MAGNETIC RESONANCE APPARATUS AND PROGRAM

Abstract

Methods and systems are disclosed herein for selecting a channel adapted to detection of the position of a liver. The position “m” of the border between the liver and the lung is obtained from a profile. A sum Sliver of signal intensities in a liver region R1 and a sum Slung of signal intensities in a lung region R2 are calculated. Sliver and Slung are compared. In the case where Sliver is equal to or less than Slung (Sliver≤Slung), a channel is not selected as a channel used at the time of detecting the position of the edge of the liver. On the other hand, in the case where Sliver is larger than Slung (Sliver>Slung), a channel is selected as a channel used at the time of detecting the position of the edge of the liver.

Description

BACKGROUND

The present invention relates to a magnetic resonance apparatus obtaining a navigator signal generated from a navigator region including a body site which moves by using a coil having a plurality of channels and to a program applied to the magnetic resonance apparatus.

Respiration synchronization imaging using a navigator signal is known, refer to Japanese Patent Application No. 2011-193884.

SUMMARY

In recent years, a multi-channel coil having a plurality of channels is spread, and aspiration synchronization imaging using the multi-channel coil is performed. In the imaging, generally, a navigator region is set in a border position of the liver and the lung and a navigator signal is acquired from the navigator region by the multi-channel coil. On the basis of the navigator signals acquired by the channels in the multi-channel, the position of the edge of the liver is detected. There is, however, a case that depending on the channels, the signal of the lung region is strong. In the case where the signal of the lung region is strong, there is a problem that the detection precision of the position of the liver is low. Therefore, a technique capable of selecting a channel suitable to detect the position of the liver from the plurality of channels in the case where a channel acquiring the strong signal of the lung region is included in the plurality of channels is demanded.

A first aspect of the present invention relates to a magnetic resonance apparatus obtaining a navigator signal generated from a navigator region including a first body site which moves and a second body site which moves by using a coil having a plurality of channels, including:

scan means executing a first navigator sequence for obtaining a first navigator signal generated from the navigator region;

profile generating means generating a first profile expressing relation between each position in the navigator region and signal intensity for each of the channels on the basis of the first navigator signal received by each of the plurality of channels;

means obtaining a first region corresponding to the first body site in the first profile and a second region corresponding to the second body site in the first profile; and

selecting means selecting a channel used to obtain the position of the first body site from the plurality of channels on the basis of a feature amount of the signal intensity in the first region and a feature amount of the signal intensity in the second region.

A second aspect of the present invention relates to a program applied to a magnetic resonance apparatus executing a first navigator sequence for obtaining a first navigator signal generated from a navigator region including a first body site which moves and a second body site which moves by using a coil having a plurality of channels, the program for making a computer execute:

a profile generating process generating a first profile expressing relation between each position in the navigator region and signal intensity for each of the channels on the basis of the first navigator signal received by each of the plurality of channels;

a process obtaining a first region corresponding to the first body site in the first profile and a second region corresponding to the second body site in the first profile; and

a selecting process selecting a channel used to obtain the position of the first body site from the plurality of channels on the basis of a feature amount of the signal intensity in the first region and a feature amount of the signal intensity in the second region.

A channel is selected on the basis of the feature amount of the signal intensity in the first region and the feature amount of the signal intensity in the second region. Therefore, a channel adapted to obtain the position of the first body site can be selected.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic diagram illustrating a magnetic resonance apparatus as an embodiment of the present invention.

FIG. 2 is an explanatory diagram of a receiver coil 4.

FIG. 3 is a diagram illustrating scans executed in a first mode.

FIG. 4 is a diagram schematically illustrating an imaging region.

FIG. 5 is an explanatory diagram of a sequence executed by a pre-scan A.

FIG. 6 is a diagram illustrating the flow at the time of executing a navigator sequence NAV at time t₁ and detecting the position of the edge of the liver at time t₁.

FIG. 7 is a diagram schematically illustrating profiles F₁ to F_m+n obtained by channels CH₁ to CH_m+n of the receiver coil 4.

FIG. 8 is an explanatory diagram at the time of determining whether the channel CH₁ is selected or not.

FIG. 9 is a diagram illustrating a result of comparison between S_liver and S_lung.

FIG. 10 is a diagram illustrating channels CH₂ to CH_m and CH_m+2 to CH_m+n.

FIG. 11 is an explanatory diagram at the time of acquiring the position of the edge of the liver.

FIG. 12 is a diagram illustrating the flow at the time of executing the navigator sequence NAV at time t₂ and detecting the position of the edge of the liver at time t₂.

FIG. 13 is a diagram schematically illustrating profiles F₂ to F_m and F_m+2 to F_m+n generated.

FIG. 14 is a diagram schematically illustrating a composite profile Fc.

FIG. 15 is a diagram illustrating an example of a trigger level TL.

FIG. 16 is an explanatory diagram of a main scan B.

FIG. 17 is an explanatory diagram of an example of a method of selecting a channel by using a template TI.

FIG. 18 is a diagram schematically illustrating a composite profile X obtained by using a method of using the template TI.

DETAILED DESCRIPTION

Hereinafter, modes for carrying out the invention will be described. The present invention, however, is not limited to the following modes.

FIG. 1 is a schematic diagram illustrating a magnetic resonance apparatus as an embodiment of the present invention. A magnetic resonance apparatus (hereinbelow, called an “MR apparatus”) 100 has a magnet 2, a table 3, a receiver coil 4, and the like.

The magnet 2 has a bore 21 in which a subject 10 is put. The magnet 2 has therein a superconductive coil, a gradient coil, an RF coil, and the like.

The table 3 has a cradle 3a supporting the subject 10. The cradle 3a is configured to be movable in the bore 21. By the cradle 3a, the subject 10 is carried into the bore 21. The receiver coil 4 receives a magnetic resonance signal from the subject 10.

FIG. 2 is an explanatory diagram of the receiver coil 4. The receiver coil 4 has a first coil unit 41 and a second coil unit 42. The first coil unit 41 has m pieces of channels CH₁ to CH_m for receiving a magnetic resonance signal from the subject, and the second coil unit 42 has n pieces of channels CH_m+1 to CH_m+n for receiving a magnetic resonance signal from the subject. Therefore, in the embodiment, the receiver coil 4 is constructed as an (m+n)-channel coil. The first coil unit 41 is disposed on the abdomen side of the subject, and the second coil unit 42 is disposed on the back side of the subject. Referring again to FIG. 1, the description will be continued.

The MR apparatus 100 further has a transmitter 5, a gradient magnetic field power supply 6, a control unit 7, an operating unit 8, a display unit 9, and the like. The transmitter 5 supplies current to the RF coil, and the gradient magnetic field power supply 6 supplies current to the gradient coil. A combination of the magnet 2, the receiver coil 4, the transmitter 5, and the gradient magnetic field power supply 6 corresponds to scan means.

The control unit 7 controls the operations of the components of the MR apparatus 100 so as to realize various operations of the MR apparatus 100 such as transmission of necessary information to the display unit 9 and reconfiguration of an image on the basis of signals received from the receiver coil 4. The control unit 7 includes profile generating means 71 to position detecting means 75.

The profile generating means 71 generates a profile expressing the relation between each of positions in the navigator region and signal intensity. Specifying means 72 specifies a region corresponding to liver and a region corresponding to lung in each profile. Calculating means 73 calculates a sum of signal intensities in the liver region and a sum of signal intensities in the lung region. Selecting means 74 selects a channel adapted to detect the position of the edge of the liver from the channels CH₁ to CH_m+n of the receiver coil 4 on the basis of the sum of the signal intensities in the liver region and the sum of signal intensities in the lung region. The position detecting means 75 detects the position of the edge of the liver.

The control unit 7 is an example of constructing the profile generating means 71 to the position detecting means 75 and functions as those means by executing a predetermined program.

The operating unit 8 is operated by the operator and enters various information to the control unit 7. The display unit 9 displays various information. The MR apparatus 100 is constructed as described above.

FIG. 3 is a diagram illustrating scans executed in a first mode, and FIG. 4 is a diagram schematically illustrating an imaging region. In the first embodiment, a pre-scan A and a main scan B are executed.

The pre-scan A is a scan executed to determine a trigger level TL (refer to FIG. 16) which will be described later. The trigger level TL will be described later. The main scan B is a scan for imaging the liver. Hereinbelow, the pre-scan A and the main scan B will be described in order.

FIG. 5 is an explanatory diagram of a sequence executed by the pre-scan A. In the pre-scan A, a navigator sequence NAV is repeatedly executed. The navigator sequence NAV is a sequence for collecting a navigator signal from a navigator region R_nav.

In the pre-scan A, first, the navigator sequence NAV is executed at time t1 to detect the position of the edge of the liver at time t1 (refer to FIG. 6).

FIG. 6 is a diagram illustrating the flow at the time of executing the navigator sequence NAV at time t1 and detecting the position of the edge of the liver at time t1.

In step ST1, the navigator sequence NAV is executed at time t1. By executing the navigator sequence NAV, the navigator signal is obtained from the navigator region R_nav. The navigator signal is received by each of the channels CH₁ to CH_m+n of the reception coil 4. The profile generating means 71 (refer to FIG. 1) converts the navigator signal obtained by each of the channels CH₁ to CH_m+n of the reception coil 4 to a profile expressing the relation between each position in the SI direction of the navigator region R_nav and signal intensity. By the operation, a profile is generated for each of the channels of the reception coil 4. FIG. 7 schematically illustrates profiles F₁ to F_m+n obtained by the channels CH₁ to CH_m+n of the reception coil 4, respectively. The navigator sequence NAV is designed so that a high signal corresponds to the liver and the low signal corresponds to the lung. Therefore, by detecting the position where the signal values of the profiles F₁ to F_m+1 change drastically, the position of the edge of the liver at time t1 can be detected. For example, referring to the profile F₂, the signal intensity changes drastically in position x, so that the position x can be therefore considered as the position of the edge of the liver. In some embodiments, drastic change means that the change exceeds a predefined threshold.

There is, however, the case that, depending on the channels of the coil, the signal intensity in the region of the lung in the profile is high. For example, in the profile Fi, the signal intensity in the region of the lung is high. When the signal intensity in the region of the lung is high as described above, the position where the signal intensity changes drastically appears not only in the vicinity of the edge of the liver but also in the region of the lung. It causes erroneous detection of the position of the edge of the liver. Therefore, although (m+n) pieces of the profiles F₁ to F_m+n are obtained by the channels CH₁ to CH_m+n, it does not mean that a profile suitable to detect the position of the edge of the liver is obtained from all of the channels.

It is consequently necessary to select a channel from which a profile suitable to detect the position of the edge of the liver from the channels CH₁ to CH_m+n. To select a channel, the program advances to step ST2.

In step ST2, on the basis of the profiles of the channels, a channel used at the time of detecting the position of the edge of the liver is selected from the channels CH₁ to CH_m+n. Hereinafter, a method of selecting a channel in the embodiment will be described.

In the case of selecting a channel, whether or not the channel CH₁ is selected as a channel used at the time of detecting the position of the edge of the liver from the channels CH₁ to CH_m+1 is determined. The determination is performed as follows.

FIG. 8 is an explanatory diagram at the time of determining whether the channel CH₁ is selected or not.

First, the specifying means 72 (refer to FIG. 1) obtains position “b” of the border between the liver and the lung on the basis of the profile F₁ of the channel CH₁. As a method of obtaining the position “b” of the border, various methods are considered. For example, by combining all of the profiles F₁ to F_m+n, a composite profile is obtained. The position where the signal intensity changes drastically is detected from the composite profile, and the detected position can be considered as the position “b” of the border in the profile F₁.

It is sufficient that the position “b” of the border expresses a rough position of the border between the liver and the lung, and it is unnecessary to accurately obtain the position of the border. Therefore, an intermediate position in the SI direction of the navigator region may be set as the position “b” of the border.

The specifying means 72 specifies two regions in the profile F₁ using the position “b” of the border as a reference, that is, a region R₁ corresponding to the liver (hereinbelow, called “liver region”) and a region R₂ corresponding to the lung (hereinbelow, called “lung region”).

Next, the calculating means 73 (refer to FIG. 1) calculates a sum S_liver of signal intensities in the liver region R1 and a sum S_lung of signal intensities in the lung region R2. The sums S_liver and S_lung of the signal intensities can be obtained by the following equations.

$\begin{array}{cc}{S}_{\mathrm{liver}}=\sum _{i=1}^{b-1}\mathrm{Si}& \left(1\right)\\ S_{\mathrm{lung}}=\sum _{i=b}^z\mathrm{Si}& \left(2\right)\end{array}$

where i: position in the SI direction, and Si: signal intensity in the position “i”.

After obtaining the sums S_liver and S_lung of the signal intensities, the selecting means 74 (refer to FIG. 1) compares S_liver and S_lung and determines whether S_liver is equal to or less than S_lung. In the case where S_liver is equal to or less than S_lung (S_liver≤S_lung), it is considered that the signal intensity in the region of the lung is high, so that the selecting means 74 determines not to select the channel CH₁ as a channel used at the time of detecting the position of the edge of the liver. On the other hand, in the case where S_liver is larger than S_lung (S_liver>S_lung), it is considered that the signal intensity in the region of the lung is low, so that the selecting means 74 selects the channel CH₁ as a channel used at the time of detecting the position of the edge of the liver.

It is assumed here that S_liver≤S_lung. Therefore, the selecting means 74 determines not to select the channel CH₁ as a channel used at the time of detecting the position of the edge of the liver.

Similarly, the position “b” of the border is set also for the profile F₂ of the channel CH₂ to the profile F_m+n of the channel CH_m+n, and the sums S_liver and S_lung of the signal intensities are calculated by the equations (1) and (2). S_liver and S_lung are compared. In the case where S_liver≤S_lung, the selecting means 74 determines not to select the channel as a channel used at the time of detecting the position of the edge of the liver. On the other hand, in the case of S_liver>S_lung, the selecting means 74 selects the channel as a channel used at the time of detecting the position of the edge of the liver. FIG. 9 illustrates a result of comparison between S_liver and S_lung in each of the profiles F₁ to F_m+n of the channels CH₁ to CH_m+n. It is assumed that S_liver≤S_lung is satisfied in the profile F₁ of the channel CH₁ and the profile F_m+1 of the channel CH_m+1, and S_liver>S_lung is satisfied in the profiles of the other channel CH₂ to CH_m and CH_m+2 to CH_m+n. Therefore, the selecting means 74 determines not to select the channels CH₁ and CH_m+1 as channels used at the time of detecting the position of the edge of the liver, and to select the other channels CH₂ to CH_m and the channels CH_m+2 to CH_m+n as channels used at the time of detecting the position of the edge of the liver. In FIG. 10, the channels CH₂ to CH_m and CH_m+2 to CH_m+n are indicated by thick broken lines. After selecting the channels, the program advances to step ST3.

In step ST3, based on the profiles F₂ to F_m and F_m+2 to F_m+n obtained by the channels CH₂ to CH_m and CH_m+2 to CH_m+n, the position of the edge of the liver at time t1 is obtained (refer to FIG. 11).

FIG. 11 is an explanatory diagram at the time of acquiring the position of the edge of the liver. The position detecting means 75 (refer to FIG. 1), first, combines the profiles F₂ to F_m and F_m+2 to F_m+n to obtain a composite profile Fc. In this case, the position detecting means 75 obtains the composite profile Fc by calculating the root mean of the signal intensities of the profiles F₂ to F_m and F_m+2 to F_m+n.

The position detecting means 75 detects the position i=i1 where the signal intensity changes drastically from the composite profile Fc. Consequently, the position i1 (refer to FIG. 5) of the edge of the liver at time t1 can be detected. By combining the profiles F₂ to F_m and F_m+2 to F_m+n, the SN ratio can be increased, so that the detection precision of the position of the edge of the liver can be improved. After obtaining the position i1 of the edge, the flow of FIG. 6 is finished.

After detecting the position p1 of the edge of the liver at time t1, the navigator sequence is executed at the following time t2.

FIG. 12 is a diagram illustrating the flow at the time of executing the navigator sequence NAV at time t2 and detecting the position of the edge of the liver at time t2.

In step ST1, the navigator sequence NAV is executed at time t2. By executing the navigator sequence NAV, the navigator signal is obtained from the navigator region R_nav. The profile generating means 71 converts the navigator signals received by the channels CH₂ to CH_m and CH_m+2 to CH_m+n (refer to FIG. 10) to profiles each expressing the relation between each position in the SI direction of the navigator region R_nav and signal intensity. By the conversion, profiles are generated for the channels CH₂ to CH_m and CH_m+2 to CH_m+n. FIG. 13 schematically illustrates the profiles F₂ to F_m and F_m+2 to F_m+n generated. After obtaining the profiles F₂ to F_m and F_m+2 to F_m+n, the position detecting means 75 calculates the root mean of the signal intensities of the profiles F₂ to F_m and F_m+2 to F_m+n to obtain the composite profile Fc. FIG. 14 schematically illustrates the composite profile Fc.

The position detecting means 75 detects the position i2 where the signal intensity changes drastically from the composite profile Fc. In such a manner, the position i2 (refer to FIG. 5) of the edge of the liver at time t2 can be detected.

Similarly, also at time t3 to tz (refer to FIG. 5), according to the flow shown in FIG. 12, the navigator sequence NAV is executed, and profiles are generated by using the navigator signals received in the selected channels CH₂ to CH_m and CH_m+2 to CH_m+n. The profiles are combined and the position of the edge of the liver is detected from the composite profile.

Therefore, as illustrated in FIG. 5, data of the positions i1 to iz of the edge of the liver at time t1 to tz can be obtained. After obtaining the data, on the basis of the data of the positions i1 to iz of the edge of the liver, the trigger level TL is determined. FIG. 15 is a diagram illustrating an example of the trigger level TL. The trigger level TL expresses the reference position of the edge of the liver at the time of executing a data acquisition sequence DAQ (refer to FIG. 16) in the main scan B which will be described later. The trigger level TL can be set, for example, in an intermediate value between the maximum value and the minimum value of the position of the edge of the liver. How the trigger level TL is used at the time of executing the main scan B will be described later. After executing the pre-scan A, the main scan B is executed.

FIG. 16 is an explanatory diagram of the main scan B. In the main scan B, the navigator sequence NAV and the data acquisition sequence DAQ for acquiring data of the liver are executed.

Also in the main scan B, the navigator system NAV is executed according to the flow illustrated in FIG. 12 to detect the position of the edge of the liver.

In such a manner, changes with time of the position of the edge of the liver are monitored. When the position of the edge of the liver moves from the upper side of the trigger level TL to the lower side, the data acquisition sequence DAQ is executed.

Similarly, the navigator sequence NAV and the data acquisition sequence DAQ are repeatedly executed, and the main scan B is finished. On the basis of the data acquired by the main scan B, an image of the liver is reconstructed, and the imaging of the subject is finished.

In the embodiment, the sum S_liver of signal intensities in the liver region and the sum S_lung of signal intensities in the lung region are compared, and a channel where S_liver>S_lung is satisfied is selected as a channel used to detect the position of the edge of the liver. Therefore, a channel where S_liver≤S_lung is satisfied is not selected as a channel used to detect the position of the edge of the liver, so that the precision of detection of the position of the edge of the liver can be increased.

In the embodiment, the sum S_liver of signal intensities in the liver region and the sum S_lung of signal intensities in the lung region are calculated. However, if a feature amount of the signal intensities in the liver region and a feature amount of the signal intensities in the lung region can be obtained, values different from the sums S_liver and S_lung of the signal intensities may be calculated. For example, an average value S1 of the signal intensities in the liver region may be calculated in place of the sum S_liver of signal intensities in the liver region, and an average S2 of the signal intensities in the lung region may be calculated in place of the sum S_lung of the signal intensities of the lung region. In the case of calculating the average values S1 and S2 of the signal intensities, it is sufficient to select a channel where S1>S2 is satisfied as a channel used to detect the position of the edge of the liver. In this case, a channel where S1≤S2 is satisfied is not selected as a channel used to detect the position of the edge of the liver, so that the precision of detection of the position of the edge of the liver can be increased.

In the embodiment, by comparing the sum S_liver of signal intensities in the liver region and the sum S_lung of signal intensities in the lung region, a channel is selected. On the other hand, it is also considered to prepare a template expressing an ideal signal intensity of each position in the navigator region, obtain a correlation coefficient between the template and each profile, and select a channel where the correlation coefficient is large (refer to FIG. 17).

FIG. 17 is an explanatory diagram of an example of a method of selecting a channel by using a template TI.

In FIG. 17, the template TI is illustrated. The template TI is data expressing ideal signal intensity in each position in the navigator region. In the method using the template TI, correlation coefficients C₁ to C_m+n between the template TI and the profiles F₁ to F_m+n are obtained, and a channel in which the correlation coefficient is large is selected from the channels CH1 to CH_m+n. Therefore, a channel in which the correlation coefficient is small is not selected, so that the precision of detecting the position of the edge of the liver can be increased. In this method, however, it is considered to select only a channel in which the correlation coefficient is as high as possible. The number of channels selected is small and, generally, it is set to select only the channel in which the correlation coefficient is the largest and the channel in which the correlation coefficient is the second largest (that is, two channels). For example, when it is assumed that, in FIG. 17, the correlation coefficient C₂ of the channel CH₂ is the largest and the correlation coefficient C_m+2 of the channel CH_m+2 is the second largest in the correlation coefficients C₁ to C_m+n, only the two channels CH₂ and CH_m+2 are selected. Therefore, in the method using the template TI, a profile F₂ of the channel CH₂ and a profile F_m+2 of the channel CH_m+2 are combined (refer to FIG. 18).

FIG. 18 is a diagram schematically illustrating a composite profile X obtained by using the method of using the template TI. In FIG. 18, the composite profile Fc obtained by the method of the embodiment is also illustrated.

There is a case that signal unevenness appears in the liver region of the profile depending on imaging parameters or the like. FIG. 18 illustrates an example where signal unevenness appears in the liver region in the profile F₂. Generally, the signal unevenness in the liver region tends to appear as the number of channels of the coil becomes larger. In the case where such signal unevenness appears in the profile F₂, only by combining the profiles F₂ and F_m+2, signal unevenness in the profile F₂ cannot be sufficiently reduced, and signal unevenness appears also in the region of the liver in the composite profile X. When signal unevenness appears in the composite profile X, it causes deterioration in the precision of detecting the position of the edge of the liver.

On the other hand, in the embodiment, the template TI is not used. The sum S_liver of signal intensities in the liver region and the sum S_lung of signal intensities in the lung region are compared, and a channel where S_liver>S_lung is satisfied is selected as a channel used to detect the position of the edge of the liver. Therefore, the channel where S_liver>S_lung is satisfied is selected as a channel used to detect the position of the edge of the liver regardless of the correlation coefficient. Consequently, in the method of the embodiment, as compared with the method using the template, larger number of channels can be selected as channels used at the time of detecting the position of the edge of the liver. Referring to FIG. 18, it is understood that, in the method using the template, only the channels CH₂ and CH_m+2 (that is, two channels) are selected and, in the method of the embodiment, the channels CH₂ to CH_m and CH_m+2 to CH_m+n are selected. Therefore, in the method of the embodiment, larger number of profiles are combined than that in the method using the template, so that the composite profile Fc in which the influence of the signal unevenness of the channel CH₂ is sufficiently reduced can be obtained, and the precision of detecting the position of the edge of the liver can be improved.

In the embodiment, the navigator region R_nav is set so as to include the liver and the lung. As long as a body site which is moves is included, the navigator region R_nav may include parts different from the liver or lung. For example, the navigator region R_nav may be set so as to include the liver and the heart.

In the embodiment, on the basis of a navigator signal obtained by the navigator sequence NAV at the time t1 of the pre-scan A, a channel used to detect the position of the edge of the liver is selected from the channels CH₁ to CH_m+n. It is also possible to execute the navigator sequence NAV for selecting a channel twice or more and select a channel on the basis of navigator signals obtained by the navigator sequences NAV.

In the embodiment, the position of the edge of the liver is detected according to the flow of FIG. 6 at time t1 and the position of the edge of the liver is detected according to the flow of FIG. 12 at time t2 and after that. However, also at time t2 and after that, the position of the edge of the liver may be detected according to the flow of FIG. 6.

In the embodiment, the example of acquiring data by triggering has been described. The present invention, however, is not limited to triggering but can be applied to any imaging as long as a navigator signal has to be received by a coil having a plurality of channels.

Claims

1. A method comprising: acquiring, by a receiver coil that comprises a plurality of channels, magnetic resonance (MR) signals generated from a navigator region including a first body site and a second body site;for each channel of the plurality of channels: setting a rough position of a border between a first region corresponding to the first body site and a second region corresponding to the second body site;determining a sum of signal intensities in the first region;determining a sum of signal intensities in a second region;comparing the sum of signal intensities in the first region with the sum of signal intensities in the second region;selecting the channel for determining an edge of the first region in response to the sum of signal intensities in the first region being greater than the sum of signal intensities in the second region; andnot selecting the channel for determining the edge of the first region in response to the sum of signal intensities in the first region being equal to or less than the sum of signal intensities in the second region.

2. The method of claim 1, wherein the first body site and the second body site are in motion.

3. The method of claim 1, wherein the first body site is a liver and the second body site is a lung.

4. The method of claim 1, further comprises, for each channel of the plurality of channels: generating a profile representing the signal intensity at each position in SI direction of the navigator region; andsetting the rough position of the border at a position where the signal intensity in the profile changes drastically.

5. The method of claim 1, further comprising, for each channel of the plurality of channels: generating a profile representing the signal intensity at each position in SI direction of the navigator region;combining the profiles of the selected channels to obtain a composite profile; anddetecting the edge of the first region at a position where the signal strength in the composite profile changes drastically.

6. A magnetic resonance imaging (MRI) apparatus comprising: a receiver coil that comprises a plurality of channels, wherein the receiver coil is configured to acquire magnetic resonance (MR) signals generated from a navigator region including a first body site and a second body site; anda control unit configured to, for each channel of the plurality of channels: set a rough position of a border between a first region corresponding to the first body site and a second region corresponding to the second body site;determine a sum of signal intensities in the first region;determine a sum of signal intensities in a second region;compare the sum of signal intensities in the first region with the sum of signal intensities in the second region;select the channel for determining an edge of the first region in response to the sum of signal intensities in the first region being greater than the sum of signal intensities in the second region; andnot select the channel for determining the edge of the first region in response to the sum of signal intensities in the first region being equal to or less than the sum of signal intensities in the second region.

7. The MRI apparatus of claim 6, wherein the first body site and the second body site are in motion.

8. The MRI apparatus of claim 6, wherein the first body site is a liver and the second body site is a lung.

9. The MRI apparatus of claim 6, wherein the control unit is further configured to, for each channel of the plurality of channels: generate a profile representing the signal intensity at each position in SI direction of the navigator region; andset the rough position of the border at a position where the signal intensity in the profile changes drastically.

10. The MRI apparatus of claim 6, wherein the control unit is further configured to, for each channel of the plurality of channels: generate a profile representing the signal intensity at each position in SI direction of the navigator region;combine the profiles of the selected channels to obtain a composite profile; anddetect the edge of the first region at a position where the signal strength in the composite profile changes drastically.