阅读说明：本技术 用于对倾斜扫描进行波形优化的系统和方法 (System and method for waveform optimization for tilt scanning ) 是由 阿里·埃尔索兹 于 2019-08-12 设计创作，主要内容包括：本发明题为“用于对倾斜扫描进行波形优化的系统和方法”。提供了用于对倾斜成像的梯度波形进行优化的方法和系统。在一个实施方案中,方法包括：在逻辑轴中生成初始梯度波形；评估初始梯度波形中的每个初始梯度波形的面积需求；增加第一逻辑轴中的初始梯度波形的最大振幅；减小第二逻辑轴中的初始梯度波形的最大振幅,其中第一逻辑轴中的面积需求大于第二逻辑轴中的面积需求；将梯度波形转换为物理梯度波形；以及在扫描期间利用物理梯度波形来驱动成像系统的物理放大器。这样,可在不具有因回波时间、重复时间和回波间隔增加引起的性能降低的情况下执行倾斜扫描。(The invention provides a system and method for waveform optimization for tilt scanning. Methods and systems for optimizing gradient waveforms for oblique imaging are provided. In one embodiment, a method comprises: generating an initial gradient waveform in a logical axis; evaluating an area requirement of each of the initial gradient waveforms; increasing the maximum amplitude of the initial gradient waveform in the first logical axis; reducing the maximum amplitude of the initial gradient waveform in a second logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the second logical axis; converting the gradient waveforms into physical gradient waveforms; and driving a physical amplifier of the imaging system with the physical gradient waveform during the scan. In this way, the tilt scan can be performed without performance degradation due to increased echo time, repetition time, and echo spacing.)

1. A method for performing a tilt scan of Magnetic Resonance (MR), comprising:

generating an initial gradient waveform in logical axes, the logical axes including a frequency encoding axis, a phase encoding axis, and a slice selection axis;

evaluating an area requirement for each of the logical axes;

increasing a maximum amplitude of the initial gradient waveform in a first logical axis;

reducing a maximum amplitude of the initial gradient waveform in a second logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the second logical axis;

converting the altered gradient waveforms to physical gradient waveforms; and

driving a physical amplifier of an imaging system with the physical gradient waveform during the tilt scan of the MR.

2. The method of claim 1, wherein the maximum amplitudes of the initial gradient waveforms in the logical axes are equal.

3. The method of claim 1, further comprising increasing a slew rate of the initial gradient waveform in the first logical axis.

4. The method of claim 1, further comprising reducing a pulse width of the initial gradient waveform in the first logical axis.

5. The method of claim 1, further comprising reducing a slew rate of the initial gradient waveform in the second logical axis.

6. The method of claim 1, further comprising increasing a pulse width of the initial gradient waveform in the second logical axis.

7. The method of claim 1, further comprising reducing a maximum amplitude of the initial gradient waveform in a third logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the third logical axis.

8. A magnetic resonance imaging system comprising:

a gradient coil unit comprising a first gradient coil, a second gradient coil, and a third gradient coil, each gradient coil defining a physical axis;

a gradient coil driver unit including first, second and third amplifiers electrically coupled to the first, second and third gradient coils, respectively;

a processor communicatively coupled to the gradient coil driver unit and configured to:

generating an initial gradient waveform in logical axes, the logical axes including a frequency encoding axis, a phase encoding axis, and a slice selection axis;

evaluating an area requirement for each of the logical axes;

increasing a maximum amplitude of the initial gradient waveform in a first logical axis;

reducing a maximum amplitude of the initial gradient waveform in a second logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the second logical axis;

converting the altered gradient waveforms to physical gradient waveforms; and

the gradient coil driver unit is driven with the physical gradient waveforms during a tilt scan.

9. The system of claim 8, wherein the maximum amplitudes of the initial gradient waveforms in the logical axes are equal.

10. The system of claim 8, wherein the processor is further configured to increase a slew rate of the initial gradient waveform in the first logical axis.

11. The system of claim 8, wherein the processor is further configured to reduce a pulse width of the initial gradient waveform in the first logical axis.

12. The system of claim 8, wherein the processor is further configured to reduce a slew rate of the initial gradient waveform in the second logical axis.

13. The system of claim 8, wherein the processor is further configured to increase a pulse width of the initial gradient waveform in the second logical axis.

14. A non-transitory computer-readable medium comprising instructions that, when executed, cause a processor to:

generating an initial gradient waveform in logical axes, the logical axes including a frequency encoding axis, a phase encoding axis, and a slice selection axis;

evaluating an area requirement for each of the logical axes;

increasing a maximum amplitude of the initial gradient waveform in a first logical axis;

reducing a maximum amplitude of the initial gradient waveform in a second logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the second logical axis;

converting the altered gradient waveforms to physical gradient waveforms; and

the physical gradient waveforms are utilized during a tilt scan to drive a physical amplifier of a magnetic resonance imaging system.

15. The computer-readable medium of claim 14, wherein the maximum amplitudes of the initial gradient waveforms in the logical axes are equal.

16. The computer-readable medium of claim 14, further comprising instructions that when executed cause the processor to increase a slew rate of the initial gradient waveform in the first logical axis.

17. The computer-readable medium of claim 14, further comprising instructions that when executed cause the processor to reduce a pulse width of the initial gradient waveform in the first logical axis.

18. The computer-readable medium of claim 14, further comprising instructions that when executed cause the processor to reduce a slew rate of the initial gradient waveform in the second logical axis.

19. The computer readable medium of claim 14, further comprising instructions that when executed cause the processor to increase a pulse width of the initial gradient waveform in the second logical axis.

20. The computer readable medium of claim 14, further comprising instructions that when executed cause the processor to reduce the maximum amplitude of the initial gradient waveform in a third logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the third logical axis.

Technical Field

Embodiments of the subject matter disclosed herein relate to Magnetic Resonance Imaging (MRI), and more particularly, to optimizing gradient waveforms for oblique imaging.

Background

Magnetic Resonance Imaging (MRI) is a medical imaging modality that can produce images of the interior of the human body without the use of x-rays or other ionizing radiation. MRI uses superconducting magnets to generate a strong, consistent, steady magnetic field. When a human body or a part of a human body is placed in a magnetic field, the nuclear spins associated with the hydrogen nuclei in the tissue water become polarized, with the magnetic moments associated with these spins becoming preferentially aligned in the direction of the magnetic field, resulting in a small net tissue magnetization along that axis. The MRI system further includes gradient coils that generate small amplitude, spatially varying magnetic fields with orthogonal axes to spatially encode the MR signals by generating characteristic resonance frequencies at each location in the body. Radio Frequency (RF) coils are then used to generate RF energy pulses at or near the resonance frequency of the hydrogen nuclei, which add energy to the nuclear spin system. As the nuclear spins relax back to their quiescent state, they release the absorbed energy in the form of RF signals. The signal is detected by the MRI system and transformed into an image using a reconstruction algorithm.

Disclosure of Invention

In one embodiment, a method for performing a tilt scan of Magnetic Resonance (MR) includes: generating initial gradient waveforms in logical axes, the logical axes including a frequency encoding axis, a phase encoding axis, and a slice selection axis, wherein the maximum amplitudes of the initial gradient waveforms in the logical axes are equal; evaluating an area requirement of each of the initial gradient waveforms; increasing the maximum amplitude of the initial gradient waveform in the first logical axis; reducing the maximum amplitude of the initial gradient waveform in a second logical axis, wherein the area requirement in the first logical axis is greater than the area requirement in the second logical axis; converting the gradient waveforms into physical gradient waveforms; and driving a physical amplifier of the imaging system with the physical gradient waveform during the scan. In this way, the tilt scan can be performed without performance degradation due to increased echo time, repetition time, and echo spacing.

It should be appreciated that the brief description above is provided to introduce in simplified form a selection of concepts that are further described in the detailed description. It is not meant to identify key or essential features of the claimed subject matter, the scope of which is defined uniquely by the claims that follow the detailed description. Furthermore, the claimed subject matter is not limited to implementations that solve any disadvantages noted above or in any part of this disclosure.

Drawings

The invention will be better understood from a reading of the following description of non-limiting embodiments with reference to the attached drawings, in which:

FIG. 1 is a block diagram of an MRI system according to an exemplary embodiment;

FIG. 2 shows a set of graphs illustrating exemplary waveforms for an axial imaging plane;

FIG. 3 shows a set of graphs illustrating exemplary waveforms of tilted imaging planes;

FIG. 4 shows a set of graphs illustrating changes in amplitude from an orthogonal imaging plane to an oblique imaging plane, according to an example embodiment;

FIG. 5 shows a set of graphs illustrating optimized pulse amplitudes in tilted imaging planes, according to an example embodiment;

FIG. 6 shows a graph showing waveform components of a gradient waveform along a physical axis in a logical axis, where the physical gradient is utilized at the maximum specification of a tilt scan;

FIG. 7 illustrates a graph showing an exemplary optimization of waveform components of a gradient waveform along a physical axis, where physical gradients are not utilized at maximum specification of a tilt scan, according to one embodiment;

FIG. 8 illustrates a graph showing an exemplary optimization of waveform components of a gradient waveform using unused capacity of the physical gradient as shown in FIG. 7;

FIG. 9 shows a graph illustrating an example of waveform components of a gradient waveform along a physical axis optimized as shown in FIG. 8;

FIG. 10 shows a set of graphs showing an unoptimized gradient waveform;

FIG. 11 shows a set of graphs illustrating the gradient waveforms of FIG. 10 after one optimization iteration, in accordance with an example embodiment;

FIG. 12 shows a set of graphs illustrating the gradient waveforms of FIG. 10 after twenty-sub-optimization iterations, in accordance with an example embodiment;

FIG. 13 shows a set of graphs illustrating the gradient waveforms of FIG. 10 after fifty sub-optimization iterations, in accordance with an example embodiment;

FIG. 14 shows a set of graphs showing an unoptimized gradient waveform;

FIG. 15 shows a set of graphs illustrating the gradient waveforms of FIG. 14 after optimization, in accordance with an exemplary embodiment;

FIG. 16 shows a set of graphs showing an unoptimized gradient waveform;

FIG. 17 shows a set of graphs illustrating the gradient waveforms of FIG. 16 after one optimization iteration, in accordance with an example embodiment;

FIG. 18 shows a set of graphs illustrating the gradient waveforms of FIG. 16 after ten sub-optimization iterations, in accordance with an example embodiment;

FIG. 19 shows a set of graphs illustrating the gradient waveforms of FIG. 16 after twenty-five sub-optimization iterations, in accordance with an example embodiment;

FIG. 20 depicts a high level flow chart that illustrates an exemplary method for performing a tilt scan with an optimized waveform in accordance with one embodiment;

FIG. 21 depicts a high level flow chart that illustrates an exemplary method for optimizing a waveform, according to one embodiment; and is

FIG. 22 illustrates a graph showing echo interval variation of an optimized waveform, according to an exemplary embodiment.

Detailed Description

The following description relates to various systems and methods for optimizing gradient waveforms in an MRI system. In particular, a method for optimizing gradient waveforms in an MRI system (such as the MRI system depicted in fig. 1) is provided. As depicted in fig. 2 and 3, for tilted imaging planes, scan parameters characterizing the gradient waveforms (such as echo spacing, echo time, and repetition time) may be increased compared to orthogonal imaging planes, which reduces the imaging performance of the tilted scan. As shown in fig. 4, for oblique views, the amplitude of the different gradient waveforms is reduced because a single gradient amplifier generates components of multiple gradients. As shown in fig. 5, the amplitude and pulse width of the gradient waveforms may be optimized for oblique views. As depicted in fig. 6-9, the amplitude of the gradient waveforms may be optimized according to the angle between the logical axis of the gradient waveforms and the physical axis of the gradient amplifier or coil. Exemplary iterative optimization of gradient waveforms is depicted in fig. 10-19. An exemplary method of oblique imaging (such as the method depicted in fig. 20) includes: optimizing the waveforms in the logical axes according to area requirements, and converting the optimized waveforms into physical gradient waveforms to drive the gradient amplifiers. A method for optimizing a waveform, such as the method depicted in fig. 21, includes adjusting the amplitude and slew rate of the waveform. Optimization of gradient waveforms followed by optimization of scan parameters according to the methods described herein (as depicted in fig. 22) allows for tilt imaging to be performed without a performance penalty.

Fig. 1 shows a Magnetic Resonance Imaging (MRI) apparatus 10 including a static magnetic field magnet unit 12, a gradient coil unit 13, an RF coil unit 14, an RF body coil unit 15, a transmission/reception (T/R) switch 20, an RF driver unit 22, a gradient coil driver unit 23, a data acquisition unit 24, a controller unit 25, a patient bed 26, a data processing unit 31, an operation console unit 32, and a display unit 33. The MRI apparatus 10 transmits an electromagnetic pulse signal to a subject 16 placed in an imaging space 18 formed with a static magnetic field to perform scanning that obtains a Magnetic Resonance (MR) signal from the subject 16, thereby reconstructing an image of a slice of the subject 16 based on the MR signal thus obtained by the scanning.

The static field magnet unit 12 typically includes, for example, an annular superconducting magnet mounted within an annular vacuum vessel. The magnet defines a cylindrical space around the subject 16 and generates a constant main static magnetic field B₀。

The MRI apparatus 10 further comprises a gradient coil unit 13 which generates gradient magnetic fields in the imaging space 18 in order to provide three-dimensional position information for the MR signals received by the RF coil unit 14. The gradient coil unit 13 includes three gradient coil systems, each of which generates a gradient magnetic field (which is included in one of three spatial axes perpendicular to each other) in each of the frequency encoding direction, the phase encoding direction, and the slice selection direction according to imaging conditions. More specifically, the gradient coil unit 13 applies a gradient field in a slice selection direction of the subject 16 to select a slice; and the RF coil unit 14 transmits RF pulses to and excites a selected slice of the subject 16. The gradient coil unit 13 also applies a gradient field in the phase encoding direction of the subject 16 to phase encode the MR signals from the slices excited by the RF pulses. Then, the gradient coil unit 13 applies a gradient field in the frequency encoding direction of the subject 16 to frequency encode the MR signals from the slice excited by the RF pulse.

The RF coil unit 14 is provided, for example, to surround a region to be imaged of the subject 16. A static magnetic field B is formed by the static magnetic field magnet unit 12₀The RF coil unit 14 transmits RF pulses as electromagnetic waves to the subject 16 based on control signals from the controller unit 25 in the static magnetic field space or imaging space 18, and thus generates a high-frequency magnetic field B₁. This excites proton spins in the slice of the subject 16 to be imaged. The RF coil unit 14 receives, as an MR signal, an electromagnetic wave generated when the proton spins thus excited return to being aligned with the initial magnetization vector in the slice to be imaged of the subject 16. RF coil sheetThe element 14 may use the same RF coil to transmit and receive RF pulses.

The RF body coil unit 15 is provided, for example, so as to surround the imaging space 18 and generates a main magnetic field B generated by the static magnetic field magnet unit 12 in the imaging space 18₀Orthogonal RF magnetic field pulse B₁To excite the nuclei. In contrast to the RF coil unit 14, which can be easily disconnected from the MR device 10 and replaced with another RF coil unit, the RF body coil unit 15 is fixedly attached and connected to the MRI device 10. Furthermore, although local coils such as those including the RF coil unit 14 can transmit signals to or receive signals only from a local region of the subject 16, the RF body coil unit 15 generally has a large coverage area and is usable to transmit signals to or receive signals from the entire body of the subject 16. Using receive-only local coils, and emitter coils provides uniform RF excitation and good image uniformity at the expense of high RF power deposited in the subject 16. For transmit-receive local coils, the local coil provides RF excitation to a region of interest and receives MR signals, thereby reducing the RF power deposited in the subject 16. It will be appreciated that the particular use of the RF coil unit 14 and/or the RF body coil unit 15 depends on the imaging application.

The T/R switch 20 may selectively electrically connect the RF body coil unit 15 to the data acquisition unit 24 when operating in the receive mode, and may selectively electrically connect the RF body coil unit to the RF driver unit 22 when operating in the transmit mode. Similarly, the T/R switch 20 may selectively electrically connect the RF coil unit 14 to the data acquisition unit 24 when the RF coil unit 14 is operating in the receive mode, and may selectively electrically connect the RF coil unit to the RF driver unit 22 when operating in the transmit mode. When both the RF coil unit 14 and the RF body coil unit 15 are used for a single scan, for example, if the RF coil unit 14 is configured to receive MR signals and the RF body coil unit 15 is configured to transmit RF signals, the T/R switch 20 may direct control signals from the RF driver unit 22 to the RF body coil unit 15 while directing the received MR signals from the RF coil unit 14 to the data acquisition unit 24. The coils of the RF body coil unit 15 may be configured to operate in a transmit-only mode, a receive-only mode, or a transmit-receive mode. The coils of the local RF coil unit 14 may be configured to operate in a transmit-receive mode or a receive-only mode.

The RF driver unit 22 includes a gate modulator (not shown), an RF power amplifier (not shown), and an RF oscillator (not shown) for driving the RF coil unit 14 and forming a high-frequency magnetic field in the imaging space 18. The RF driver unit 22 modulates an RF signal received from the RF oscillator into a signal having a predetermined timing of a predetermined envelope using a gate modulator based on a control signal from the controller unit 25. The RF signal modulated by the gate modulator is amplified by an RF power amplifier and then output to the RF coil unit 14 or the RF body coil unit 15.

The gradient coil driver unit 23 drives the gradient coil unit 13 based on a control signal from the controller unit 25, and thus generates a gradient magnetic field in the imaging space 18. The gradient coil driver unit 23 comprises three systems of driver circuits or gradient amplifiers 53 corresponding to the three gradient coil systems comprised in the gradient coil unit 13. As depicted, the gradient amplifier 53 includes a G of gradient in the z-direction_zAmplifier 54, G of the gradient in the y-direction_yAmplifier 55 and gradient G in the x-direction_xAnd an amplifier 56.

The data acquisition unit 24 includes a preamplifier (not shown), a phase detector (not shown), and an analog/digital converter (not shown) for acquiring the MR signals received by the RF coil unit 14. In the data acquisition unit 24, the phase detector performs phase detection on the MR signal received from the RF coil unit 14 and amplified by the preamplifier using the output from the RF oscillator of the RF driver unit 22 as a reference signal, and outputs the phase-detected analog MR signal to an analog/digital converter to be converted into a digital signal. The digital signal thus obtained is output to the data processing unit 31.

The MRI apparatus 10 includes a table 26 for placing the subject 16 thereon. The subject 16 can be moved inside and outside the imaging space 18 by moving the table 26 based on a control signal from the controller unit 25.

The controller unit 25 includes a computer and a recording medium on which a recording medium of a program to be executed by the computer is recorded. The program, when executed by a computer, causes various portions of the apparatus to perform operations corresponding to a predetermined scan. The recording medium may include, for example, a ROM, a floppy disk, a hard disk, an optical disk, a magneto-optical disk, a CD-ROM, or a nonvolatile memory card. The controller unit 25 is connected to the operation console unit 32 and processes operation signals input to the operation console unit 32, and also controls the table 26, the RF driver unit 22, the gradient coil driver unit 23, and the data acquisition unit 24 by outputting control signals to the table, the gradient coil driver unit, and the data acquisition unit. The controller unit 25 also controls the data processing unit 31 and the display unit 33 based on an operation signal received from the operation console unit 32 to obtain a desired image.

The operator console unit 32 includes user input devices such as, by way of non-limiting example, a keyboard and a mouse. The operator uses the operation console unit 32, for example, to input such data as an imaging protocol and set an area where an imaging sequence is to be performed. Data on the imaging protocol and the imaging sequence execution region is output to the controller unit 25.

The data processing unit 31 includes a computer and a recording medium on which a program to be executed by the computer to perform predetermined data processing is recorded. The data processing unit 31 is connected to the controller unit 25, and performs data processing based on a control signal received from the controller unit 25. The data processing unit 31 is also connected to the data acquisition unit 24, and generates spectral data by applying various imaging processing operations to the MR signals output from the data acquisition unit 24.

The display unit 33 includes a display device, and displays an image on a display screen of the display device based on a control signal received from the controller unit 25. The display unit 33 displays, for example, an image on an input item concerning an operator inputting operation data from the operation console unit 32. The display unit 33 also displays slice images of the subject 16 generated by the data processing unit 31.

These gradient fields can be considered to be oriented both in the physical plane and by the logical axis. In a physical sense, these fields are oriented orthogonal to each other to form a coordinate system that can be rotated by appropriate manipulation of the pulsed currents applied to the individual field coils. In a logical sense, the coordinate system defines gradients commonly referred to as slice selection gradients, frequency encoding gradients, and phase encoding gradients.

The slice selection gradient determines the slice of the tissue or anatomical structure to be imaged within the patient. The slice selection gradient field can thus be applied simultaneously with the selective RF pulses to excite known spin volumes within the desired slice that precess at the same frequency. The slice thickness is determined by the bandwidth of the RF pulse and the gradient strength throughout the field of view.

A second logical gradient axis (i.e., the frequency encoding gradient axis, also referred to as the readout gradient axis) is applied in a direction perpendicular to the slice selection gradient. Generally, frequency encoding gradients are applied before and during the formation of MR echo signals caused by RF excitation. The spins of the gyromagnetic material under the influence of this gradient are frequency encoded according to the spatial position of these spins in the overall gradient field. By means of fourier transformation, the acquired signals can be analyzed to identify their position in the selected slice by means of frequency encoding.

Finally, the phase encoding gradients are typically applied in sequence before the readout gradients and after the slice selection gradients. Localization of spins in a gyromagnetic material in a phase encode direction is achieved by: the phase change of the precessing protons of the material is sequentially induced by using slightly different gradient amplitudes applied sequentially during the data acquisition sequence. The phase change is thus applied linearly throughout the field of view and the spatial position within the slice is encoded by the polarity and the degree of phase difference accumulated relative to the null. The phase encoding gradient allows a phase difference to be generated between these spins of the material depending on the position of the spins in the phase encoding direction.

The physical gradient generated by the gradient coil unit 13 driven by the amplifier 53 may be relative to the imaging systemThe configuration is such that the physical gradient is aligned with the logical axis when imaging in the axial, sagittal, and coronal reference planes. For example, for axial, coronal, or sagittal imaging, G_ZAmplifier 54 may be used to generate a slice selection gradient, G_YAmplifier 55 can be used to generate the phase encoding gradient, and G_XThe amplifier 56 may be used to generate a frequency encoding gradient. In this way, the shortest scan parameters (e.g., echo Time (TE), repetition Time (TR), and echo interval (ESP)) for the axial prescription, sagittal prescription, and coronal prescription are achieved.

However, when the tilt scan is specified, these scan parameters become longer, which results in a decrease in the application performance of the tilt scan. As an illustrative example, fig. 2 shows a set of graphs 200 showing exemplary waveforms for an axial imaging plane, including a graph 202 of waveform amplitude and a graph 203 of waveform slew rate over time. In particular, graph 202 depicts G_XWaveform amplitudes 210, G_ZWaveform amplitudes 220 and G_YWaveform amplitude 230, and plot 203 depicts the corresponding G_X Waveform slew rates 215, G_ZWaveform slew rates 225 and G_Y Waveform slew rate 235.

In contrast, fig. 3 shows a set of graphs 300 illustrating exemplary waveforms for tilted imaging planes, including a graph 302 of waveform amplitude and a graph 303 of waveform slew rate over time. Graph 302 of waveform amplitude depicts G_XWaveform amplitudes 310, G_ZWaveform amplitudes 320 and G_YWaveform amplitude 330, and plot 303 depicts the corresponding G_XWaveform slew rates 315, G_Z Waveform slew rates 325 and G_Y Waveform slew rate 335.

As depicted in FIGS. 2 and 3, with G_XMaximum value of waveform amplitude 210, G_XThe maximum value of the waveform amplitude 310 decreases. Furthermore, G_XThe pulse duration of the waveform amplitude 310 is substantially longer than G of the axial imaging plane_XThe pulse duration of the waveform amplitude 210. Due to relatively long scan parameters (such as TE, TR and ESP) and relative subtractionThe tilt scan amplitude is small and therefore the performance of the tilt scan application is generally reduced compared to an orthogonal imaging plane.

Fig. 4 shows a set of graphs 400 illustrating exemplary pulse amplitudes in two logical axes of an orthogonal imaging plane and a tilted imaging plane. The set of graphs 400 includes a plot 401 of the maximum of the amplitudes of the quadrature and tilt pulses in the logical axes X and Y, a plot 402 of the amplitudes of the axial and tilt pulses 410 and 420 in the logical axis X, and a plot 403 of the amplitudes of the axial and tilt pulses 430 and 440 in the logical axis Y that is orthogonal to the logical axis X.

For orthogonal imaging planes (such as axial, sagittal, or coronal imaging planes), by G_XAmplifier (e.g., G)_XAmplifier 56) driven G_XAxial pulse 410 generated by the coil and G_YAmplifier (e.g., G)_YAmplifier 55) driven G_YThe axial pulses 430 generated by the coils may be assigned the largest possible amplitude because the logical axis X and the logical axis Y are aligned with the physical axis X and the physical axis Y of the gradient coils. In particular, pulse 410 may reach G_XThe maximum amplitude 412 achievable by the amplifier, and the pulse 430 up to G_YThe maximum amplitude 432 achievable by the amplifier. Both amplitudes 412 and 432 may be achieved even though the first axial pulse 410 and the second axial pulse 430 are time aligned.

In the tilted plane, the logical axes X and Y are rotated α with respect to the logical axes of the axial plane, as shown in diagram 401_XThe coils may contribute to a portion of the waveform in the logic axis X and a portion of the waveform in the logic axis Y (described in detail below in connection with fig. 6). To ensure that the combination of waveforms in logical axes X and Y does not exceed G_XAmplifier and G_YThe maximum amplitude achievable by the amplifier is reduced by the maximum value of the waveform amplitude of the ramp pulses in the logic axes X and Y. Specifically, as shown in the diagram 401, a square formed by the maximum values 422 and 442 of the waveform amplitudes in the logical axes X and Y of the inclined plane is limited within a square formed by the maximum values 412 and 432 of the waveform amplitudes in the physical axis. Therefore, the ramp pulse 420 may achieve a maximum amplitude 422 in the logical axis X that is less than the maximum amplitude 412 in the physical axis X, and the tilt pulse 440 may achieve a maximum amplitude 442 in the logical axis Y that is less than the maximum amplitude 432 in the physical axis Y. The duration (i.e., width) of the pulses of the oblique scan is longer than the duration of the pulses of the orthogonal scan if the area enclosed by the pulses remains the same. In particular, the duration of pulse 420 is longer than the duration of pulse 410, and the duration of pulse 440 is longer than the duration of pulse 430, as shown in graphs 402 and 403.

Although two logical axes X and Y are depicted in FIG. 4 for simplicity, it should be understood that three logical axes X, Y and Z may in fact be used. For example, if three logical axes are used, the square shown in diagram 401 may be changed to a cube.

Thus, as shown in fig. 2-4, when a tilt scan is prescribed, the maximum logical amplitude is reduced and the scan parameters (e.g., echo Time (TE), repetition Time (TR), and echo interval (ESP)) are increased. For some applications, pulses in different logical axes start at the same time and have the same area requirement. For example, in one application, two "breakers" on different logical axes with the same area requirements at the same time are used to terminate the signal at the end of each TR cycle. For other applications, the area requirements of the overlapping pulses and/or the start times of the overlapping pulses may be different for different logical axes. The area requirements of each gradient waveform may depend on the prescription. For example, if the resolution in one direction changes, the area requirements of the corresponding waveform will change accordingly. Thus, even for the same Pulse Sequence Diagram (PSD), one recipe may require pulses in different logical axes to start at the same time and have the same area requirement, while for another recipe (e.g., having lower resolution along one direction), the area requirements of overlapping pulses may be different.

Pulse optimization may be performed for those applications where the area requirements of the overlapping pulses and/or the starting times of the overlapping pulses are different. As an illustrative example, fig. 5 shows a set of graphs 500 illustrating optimization of pulse amplitude in a tilted imaging plane, in accordance with one embodiment. The set of graphs 500 includes a graph 502 of the amplitudes of a first un-optimized tilt pulse 510 and a first optimized tilt pulse 520 in the logic axis X, and a graph 503 of the amplitudes of a second un-optimized tilt pulse 530 and a second optimized tilt pulse 540 in the logic axis Y.

In the logical axis X, the first non-optimized tilt pulse 510 has an amplitude 512 and a pulse width (i.e., duration) 514, where the amplitude 512 is less than the maximum achievable amplitude 522 in the physical axis X. Meanwhile, in the logic axis Y, the second un-optimized ramped pulse 530 has an amplitude 532 and a pulse width 534. As depicted, there is a high area requirement on the logic axis X and a low area requirement on the logic axis Y.

To optimize the first non-optimized tilt pulse 510 and the second non-optimized tilt pulse 530, the slew rate and amplitude may be increased in the logic axis X, while the amplitude and slew rate may be decreased or de-rated in the logic axis Y. Thus, the amplitude 522 of the first optimized ramped pulse 520 is equal to the maximum amplitude achievable in the physical axis X, where the pulse width 524 is reduced relative to the pulse width 514 due to the increased slew rate. The amplitude 542 of the second optimized ramped pulse 540 is lower than the amplitude 532 and in particular lower than the maximum amplitude 550 achievable in the physical axis Y, while the pulse width 544 increases relative to the pulse width 534 due to the de-rating.

Thus, optimizing pulses 510 and 530 to generate optimized pulses 520 and 540 in this example includes derating in logic axis Y so that the slew rate may be increased in logic axis X, and calculating the maximum amplitude achievable in logic axis X based on the amplitude of the derating in logic axis Y.

Fig. 6 illustrates a graph 600 showing waveform components of a gradient waveform along a physical axis in a logical axis. In particular, the graph 600 depicts a first logical axis 605 (e.g., logical axis Y) and a second logical axis 610 (e.g., logical axis X) rotated by an angle 612 relative to a physical axis 615 (e.g., physical axis X).

The gradient amplifier associated with the physical axis 615 has an output capacity depicted as a maximum amplitude 617 along the physical axis 615.

Graph 600 depicts a first waveform having an amplitude 620 along a first logical axis 605 and a second waveform having an amplitude 630 along a second logical axis 610. The gradient generated along the physical axis 615 contributes to a portion of the waveform in the first logical axis 605 and a portion of the waveform in the second logical axis 610 when the logical axis 610 is rotated an angle 612 relative to the physical axis 615. The amplitudes 620 and 630 are initially assigned to the respective waveforms such that the component 622 of the first waveform and the component 632 of the second waveform are equal and take full advantage of the capacity of the gradient amplifier, as indicated by the maximum amplitude 617. For example, the amplitudes 620 and 630 may be initially determined from the diagram 401 of FIG. 4.

Since high area requirements are delineated by amplitudes 620 and 630 in both logical axes 605 and 610, respectively, the physical gradient is utilized at its maximum specification for the tilt scan.

Fig. 7 shows a graph 700 that shows that if there is a low area requirement in one of the logical axes, the gradient generated along the physical axis 615 is not utilized at its maximum specification for the tilt scan. For example, if the demand of the second waveform corresponds to amplitude 730 instead of amplitude 630, then the component 732 of amplitude 630 is likewise smaller. Since the total demand 705 on the physical axis 615 is less than the maximum amplitude 617, there is unused capacity 750 along the physical axis 615.

Since the demand along the first logical axis 605 (as depicted by the amplitude 620) is greater than the demand along the second logical axis 610 (as depicted by the amplitude 730), the amplitude of the first waveform can be increased to take advantage of the unused capacity 750 of the physical axis 615. For example, as depicted by the graph 800 in fig. 8, the amplitude of the first waveform in the first logical axis 605 is increased from the amplitude 620 to an optimized amplitude 820 in order to maximize the utilization of the amplifier in the physical axis 615. The waveform component 822 of the first waveform along the physical axis 615 is therefore increased to utilize the unused capacity 750, such that the total demand on the physical axis 615 is equal to the maximum amplitude 617.

Thus, as depicted by the graph 900 in fig. 9, the amplitude 820 of the first waveform is increased to account for the lower amplitude 730 of the second waveform, and the components 822 and 732 of the first and second waveforms, respectively, along the physical axis 615 add up to the maximum amplitude 617 of the physical axis 615. Although fig. 6-9 depict two physical axes and two logical axes for simplicity of discussion, it should be understood that optimization of waveform amplitudes for three physical axes (i.e., physical axis X, physical axis Y, and physical axis Z) and three logical axes (i.e., logical axis X, logical axis Y, and logical axis Z) may be similarly performed.

The relationship between the logical gradient waveforms and the physical gradient waveforms may be expressed as:

wherein G is_phyX、G_phyYAnd G_phyZIs a gradient waveform in the physical axis, G_logicX、G_logicYAnd G_logicZIs the gradient waveform in the logical axis, and R is a 3 × 3 rotation matrix. As is well known in the art, the elements of the rotational matrix are determined by slice orientation.

After evaluating the gradient area requirements in each logical axis, a first logical axis X requirement G may be determined_logicDemXSecond logical axis Y request G_logicDemYAnd third logical axis Z requirement G_logicDemZ. When designing the PSD, the area requirements for each gradient waveform and the position at which each waveform is placed in the broadcast can be known. The amplitude requirement from each physical axis can be calculated using a rotation matrix:

wherein G is_phyDemX、G_phyDemYAnd G_phyDemZThe amplitude requirements from the physical X, Y and Z-axis, respectively. Using these amplitude requirements from each physical axis, the three scale factors scaleX, scaleY, and scaleZ can be calculated by dividing the amplitude requirements from each physical axis by the maximum amplitude that can be provided by each physical axis. The final scale factor scaleXYZ is obtained by taking the maximum value among all scale factors:

this common scale factor scaleux ensures that the gradient amplitude on each physical axis does not exceed the gradient amplifier capability after optimization. Finally, the optimized gradient amplitude on the logical axis can be calculated using the following formula:

wherein G is_logicOptX、G_logicOptYAnd G_logicOptZOptimized gradient waveform amplitudes in the logic X, Y and Z-axis, respectively.

Fig. 10 shows a set of graphs 1000 illustrating unoptimized gradient waveforms including a graph 1002 of the amplitude of three gradient waveforms 1010, 1020, and 1030 as a function of time, and a graph 1003 of slew rates 1012, 1022, and 1032 corresponding to the gradient waveforms of the graph 1002, respectively.

Fig. 11-13 illustrate a set of graphs illustrating an iterative optimization of the gradient waveform of fig. 10, according to an example embodiment. The above formula illustrates the analysis method. On the other hand, an iterative approach may be used, where the change from a non-optimized waveform to an optimized waveform can be gradually seen. In particular, fig. 11 shows a set of graphs 1100 including a graph 1102 and a graph 1103 showing the amplitude and slew rate, respectively, after one optimization iteration. As depicted, the slew rate 1122 is reduced relative to the slew rate 1022, and further the amplitude of the pulses in waveform 1120 is reduced relative to waveform 1020. The start time of the pulse in waveform 1120 is also adjusted relative to the start time of the pulse in waveform 1020 to adjust the overlap area requirements of waveforms 1010 and 1020. The amplitude of waveform 1110 increases relative to the amplitude of waveform 1010 due to de-rating of waveform 1020. In addition, the pulse width of the pulses of waveform 1110 decreases as the amplitude increases so that the area requirements remain unchanged.

Fig. 12 shows a set of graphs 1200 including graphs 1202 and 1203 showing amplitudes 1210, 1220, and 1230, and slew rates 1212, 1222, and 1232, respectively, after twenty sub-optimization iterations. As depicted, the slew rate 1222 and start time of the pulses of the second waveform 1220 are adjusted relative to the waveform 1120. Further, the amplitude of waveform 1210 increased above 2.5G/cm as the pulse width of the pulses in waveform 1220 increased.

Fig. 13 shows a set of graphs 1300 including graphs 1302 and 1303 showing amplitude and slew rate after fifty sub-optimization iterations, respectively. As depicted, the amplitude of the first waveform 1310 reaches 3.0G/cm, which is a substantial amplitude increase compared to the 2.4G/cm unoptimized amplitude depicted in FIG. 10. The amplitude of the second waveform 1320 is substantially reduced relative to the second waveform 1020 depicted in fig. 10, and the timing and slew rate 1322 have been substantially adjusted such that the area requirement of the waveform 1320 is equivalent to the area requirement of the waveform 1020.

Because waveform 1030 indicates no demand, optimized waveforms 1130, 1230, and 1330 and corresponding slew rates 1132, 1232, and 1332 may not change relative to initial waveform 1030 and corresponding slew rate 1032.

After the gradient waveforms in the logical axes are optimized as needed, these waveforms are combined and converted to physical gradient waveforms to drive the individual gradient amplifiers. The physical gradient waveforms thus contribute to optimized gradient waveforms from different logical axes. As an illustrative example, fig. 14 shows a set of graphs 1400 showing non-optimized physical gradient waveforms, while fig. 15 shows a set of graphs 1500 showing the physical gradient waveforms of fig. 14 after optimization. After optimization, the maximum amplitude and maximum slew rate of the physical gradient are not violated.

In the optimized example depicted in fig. 10-13, the amplitude of the first waveform 1010 is optimally increased by de-rating the second waveform 1020 alone, since the third waveform 1030 indicates no demand. It should be understood that in many cases, all three gradient waveforms may be optimized or adjusted. As an example, fig. 16 shows a set of graphs 1600 that illustrate the amplitude and slew rate of an unoptimized gradient waveform. The set of graphs 1600 particularly depicts pulses in each of the first, second, and third waveforms 1610, 1620, 1630 and corresponding slew rates 1612, 1622, and 1632. In this example, the area under waveform 1620 (i.e., the area requirement) is greater than the area under waveforms 1610 and 1630, and thus waveform 1620 has the highest area requirement.

During optimization, the amplitude of waveform 1620 and corresponding slew rate 1622 may be increased to maximize the amplitude, while waveforms 1610 and 1630 may be de-rated to accommodate the maximization of waveform 1620. Fig. 17 shows a set of graphs 1700 illustrating the gradient waveforms of fig. 16 after one optimization iteration, and fig. 18 shows a set of graphs 1800 illustrating the gradient waveforms of fig. 16 after ten optimization iterations. As depicted, the amplitude of waveform 1620 is iteratively increased while waveforms 1610 and 1630 are de-rated. Fig. 19 shows a set of graphs 1900 showing the gradient waveforms of fig. 16 after twenty-five sub-optimization iterations. The amplitude of optimized second waveform 1920 is 3.0G/cm, which is substantially greater than the 2.3G/cm amplitude of un-optimized second waveform 1620. The optimized slew rate 1922 of the optimized second waveform 1920 is also substantially increased relative to the slew rate 1622. Further, the amplitudes of the first optimized waveform 1910 and the third optimized waveform 1930 are substantially close to the amplitudes of the unoptimized waveforms 1610 and 1630. However, the timing of the pulses of the first optimized waveform 1910 and the third optimized waveform 1930 are adjusted relative to the non-optimized waveforms 1610 and 1630, and the slew rates 1912 and 1932 are substantially reduced relative to the slew rates 1612 and 1632. In this way, the area requirements of the three waveforms are maintained while optimizing the amplitude of the waveforms with the highest area requirement.

Fig. 20 illustrates a high level flow chart that illustrates an exemplary method 2000 of performing a tilt scan with an optimized waveform, in accordance with one embodiment. The method 2000 is described with reference to the systems and components of fig. 1, but it should be understood that the method 2000 may be implemented with other systems and components without departing from the scope of the present disclosure. For example, the method 2000 may be implemented as executable instructions in a non-transitory memory of the MRI apparatus 10.

Method 2000 begins at 2005. At 2005, a scan prescription is received. The scan recipe may include a user selection of one or more scan parameters (including, but not limited to, scan plane, resolution, pulse sequence, etc.).

At 2010, it is determined whether the scan prescription specifies a tilt scan. If the scan prescription does not include a tilt scan ("NO"), method 2000 proceeds to 2015, where the scan is performed according to the scan prescription. Gradient waveforms are generated according to a scan prescription having selected scan parameters, and gradient amplifiers are driven with the gradient waveforms to produce gradient fields via the gradient coils, as described above with reference to fig. 1. The method 2000 then returns.

However, if the scan prescription includes a tilt scan ("yes" at 2010), method 2000 proceeds to 2020. At 2020, the area requirements for each logical axis are evaluated. For example, the area requirements may be evaluated based on pulse sequence, resolution, and the like. As discussed above, the area requirements of one logical axis may vary for different resolutions in that logical axis.

At 2025, the waveform in the logic axis is optimized according to the requirements. As discussed above, the amplitude and slew rate of the waveform with the highest area requirement may be increased while the amplitude, timing, and/or slew rate of one or more other waveforms are decreased such that the area requirement of each waveform is achieved. Furthermore, the physical constraints of the gradient amplifier are observed by limiting the components of the logical gradient waveform on the physical axis to maximum amplitude and slew rate. The optimized waveform may be determined by an analytical method (e.g., as shown in the above equation) or an iterative method.

At 2030, the optimized waveforms are converted to physical gradient waveforms for the gradient amplifiers by using, for example, a rotation matrix. That is, the optimized waveforms in the logical axis are transformed and combined into physical gradient waveforms along the physical axis, which will drive the corresponding gradient amplifiers. Although the amplitude and slew rate of the waveform are adjusted during optimization, the physical gradient waveform does not violate the maximum amplitude and slew rate of the gradient amplifier. Continuing at 2035, a scan is performed according to the scan prescription using the physical gradient waveforms. That is, during a scan, the gradient amplifiers drive the gradient coils with physical gradient waveforms. The method 2000 then returns.

Accordingly, a method for magnetic resonance imaging comprises: optimizing gradient waveforms in logical axes that are rotated relative to physical axes of a gradient coil of an imaging system; and controlling the gradient amplifier with the optimized gradient waveforms during scanning of the subject with the imaging system.

Fig. 21 illustrates a high-level flow diagram showing an exemplary method 2100 for optimizing a waveform, according to one embodiment. The method 2100 is described with reference to the systems and components of fig. 1, but it should be understood that the method 2100 may be implemented with other systems and components without departing from the scope of the present disclosure. For example, the method 2100 may be implemented as executable instructions in a non-transitory memory of the MRI apparatus 10.

Method 2100 begins at 2105. At 2105, gradient waveforms in logical axes are initialized, one for each logical axis. In some embodiments where the prescribed scan planes are orthogonal, the maximum amplitude in each logical axis may be set to be the same as the maximum amplitude in the physical axis because the logical axis is aligned with the physical axis. In some implementations of prescribed scan plane tilt, the gradient waves in the logical axis may be initialized based on the angle of the tilted plane relative to the orthogonal plane. For example, a gradient wave may be initialized according to the diagram 401 of FIG. 4, where the square formed by the maxima 422 and 442 of the waveform amplitude in the logical axes X and Y of the tilted plane is confined to the square formed by the maxima 412 and 432 of the waveform amplitude in the physical axis. In this way, the maximum amplitudes assigned to the respective waveforms are equal and the capacity of the gradient amplifier is fully utilized (e.g., as shown in FIG. 6). If three logical axes are used, the square shown in diagram 401 may be changed to a cube to initialize the gradient waveform.

At 2110, it is determined whether the prescribed scan plane is tilted. If not a tilt scan ("NO"), the method 2100 continues to 2115 where the initial gradient waveform obtained at 2105 is maintained (i.e., where the maximum amplitude is the same as the maximum amplitude in the physical axis). Method 2100 then returns.

However, if the prescribed scan plane is tilted ("yes"), then method 2100 proceeds to 2120. At 2120, the area requirements of each waveform are evaluated. The area requirements may be evaluated based on pulse sequence, resolution, etc.

At 2125, it is determined whether the area requirements of the waveforms in the different logical axes are different. As discussed above, for some applications, pulses in different logical axes start at the same time and have the same area requirements. For other applications, the area requirements of the overlapping pulses and/or the start times of the overlapping pulses may be different for different logical axes. The waveform optimization discussed herein may be applied to the latter scenario. If the area requirements are not different ("NO"), the method 2100 continues to 2130, where the initial waveform obtained at 2105 (i.e., equal maximum amplitude in the logical axis) is maintained. Method 2100 then returns.

However, if the area requirements are different ("yes"), then method 2100 continues to 2135. At 2135, the maximum amplitude of the waveform with the larger area requirement is increased and the maximum amplitude of the waveform with the smaller area requirement is decreased. Further, continuing at 2140, the slew rate, duration, and timing of the waveform are adjusted according to the area requirements and the adjusted maximum amplitude. The slew rate, duration and timing are adjusted so that the maximum slew rate that the gradient amplifier can achieve is not exceeded. Method 2100 then returns.

Fig. 22 illustrates a graph 2200 showing echo spacing variations of an optimized waveform, in accordance with one embodiment. In particular, graph 2200 includes graph 2205 showing echo intervals imaged in various orientations with an MRI device that does not include optimized waveforms, and graph 2210 showing echo intervals imaged in various orientations with an MRI device optimized waveforms according to the methods described herein.

The first orientation (orientation 1) comprises an axial orientation, the second orientation (orientation 2) comprises a single-angled tilt orientation, and the third orientation (orientation 3) comprises a double-angled tilt orientation. As depicted by graph 2205, the echo spacing in the second orientation (i.e., when specifying a single-angle tilt orientation) substantially increases and the echo spacing in the third orientation (i.e., when specifying a double-angle tilt orientation) further increases relative to the first orientation. In particular, a 6.7% increase in the echo spacing was observed between the first orientation and the third orientation.

The echo spacing similarly increases even when the waveform is optimized (as depicted by graph 2210), but the relative rate of increase is less pronounced between orientations. In particular, only a 1.2% change was observed between the first and third orientations of the MRI device with the optimized waveform. Therefore, by optimizing the waveform according to the area requirement, the tilt scan can be performed without a significant increase in scan parameters (such as echo time, repetition time, and echo interval).

Technical effects of the present disclosure include adjusting amplitude and pulse width of a gradient waveform according to an angle between a logical axis and a physical axis. Another technical effect of the present disclosure includes acquiring MR data in a tilted imaging plane with improved timing.

As used herein, an element or step recited in the singular and proceeded with the word "a" or "an" should be understood as not excluding plural said elements or steps, unless such exclusion is explicitly recited. Furthermore, references to "one embodiment" of the present invention are not intended to be interpreted as excluding the existence of additional embodiments that also incorporate the recited features. Furthermore, unless explicitly stated to the contrary, embodiments "comprising," "including," or "having" an element or a plurality of elements having a particular property may include additional such elements not having that property. The terms "comprising" and "under … … are used as the plain-language equivalents of the respective terms" comprising "and" wherein ". Furthermore, the terms "first," "second," and "third," etc. are used merely as labels, and are not intended to impose numerical requirements or a particular positional order on their objects.

This written description uses examples to disclose the invention, including the best mode, and also to enable any person skilled in the relevant art to practice the invention, including making and using any devices or systems and performing any incorporated methods. The patentable scope of the invention is defined by the claims, and may include other examples that occur to those of ordinary skill in the art. Such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims, or if they include equivalent structural elements with insubstantial differences from the literal languages of the claims.