135c performs the movement of the utterance part of the subject P by the body movement specified in S206 by moving the head similarly to the first embodiment. It estimates in real time from the amount, and outputs the position information of the uttered part after the movement to the sound adjustment function 134b (step S95). The voice adjustment function 134b reads the position of the uttered part after the body movement calculated by the characteristic part following 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, the sequence control function 120a determines whether or not the imaging sequence has ended (step S97). When the imaging sequence ends, the extraction of the voice of the subject P acquired from the array microphone 112 by the sound adjustment function 134b ends. If the imaging sequence has not ended, the process returns to S94, and another protocol is executed.

  In addition, the processes related to step S208 and step 209 in the flowchart of FIG. 12 are the same as step S108 and step S109 in the first embodiment, and thus description thereof will be omitted.

(Third embodiment)
In the third embodiment, transmission of a noise canceling sound for reducing noise in the auditory region of the subject P by following the auditory region and utterance region of the subject P, and following the utterance region of the subject P A case will be described in which voice collection is performed at the same time to achieve two-way 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. However, in the third embodiment, a plurality of array microphones 112 are used. A description will be given of a method of removing noise as an example. However, the third embodiment may be implemented using the technique of generating the noise canceling sound from the pulse sequence described in the first embodiment. Further, 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 illustrating a configuration of the MRI apparatus 100 according to the third embodiment. The third embodiment is configured to include both the speaker 111 arranged in the first embodiment, the array microphone 112 arranged in the second embodiment, and the external audio output device 140. In the third embodiment, in addition to the speaker 111 having a function of transmitting a noise canceling sound, the speaker 111 includes a speaker 111 having a function of transmitting an instruction from an operator. In addition, the array microphone 112 collects noise in the imaging opening in order to generate a noise canceling sound by the sound adjustment function 134c. For this reason, in the third embodiment, it is desirable that the arrangement position of the array microphone 112 is near the auditory site of the subject P.

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

  FIG. 16 is a diagram illustrating an example of a mounting position of the speaker 111 and the array microphone 112 in the MRI apparatus 100. The mounting position of the speaker 111 and the array microphone 112 may be the same as the arrangement described in the first embodiment and the second embodiment. For example, the arrangement of the array microphone 112 may be plural at the end inside the imaging opening of the MRI apparatus 100. It may be arranged. Further, it may be arranged at the end 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 following the auditory region and the utterance site of the subject P in real time, even if the subject P moves, and the positions of the auditory site and the utterance site are shifted, the positions of the auditory site and the utterance site are followed. Then, the noise canceling sound can be transmitted to the auditory part after the movement using the speaker 111. In addition, the array microphone 112 can collect the voice of the subject P according to the uttered part after the movement. Thus, communication between the subject P and the operator during conversation during the MR examination can be improved.

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

  FIG. 17 is a block diagram illustrating a processing circuit 135x according to the fourth embodiment. In the fourth embodiment, the MRI apparatus 100 has 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 acquisition of the three-dimensional MR data (execution of the first protocol) in step S104 of the first embodiment. More specifically, when the operator performs an input for executing calibration via the input device 131, the calibration function 135d reads the imaging condition set in step S101, and performs an inclination corresponding 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. When performing the calibration process, it is not always necessary to perform the MR imaging, so the calibration process may be performed in a state where the RF pulse is not 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 a part of the subject P and a parameter of the noise canceling sound where the noise canceling effect is high. 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 sends out a noise canceling sound to the noise canceling position via the speaker 111. Go. By communicating with the subject P, the operator can extract a noise canceling position at which the noise canceling effect is maximized. By performing the calibration before MR imaging, it can be expected that the noise canceling effect will be enhanced. Further, since the opportunity to communicate with the subject P and the operator is provided before the MR imaging, the psychological burden and anxiety of the subject P can be expected to be reduced.

  In the embodiment described above, the auditory region and the utterance region set by the operator are described as following the position on the captured MR image, but the embodiment is not limited to the above-described embodiment. For example, an optical camera (optical imaging unit) such as a fiberscope camera, which does not separately include a magnetic substance, is disposed in the imaging opening 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 so. In this case, the auditory part and the utterance part of the subject P use the part set on the MR image at the time of positioning the characteristic part in the first and second embodiments. The characteristic site tracking function 135c reads the amount of movement of the subject P acquired by the optical camera and performs position correction. At this time, in order to follow the movement of the subject P in each of the three-dimensional directions, it is preferable that the optical camera captures the subject P from two or more directions. Further, as an example of a position tracking method on the optical image of the subject P, each part of the subject P, such as eyes, nose, and ears, is detected as a marker, and the amount of movement of each part is used to determine the body of the auditory part or the vocal part. There is a method of estimating the position after the movement. When reading the movement amount of the subject P from the optical camera, the characteristic portion following 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 use the calibration function 135d to specify the utterance part of the subject P, and also specify the position where the sound collection effect of the array microphone 112 is maximized.

  According to the above-described embodiment, even if the subject P is moved by body movement or the like during MR image capturing, the position after the movement is followed to transmit the noise canceling sound or adjust the sound collection position of the array microphone. Can be performed. Accordingly, an instruction from the operator can be reliably transmitted to the subject P in a situation where communication between the operator and the subject P is required, for example, during imaging of fMRI. Further, the operator can more reliably hear the voice of the subject P, and communication between the operator and the subject P can be improved.

  The components described as “units” in the present embodiment may be realized by hardware, may be realized by software, or may be hardware and software. May be realized by a combination of the above.

  In addition, the term “processor” used in the above description may be, for example, a central processing unit (CPU), a graphical processing unit (GPU), or an application-specific integrated circuit (ASIC), a programmable logic device, or the like. (For example, a Simple Programmable Logic Device (SPLD), a Composite Programmable Logic Device (CPLD), and a Field Programmable Gate Array (FPGA) The processor realizes the function by reading and executing the program stored in the storage circuit 133. In addition, instead of storing the program in the storage circuit, the processor may be directly incorporated into the circuit of the processor. In this case, the processor realizes a function by reading and executing a program incorporated in the circuit. Note that 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 to realize its function.Moreover, a plurality of components in FIG. The function may be realized.

  Although several embodiments of the present invention have been described, these embodiments are provided by way of example and are not intended to limit the scope of the invention. These new embodiments can be implemented in other various forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and their equivalents.

  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 .., Receiving coil, 109b, head coil, 110, receiving circuit, 111, speaker, 112, array microphone, 120, processing circuit, 120a, sequence control function, 131, input device, 132, display device, 133, storage 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 ... Character site tracking function, 135d ... Calibration Function 140, external audio output device 141, wiring.

Claims (23)

The same object including a first protocol for acquiring a first image by imaging the object and a second protocol executed after the first protocol to acquire a second image. A sequence control unit that controls execution of a series of protocol groups,
A display unit that displays the first image obtained by executing the first protocol ;
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 the position information of the feature region, during execution of the second protocol, the noise canceling sound corresponding to the second protocol, a speaker for sending to the characteristic site,
A magnetic resonance imaging apparatus comprising: A calculating unit configured to calculate the positional shift amount of the characteristic portion by comparing the first image and the second image,
The speaker transmits the noise canceling sound to a position corrected based on the amount of displacement of the characteristic portion during execution of the second protocol .
The magnetic resonance imaging apparatus according to claim 1. A plurality of the second images are acquired during execution of the second protocol,
The calculation unit calculates the pre-Symbol position location deviation amount by comparing a plurality of said second image,
A voice acquisition unit configured to set the noise canceling sound corresponding to the displaced feature during the execution of the second protocol, based on at least one of the position information and the pulse sequence of the feature. Further having
The magnetic resonance imaging apparatus according to claim 2. The second protocol is executed plurally,
The calculating unit, in a plurality of said second protocol, to calculate the position location shift amount that put between the second protocol that is executed after a second protocol that is executed first,
The speaker magnetic resonance imaging apparatus according to claim 2 for sending said noise canceling sound corresponding to the characteristic portions of the second protocol are executed have you to a plurality of the second protocol, after. The characteristic portion is a magnetic resonance imaging apparatus according to any one of the four said claims 1 which is the site involved in the hearing of the subject. The magnetic resonance imaging apparatus according to any one of claims 1 to 4, wherein the loudspeakers are arranged at a plurality of locations on an inner circumference of the imaging opening. Further comprising a receiving coil attached to the subject,
The magnetic resonance imaging apparatus according to any one of claims 1 to 4, wherein the speaker is disposed in the reception coil. And a microphone to get the noise,
Setting of the noise canceling sound, which is a sound having the opposite phase, the same amplitude, and the same frequency with respect to the noise obtained by the microphone , based on at least one of the position information of the characteristic portion and the pulse sequence. A voice acquisition unit that performs
Further magnetic resonance imaging apparatus according to claim 1, any one of 4 with. Further comprising 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 with respect to the subject, and during the execution of the pulse sequence, causes the speaker to transmit noise canceling sounds corresponding to noise at a plurality of positions. Receiving any of the plurality of positions as the characteristic portion by receiving input information from
The magnetic resonance imaging apparatus according to any one of claims 1 4.   The magnetic resonance imaging apparatus according to claim 9, wherein the calibration unit accepts adjustment of a position of a destination of the noise canceling sound in a state where an RF pulse is not transmitted to the subject. The same object including a first protocol for acquiring a first image by imaging the object and a second protocol executed after the first protocol to acquire a second image. A sequence control unit that controls execution of a series of protocol groups,
A display unit for acquiring the first image acquired by executing the first protocol ;
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 obtains a sound transmitted from the characteristic portion during execution of the second protocol, based on the position information of the characteristic portion;
An audio adjustment unit that adjusts the sound acquired by the microphone,
A magnetic resonance imaging apparatus comprising: A calculating unit configured to calculate the positional shift amount of the characteristic portion 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, a sound transmitted from the characteristic part via the microphone is acquired, and the sound adjustment is performed based on the positional displacement amount. Magnetic resonance imaging equipment. A plurality of the second images are acquired during execution of the second protocol,
The calculation unit calculates the pre-Symbol position location deviation amount by comparing a plurality of said second image,
13. The magnetic resonance imaging apparatus according to claim 12, wherein the sound adjustment unit obtains a sound transmitted from the characteristic part via the microphone, and adjusts the sound based on the positional shift amount. The second protocol is executed plurally,
The calculating unit, in a plurality of said second protocol, to calculate the position location shift amount that put between the second protocol that is executed after a second protocol that is executed first,
The microphone acquires a sound transmitted from the characteristic portion during execution of the plurality of second protocols,
13. The magnetic resonance imaging apparatus according to claim 12, wherein the audio adjustment unit adjusts the sound during execution of the plurality of second protocols. The magnetic resonance imaging apparatus according to any one of claims 11 to 14, further comprising a speaker that sends the sound adjusted by the audio adjustment unit to an operator. The magnetic resonance imaging apparatus according to any one of claims 11 to 14, wherein the characteristic portion is a portion related to the utterance of the subject. The magnetic resonance imaging apparatus according to any one of claims 11 to 14, wherein the microphone is arranged on a circumference at a plurality of positions in an imaging opening. Further comprising a receiving coil attached to the subject,
The magnetic resonance imaging apparatus according to any one of claims 11 to 14, wherein the microphone is arranged in the receiving coil. Further comprising a calibration unit for adjusting the position information about the utterance site of the sound from the subject,
The calibration unit executes a pulse sequence on the subject, during the execution of the pulse sequence, the sounds acquired by the plurality of microphones, based on the displacement amount read from the calculation unit. Outputting, from the sound adjusting unit, sounds adjusted corresponding to a plurality of positions, and receiving input information of an operator from the input unit, thereby receiving any of the plurality of positions as the characteristic portion. 15. The magnetic resonance imaging apparatus according to any one of 12 to 14.   20. The magnetic resonance imaging apparatus according to claim 19, wherein the calibration unit receives adjustment of a position of a sound utterance part from the subject in a state where the RF pulse is not transmitted to the subject. The magnetic resonance according to any one of claims 1, 2, 3, 4, 11, 12, 13, and 14, wherein the first image is an MPR image generated from three-dimensional MR data of the subject. Imaging device. An optical imaging unit for obtaining a third image taken through the patient,
A calculating unit that calculates the positional shift amount of the characteristic portion by comparing the first image and the third image;
A sound acquisition unit that acquires the noise canceling sound corresponding to the characteristic portion after the displacement based on the displacement amount calculated by the calculation unit;
The magnetic resonance imaging apparatus according to claim 1, further comprising: An optical imaging unit for obtaining a third image taken through the patient,
A calculating unit that calculates the positional shift amount of the characteristic portion by comparing the first image and the third image;
A sound adjustment unit that obtains a sound transmitted from the characteristic portion after the displacement based on the displacement amount calculated by the calculation unit, and adjusts the sound based on the displacement amount,
The magnetic resonance imaging apparatus according to claim 11, further comprising: