Patent Application
20150000112
The invention relates to the field of magnetic resonance (MR) imaging. It concerns a method of manufacturing a personalized RF coil array for MR imaging guided interventions. Moreover, the invention relates to a computer program and to a computer workstation.
Image-forming MR methods which utilize the interaction between magnetic fields and nuclear spins in order to form two-dimensional or three-dimensional images are widely used nowadays, notably in the field of medical diagnostics, because for the imaging of soft tissue they are superior to other imaging methods in many respects, do not require ionizing radiation and are usually not invasive.
According to the MR method in general, the body of the patient to be examined is arranged in a strong, uniform magnetic field whose direction at the same time defines an axis (normally the z-axis) of the co-ordinate system on which the measurement is based. The magnetic field produces different energy levels for the individual nuclear spins in dependence on the magnetic field strength which can be excited (spin resonance) by application of an electromagnetic alternating field (RF field) of defined frequency (so-called Larmor frequency, or MR frequency). From a macroscopic point of view, the distribution of the individual nuclear spins produces an overall magnetization which can be deflected out of the state of equilibrium by application of an electromagnetic pulse of appropriate frequency (RF pulse) while the magnetic field of the RF pulse extends perpendicular to the z-axis, so that the magnetization performs a precession about the z-axis. This motion of the magnetization describes a surface of a cone whose angle of aperture is referred to as flip angle. The magnitude of the flip angle is dependent on the strength and the duration of the applied electromagnetic pulse. In the case of a so-called 90° pulse, the spins are deflected from the z axis to the transverse plane (flip angle 90°). The RF pulse is radiated toward the body of the patient via a RF coil arrangement of the MR device. The RF coil arrangement typically surrounds the examination volume in which the body of the patient is placed. After termination of the RF pulse, the magnetization relaxes back to the original state of equilibrium, in which the magnetization in the z direction is built up again with a first time constant T1 (spin lattice or longitudinal relaxation time), and the magnetization in the direction perpendicular to the z direction relaxes with a second time constant T2 (spin-spin or transverse relaxation time). The variation of the magnetization can be detected by means of receiving RF coils which are arranged and oriented within the examination volume of the MR device in such a manner that the variation of the magnetization is measured in the direction perpendicular to the z-axis. The decay of the transverse magnetization is accompanied, after application of, for example, a 90° pulse, by a transition of the nuclear spins (induced by local magnetic field inhomogeneities) from an ordered state with the same phase to a state in which all phase angles are uniformly distributed (dephasing). The dephasing can be compensated by means of a refocusing pulse (for example a 180° pulse). This produces an echo signal (spin echo) in the receiving coils.
In order to realize spatial resolution in the body, linear magnetic field gradients extending along the three main axes are superposed on the uniform magnetic field, leading to a linear spatial dependency of the spin resonance frequency. The signal picked up in the receiving coils then contains components of different frequencies which can be associated with different locations in the body. The signal data obtained via the receiving coils corresponds to the spatial frequency domain and is called k-space data. The k-space data usually includes multiple lines acquired with different phase encoding. Each line is digitized by collecting a number of samples. A set of k-space data is converted to a MR image by means of Fourier transformation or other suitable algorithms.
The lack of harmful effects on the examined patient and the operator make MR imaging well-suited for “interventional radiology”, wherein the acquired and reconstructed MR images are used to guide invasive procedures. The general goal of imaged guidance is to apply imaged-based information to the processes of diagnosis and therapy. Known MR imaging-guided therapy systems use pre-operatively acquired MR images to create anatomic models, which provide localization, targeting, and visualization of the 3D anatomy. These models support pre-operative planning to define and optimize access strategies and to simulate planned interventions. These models connect image coordinates with the actual position defined by an instrument's location in the surgical field. Thus, they enable a surgeon to navigate and execute procedures with full knowledge of the surrounding anatomy.
In a plurality of practical applications, shifts and deformations of soft tissues occur during surgery because of mechanical factors, physiological motion, swelling, or hemorrhage. These changes may displace organs or their tissue components to such a degree that pre-operatively acquired MR imaging-based 3D models cannot be registered with the patient's actual anatomy. In this situation the ultimate solution for accurate MR imaging-guided surgery is real-time intra-operative MR imaging or at least frequent updating of the volumetric MR images during interventional procedures. This results in methods that can continuously detect changes of the position of various tissue components and locate the targets of the interventions and their environments in order to define trajectories to the lesion to be treated. Hence, the justification of intra-operative MR imaging is the change in anatomy during surgeries or the change of tissue integrity during therapy. The goal is to allow MR imaging-guided therapy to make full use of the anatomic and functional information accessible by current MR imaging methods. By providing the physician with current MR image information, safety and efficiency of surgical or interventional procedures is significantly improved.
A problem is that it is difficult in a surgical setting to optimally place the RF coils required for MR signal acquisition around the respective body portion in such a fashion that (i) a good signal-to-noise ratio (SNR) is obtained and (ii) a good access to the interventional field is assured for the physician.
From the foregoing it is readily appreciated that there is a need for an improved RF coil arrangement for MR imaging guided interventions that enables high-quality intra-operative MR imaging as well as good access to the patient.
In accordance with the invention, a method of manufacturing a personalized RF coil array for MR imaging guided interventions is disclosed. The method comprises the steps of:
acquiring diagnostic image data reflecting the anatomy of a portion of a patient's body;
planning an intervention on the basis of the diagnostic image data, wherein an interventional field within the patient's body portion is determined;
arranging one or more RF antennae on a substrate, which is adapted to the patient's anatomy, in such a manner that the signal-to-noise ratio of MR signal acquisition via the one or more RF antennae from the interventional field is optimized.
The invention proposes a personalized design of a RF coil array for MR imaging-guided surgical procedures. The design of the RF coil array, i.e. the sizes, shapes, and/or positions of the RF antennae, is based on the anatomy of the portion of the patient's body to be treated and on the surgery plan. The diagnostic image data, which may comprise X-ray images, CT images, and/or MR images, is acquired pre-operatively in a first step. Anatomic models may be created on the basis of this diagnostic image data, which enable localization, targeting, and visualization of the 3D anatomy of the patient's body portion. In a second step, pre-operative planning is performed on the basis of the acquired diagnostic image data in order to define the interventional field and to optimize the access strategies. Finally, the design of the RF coil array is derived from the results of the surgery planning The sizes, shapes and/or positions of one or more RF antennae on the substrate is automatically computed, thereby optimizing the signal-to-noise ratio of the MR signals acquired intra-operatively from the interventional field.
The substrate, on which the one or more RF antennae are arranged, is adapted to the shape of the patient's body, so that the RF coil array can be placed firmly, in close proximity, and in a well-defined position on the patient's body during the surgical invention. Preferably, both the shape of the substrate and the position of the substrate on the patient's body are derived from the previously acquired diagnostic image data and from the planning results.
According to a preferred embodiment of the invention, an access path to the interventional field is further determined during the step of planning the intervention, wherein the one or more RF antennae are arranged on the substrate in such a manner that the signal-to-noise ratio of MR signal acquisition from the interventional field and from the access path is optimized. In this embodiment, the optimization criteria determining the design of the RF coil array are extended so as to ensure the acquisition of high-quality MR images not only from the interventional field itself, i.e. the target region of the intervention, but also from the access path, which the surgeon takes to reach the lesion to be treated. Acquisition of high-quality MR images throughout the complete intervention is thus achieved.
According to a further preferred embodiment of the invention, one or more apertures are provided on the substrate in such a manner that the access path is kept clear when the substrate is attached to the patient's body. The size, the shape, and the locations of apertures in the substrate, via which the surgeon accesses the patient's body portion, are derived from the pre-operatively acquired diagnostic image data and from the results of the surgery plan according to this embodiment of the invention. Preferably, the RF antennae are arranged on the substrate at a pre-determined minimum distance from the interventional field and/or from the access path. This ensures that the interventional field is freely accessible for the surgeon. Furthermore, interferences between the RF antennae and the surgical instruments are avoided.
According to yet another preferred embodiment of the invention, the sizes and/or the shapes of the RF antennae and/or their positions on the substrate are computed on the basis of a simulation of the RF electromagnetic field distribution during MR signal acquisition. This means that a RF electromagnetic field simulation is performed in order to automatically determine the optimum sizes, shapes, and/or positions of the RF antennae in order to optimize the signal-to-noise ratio for MR signals acquired from the interventional field and/or from the access path. As explained above, this optimization may be constrained by the provision of one or more apertures on the substrate, which have to be kept clear from the RF antennae in order to enable access to the patient's body during surgery.
In yet another preferred embodiment of the invention, the final design of the personalized RF coil array is transferred to a rapid prototyping facility, where the personalized RF coil array is fabricated. After the fabrication step the RF coil array is ready to be used for the planned surgical intervention.
The method of the invention may further comprise the step of arranging electronic components for RF signal transmission and/or reception via the RF antennae on the substrate. Such electronic components may be, for example, RF connectors for connecting RF cables to the individual antennae, RF tuning and/or matching networks, or RF pre-amplifiers directly connected to the RF antennae. Also these electronic components may be fabricated (at least in part) by means of rapid prototyping. Per se known techniques for generating printed circuit boards and associated components by means of rapid prototyping can be used for this purpose. Further discrete electronic components, which cannot be manufactured by rapid prototyping methods, can be assembled and integrated into the personalized RF coil array in a separate manufacturing step.
In a possible embodiment of the invention, the RF antennae, which are arranged on the substrate of the personalized RF coil array, are standardized RF coil modules. The use of standardized and pre-fabricated RF coil modules in the personalized RF coil array of the invention facilitates the manufacturing process. The individual standardized RF coil modules are positioned on the substrate and/or interconnected such that the signal-to-noise ratio for MR signals acquired from the interventional field and/or from the access path is optimized.
The invention does not only relate to a method, but also to a computer program, which comprises instructions for:
loading diagnostic image data reflecting the anatomy of a portion of a patient's body;
interactive planning of an intervention on the basis of the loaded diagnostic image data, wherein an interventional field within the patient's body portion is determined;
computing sizes, shapes and/or positions of one or more RF antennae to be arranged on a substrate, which is adapted to the patient's anatomy, in such a manner that the signal-to-noise ratio of MR signal acquisition via the one or more RF antennae from the interventional field is optimized.
Such a computer program can be loaded into a dedicated computer workstation comprising a display unit, via which interactive surgery planning on the basis of the loaded diagnostic image data is enabled. The computer workstation can be directly connected to a rapid prototyping facility, which manufactures a personalized RF coil array comprising the substrate and the RF antennae arranged on the substrate according to the automatically computed sizes, shapes, and/or positions.
The enclosed drawings disclose preferred embodiments of the present invention. It should be understood, however, that the drawings are designed for the purpose of illustration only and not as a definition of the limits of the invention. In the drawings:
With reference to
A magnetic resonance generation and manipulation system applies a series of RF pulses and switched magnetic field gradients to invert or excite nuclear magnetic spins, induce magnetic resonance, refocus magnetic resonance, manipulate magnetic resonance, spatially and otherwise encode the magnetic resonance, saturate spins, and the like to perform MR imaging.
Most specifically, a gradient pulse amplifier 3 applies current pulses to selected ones of whole-body gradient coils 4, 5 and 6 along x, y and z-axes of the examination volume. A digital RF frequency transmitter 7 transmits RF pulses or pulse packets, via a send-/receive switch 8, to a -body RF coil 9 to transmit RF pulses into the examination volume. A typical MR imaging sequence is composed of a packet of RF pulse segments of short duration which taken together with each other and any applied magnetic field gradients achieve a selected manipulation of nuclear magnetic resonance. The RF pulses are used to saturate, excite resonance, invert magnetization, refocus resonance, or manipulate resonance and select a portion of a body 10 positioned in the examination volume. The MR signals are also picked up by the body RF coil 9.
For intra-operative generation of MR images of the head region of the body 10, for example by means of parallel imaging, a set of local array RF antennae (coils) 11, 12, 13 are placed on a mask 19, which constitutes a substrate adapted to the patient's head anatomy within the meaning of the invention. The RF coils 11, 12, 13 are positioned contiguous to the head region selected for imaging. Hence, high-quality MR images can be acquired, for example, during brain surgery. The array coils 11, 12, 13 can be used to receive MR signals induced by body-coil RF transmissions.
The resultant MR signals are picked up by the body RF coil 9 and/or by the array RF coils 11, 12, 13 and demodulated by a receiver 14, preferably including a pre-amplifier (not shown). The receiver 14 is connected to the RF coils 9, 11, 12 and 13 via send-/receive switch 8.
A host computer 15 controls the current flow through the shimming coils 2′ as well as the gradient pulse amplifier 3 and the transmitter 7 to generate any of a plurality of MR imaging sequences, such as echo planar imaging (EPI), echo volume imaging, gradient and spin echo imaging, fast spin echo imaging, and the like. For the selected sequence, the receiver 14 receives a single or a plurality of MR data lines in rapid succession following each RF excitation pulse. A data acquisition system 16 performs analog-to-digital conversion of the received signals and converts each MR data line to a digital format suitable for further processing. In modern MR devices the data acquisition system 16 is a separate computer which is specialized in acquisition of raw image data.
Ultimately, the digital raw image data is reconstructed into an image representation by a reconstruction processor 17 which applies a Fourier transform or other appropriate reconstruction algorithms, such like SENSE or GRAPPA. The MR image may represent a planar slice through the patient, an array of parallel planar slices, a three-dimensional volume, or the like. The image is then stored in an image memory where it may be accessed for converting slices, projections, or other portions of the image representation into appropriate format for visualization, for example via a video monitor 18 which provides a human-readable display of the resultant MR image.
| Number | Date | Country | Kind |
|---|---|---|---|
| 11166210.2 | May 2011 | EP | regional |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/IB2012/052309 | 5/9/2012 | WO | 00 | 11/13/2013 |
