FIELD OF THE INVENTION
The invention relates to the detection of x-ray and gamma quanta. It finds application in the medical field, more particularly in the fields of medical imaging and medical interventions, and may be used for example to provide an x-ray image and a corresponding nuclear image of a region of interest.
BACKGROUND OF THE INVENTION
In various medical imaging procedures it is beneficial to provide both an x-ray image and a nuclear image of a region of interest. The x-ray image typically provides structural information indicative of the anatomy of the region of interest. The nuclear image, defined herein to mean an image indicative of radiotracer distribution in an object, is generated based on detected gamma quanta. The nuclear image may for example be a gamma scintigraphy or a SPECT image and typically provides functional, or physiological information relating to the region of interest. Together the two different image types can be used to improve the identification of an underlying pathology during a medical investigation.
Various medical procedures also benefit from a combination of x-ray and nuclear imaging. Selective internal radiation therapy, or SIRT, is one such medical procedure in which radiation is used to treat cancer. SIRT is often used for non-resectable cancers, i.e. cancers that cannot be treated surgically, and involves injecting microspheres of radioactive material into the arteries that supply the tumor. Liver tumors or metastases are often treated in this way. However, in delivering such therapy, a number of workflow steps are required in order to prevent potential side effects. These steps may include the closure of atypical lung and gastrointestinal shunts before injection of Yttrium-90 -containing microspheres. This prevents radiation ulcers which might otherwise be triggered by extra-hepatic localization of administered micro-spheres. For this purpose, catheter-based vessel coiling is performed under x-ray guidance during a minimally-invasive procedure. Afterwards, the remaining shunt level towards lungs and gastrointestinal area may be controlled by injection of Technetium 99mTc albumin aggregated, i.e. Tc-labeled MAA, into both main liver arteries followed by planar gamma imaging. During this procedure the patient is typically repeatedly transported between a cath lab and SPECT imaging room.
A need therefore exists for imaging systems that are capable of providing both a nuclear image and an x-ray image.
Document US2009/0016488A1 describes a medical diagnostic system having two c-arms which are adjustable with the aid of two drive means and serve as retaining devices for one medical measuring system in each case. The first measuring system is an x-ray measuring system comprising an x-ray emitter and an x-ray detector and has a high spatial resolution. The second measuring system is a nuclear medicine measuring system for visualizing tissue functions. Medical diagnoses and interventions are possible based on image information generated by both measuring systems.
However, in the field of medical imaging, and in the field of medical procedures, there remains a need for improved imaging systems that are capable of providing both a nuclear image and an x-ray image.
SUMMARY OF THE INVENTION
It is an object of the invention to provide a system for providing both a nuclear image and an x-ray image of a region of interest. Thereto a medical imaging arrangement is provided.
The medical imaging arrangement includes an x-ray source, an x-ray detector, an x-ray c-arm, and a gamma camera. The x-ray source is attached to a first portion of the x-ray c-arm and the x-ray detector is attached to a second portion of the x-ray c-arm. The x-ray source and the x-ray detector are so-positioned in order to measure x-ray transmission along a path between the x-ray source and the x-ray detector. Moreover, the gamma camera is movable along a trajectory that intersects the path between the x-ray source and the x-ray detector. Advantageously, because the gamma camera can be moved along a trajectory that intersects the path between the x-ray source and the x-ray detector, the images generated by the x-ray source and detector and the gamma camera are in close correspondence.
According to one aspect the imaging arrangement includes a patient support pallet. The patient support pallet is translatable along a longitudinal axis that passes lengthwise through the patient support pallet. Moreover the path between the x-ray source and the x-ray detector is arranged transversely with respect to the longitudinal axis. This arrangement provides improved imaging access around an object supported by the patient support pallet.
According to another aspect, in the imaging arrangement the trajectory intersects the path between the x-ray source and the x-ray detector at a point that is closer to the x-ray source than to the x-ray detector. Advantageously, in this positon the x-ray source-detector arrangement has a narrow field of view and thus sequential x-ray—nuclear imaging can be achieved with minimal movement of the gamma detector. Also, simultaneous x-ray—nuclear imaging can be achieved with a minimally-offset gamma detector.
Other aspects of the invention are described by the dependent claims.
BRIEF DESCRIPTION OF THE FIGURES
FIG. 1 illustrates a first embodiment of a medical imaging arrangement that includes an x-ray source 111, an x-ray detector 112, an x-ray c-arm 113, and a gamma camera 114.
FIG. 2 illustrates a second embodiment of a medical imaging arrangement that includes an x-ray source 211, an x-ray detector 212, and an x-ray c-arm 213.
FIG. 3 illustrates a third embodiment of a medical imaging arrangement that includes an x-ray source 311, an x-ray detector 312, an x-ray c-arm 313, a gamma camera 314 and a patient support pallet 317.
FIG. 4 illustrates a fourth embodiment of a medical imaging arrangement that includes patient support pallet 417 that is translatable along a longitudinal axis 418, and in which gamma camera 414 is movable along trajectory 416 that is comprised within a plane that transversely intersects longitudinal axis 418.
DETAILED DESCRIPTION OF THE INVENTION
As described above, the present invention provides a system for providing both a nuclear image and an x-ray image of a region of interest. Thereto a medical imaging arrangement is provided.
FIG. 1 illustrates a first embodiment of a medical imaging arrangement that includes an x-ray source 111, an x-ray detector 112, an x-ray c-arm 113, and a gamma camera 114. As illustrated in FIG. 1, x-ray source 111 is attached to a first portion of x-ray c-arm 113 and x-ray detector 112 is attached to a second portion of x-ray c-arm 113. The x-ray source and the x-ray detector are so-positioned in order to measure x-ray transmission along path 115 between the x-ray source and the x-ray detector. The field of view FOV of the x-ray source—x-ray detector arrangement in FIG. 1 is illustrated by the short dashed lines that comprise path 115. Moreover, gamma camera 114 is movable along trajectory 116 as indicated. Trajectory 116 may for example be defined by rails, or by an extendable member, or by grooves in a surface or by another support structure not shown in FIG. 1. Trajectory 116 intersects path 115 between x-ray source 111 and x-ray detector 112 at point Pint1.
Advantageously, because gamma camera 114 can be moved along a trajectory that intersects path 115 between x-ray source 111 and x-ray detector 112, gamma camera 114 can be used to generate a nuclear image that corresponds to the same region of interest ROI as that which is imaged by x-ray source 111 and x-ray detector 112. Because the trajectory and the path intersect one another, close correspondence between the nuclear image and the x-ray image can be achieved. Moreover, when the gamma camera has its own support structure, independent movement between the gamma camera and the x-ray c-arm can be achieved, thereby providing increased positioning flexibility.
Preferably, x-ray detector 112 in FIG. 1 is a flat panel x-ray detector array that includes an array of x-ray scintillator elements for generating x-ray scintillation light and a corresponding array of photodetectors arranged to capture the x-ray scintillation light. X-ray detector 112 may alternatively include a curved panel or a plurality of flat panel segments arranged around an arc to provide a curved geometry. X-ray source 111 can be a standard x-ray source, although it is also contemplated to use a dual energy source in this position. X-ray c-arm 113 is an otherwise standard x-ray c-arm and may be mounted in a fixed position or optionally arranged for movement as illustrated by the arrows near its support.
In addition to intersection point Pint1, trajectory 116 in FIG. 1 may also include an offset position along the trajectory in which the gamma camera is not intercepted by path 115 between the x-ray source and detector. This may for example be to one end of trajectory 116 at which position the gamma camera is beyond the field of view FOV of the x-ray source 111—x-ray detector 112 arrangement. The ability to move gamma camera 114 along trajectory 116 between point of intersection Pint1, and the offset position provides two possible nuclear imaging positions in which differing views and thus degrees of correspondence between the x-ray image and the nuclear image can be achieved. Clearly, additional nuclear imaging positions along trajectory 116 may also be provided. Moreover, the gamma camera may be positioned in the offset position where it is beyond the field of view FOV of the x-ray source and detector during x-ray imaging in order to prevent the gamma camera from obscuring or being affected by x-ray radiation emitted by x-ray source 111.
In-use, the arrangement of FIG. 1 may be used in a number of different modes. In one exemplary mode, x-ray source 111—x-ray detector 112 arrangement may be used to generate single-shot or a continuous stream of x-ray images of region of interest ROI in order to perform a medical procedure. One such medical procedure is the catheter-based vessel coiling procedure outlined above. Having performed the medical procedure under x-ray guidance, gamma camera 114 may be moved along trajectory 116 to point Pint1where trajectory 116 intersects path 115. In this position gamma camera 114 can be used to generate a nuclear image of the ROI that closely corresponds to the x-ray image. Moreover, because point Pint1 is close to region of interest ROI, a high number of gamma counts from the ROI will be detected by gamma camera 114, in short resulting in a higher resolution nuclear image. Thus, in this exemplary mode the x-ray and nuclear images may be generated sequentially. In another exemplary mode x-ray and nuclear images may be generated simultaneously with gamma camera 114 in the above-described offset position. In this mode the x-ray and gamma camera views of the ROI are clearly slightly different. Advantageously, in this simultaneous imaging configuration, no further adjustments of the imaging system positions are needed after an initial set-up phase.
Other gamma camera trajectories to that illustrated in FIG. 1 may also be used. FIG. 2 illustrates a second embodiment of a medical imaging arrangement that includes an x-ray source 211, an x-ray detector 212, and an x-ray c-arm 213. Moreover, multiple optional gamma camera trajectories 216A, B, C for each of corresponding gamma cameras 214A, B, C are also shown in FIG. 2. For example, trajectories 216A and 216C are aligned with arbitrary axes y and x respectively, whereas trajectory 216B is an arc that lies in the z-x plane. In a preferred configuration a single gamma camera exemplified by one of gamma camera 214A, B, C is used, and this is movable along at least one of trajectories 216A, B, C. Multiple gamma cameras may also be used in a similar manner. X-ray source 211 and corresponding x-ray detector 212 in FIG. 2 are so-positioned in order to measure x-ray transmission along path 215 between x-ray source 211 and x-ray detector 212. Moreover, each exemplary gamma camera 214A, B, C is movable along its corresponding trajectory 116A, B, C as indicated. Arc-shaped trajectory 216B may for example be defined by rails, or by an extendable beam, or by grooves in a surface or by a c-arm not shown in in FIG. 1. Each of trajectories 216A, B, C intersect path 215 between x-ray source 211 and x-ray detector 212 at point Pint2. Optionally intersection point Pint2 is closer to x-ray source 211 than to x-ray detector 212. Advantageously, in this positon the x-ray source—x-ray detector arrangement has a narrow field of view and thus sequential x-ray —nuclear imaging can be achieved with minimal movement of the gamma detector. Also, simultaneous x-ray—nuclear imaging can be achieved with a minimally-offset gamma detector.
FIG. 3 illustrates a third embodiment of a medical imaging arrangement that includes an x-ray source 311, an x-ray detector 312, an x-ray c-arm 313, a gamma camera 314 and a patient support pallet 317. The x-ray source 311 and the x-ray detector 312 are positioned on x-ray c-arm 313 in order to measure x-ray transmission along path 315. Moreover, gamma camera 314 is movable along trajectory 316. Trajectory 316 intersects path 315 between x-ray source 311 and x-ray detector 312 at point Pint3. Moreover patient support pallet 317 has a longitudinal axis 318 that passes lengthwise through the patient support pallet, and the patient support pallet 317 is translatable along longitudinal axis 318. Furthermore, path 315 between x-ray source 311 and x-ray detector 312 is arranged transversely with respect to longitudinal axis 318. Because the patient support pallet 317 is translatable along longitudinal axis 318, improved imaging access around an object supported by the patient support pallet can be achieved.
Preferably, trajectory 316 and longitudinal axis 318 in FIG. 3 are mutually parallel. This allows gamma camera 314 to be moved in harmony with the positon of an object supported by patient support pallet 317, thereby offering continuous nuclear imaging of the object during movement of the patient support pallet, for example during live x-ray imaging. In one configuration gamma camera 314 may be attached-to, or supported by patient support pallet 317, optionally via a gamma camera support structure. This allows the same portion of an object supported by patient support pallet 317 to be imaged by gamma camera 314 during translation of patient support pallet 317 along its longitudinal axis. This in turn improves image quality because a gamma image of the object can be continuously, i.e. even during translation of the object during x-ray imaging. Moreover, such a supporting arrangement ensures close correspondence between patient motion and motion of the gamma camera, thereby improving image quality. In another configuration gamma camera 314 is translatable with respect to patient support pallet 317. This permits an operator to either image a different portion of an object supported by patient support pallet 317, or to move gamma detector 314 to an offset position during x-ray imaging in order to prevent the gamma camera from obscuring or being affected by x-ray radiation as described above.
FIG. 4 illustrates a fourth embodiment of a medical imaging arrangement that includes patient support pallet 417 that is translatable along a longitudinal axis 418, and in which gamma camera 414 is movable along trajectory 416 that is comprised within a plane that transversely intersects longitudinal axis 418. Thus, in contrast to FIG. 3, in the arrangement of FIG. 4 trajectory 416 is comprised within a plane that transversely intersects longitudinal axis 418. This offers alternative access for performing nuclear imaging of an object positioned on patient support pallet 417. Advantageously, this configuration can be used to provide nuclear imaging from different angular positions to longitudinal axis 318. Preferably trajectory 416 includes an arc of rotation. Such an arc can be used to reduce the change in distance from gamma detector 414 to the center of an object in the region of interest during nuclear imaging and thereby minimize depth-dependent scatter effects in the region of interest. Alternatively trajectory 416 may be a straight line. Optionally gamma camera 414 is attached to a gamma camera c-arm 421 and the arc of rotation is defined by a movement of the gamma camera along the gamma camera c-arm.
Optionally, x-ray c-arms 313, 413 in FIG. 3 and FIG. 4 respectively may include x-ray c-arm support 320, 420 which may be configured to rotate x-ray c-arm 313, 413 about x-ray c-arm axis 319, 419. X-ray c-arm support may also be configured to rotate the c-arm itself X-ray c-arm support 320, 420 may include a swivel bearing or a sliding joint or geared track to permit such movement. X-ray c-arm axis 319, 419 and the corresponding longitudinal axis 318, 418 are mutually parallel. Moreover, in the Figures, x-ray c-arm axis 319, 419 is parallel to the y-axis. X-ray c-arm support 320, 420 may thus be used to move c-arm 313, 413 in the direction of the dotted arrows in order to achieve the rotation in the illustrated x-z plane. X-ray c-arm support 320, 420 may for example include a gear mechanism that engages with teeth attached to the c-arm in order to effect this movement. In so doing more flexible positioning of the x-ray and nuclear cameras can be achieved. The term parallel as used throughout this specification is intended to mean within approximately ±10 degrees, or within ±5 degrees of exactly parallel.
X-ray c-arms 313, 413 in FIG. 3 and FIG. 4 may additionally or alternatively be configured for rotation about the illustrated x-axis as-shown in order to further improve positioning flexibility.
In one arrangement, x-ray c-arm support 320, 420 and the gamma camera support structure are held in fixed mechanical relation to one another. Such an arrangement provides close correspondence between an x-ray image generated by the x-ray source and the x-ray detector, and an image generated by the gamma camera since any vibrations will tend to affect both imaging systems in a similar manner.
In summary a medical imaging arrangement has been described. In the medical imaging arrangement 100 an x-ray source 111 is attached to a first portion of an x-ray c-arm 113 and an x-ray detector 112 is attached to a second portion of the x-ray c-arm 113 in order to measure x-ray transmission along a path 115 between the x-ray source and the x-ray detector. A gamma camera 114 is movable along a trajectory 116 that intersects the path between the x-ray source and the x-ray detector. Since the gamma camera can be moved along a trajectory that intersects the path between the x-ray source and the x-ray detector, the gamma camera can be used to generate a nuclear image that closely corresponds to the same region of interest as that which is imaged by the x-ray source and detector.
Patent Application
20190046137
