Source: http://www.google.fr/patents/US8788020
Timestamp: 2018-01-16 08:00:04
Document Index: 308295771

Matched Legal Cases: ['Application No. 2006', 'Application No. 2011', 'Application No. 2006', 'Application No. 04793980', 'Application No. 04793980', 'Application No. 04783114', 'Application No. 12164387', 'Application No. 04793980', 'Application No. 12', 'Application No. 2006', 'Application No. 2006', 'Application No. 2006', 'Application No. 2006', 'Application No. 2011', 'Application No. 2011', 'Application No. 2006', 'Application No. 04793980', 'Application No. 04783114', 'art 82']

Brevet US8788020 - Method and system for radiation application - Google Brevets
A method for generating one or more images includes collecting data samples representative of a motion of an object, acquiring image data of at least a part of the object over a time interval, synchronizing the data samples and the image data to a common time base, and generating one or more images based...http://www.google.fr/patents/US8788020?utm_source=gb-gplus-shareBrevet US8788020 - Method and system for radiation application
Numéro de publication US8788020 B2
Numéro de demande US 10/678,741
Autre référence de publication EP1677675A2, EP1677675A4, EP1677675B1, US7620444, US20040116804, US20040138557, US20140371581, WO2005032647A2, WO2005032647A3
Numéro de publication 10678741, 678741, US 8788020 B2, US 8788020B2, US-B2-8788020, US8788020 B2, US8788020B2
Inventeurs Hassan Mostafavi, Lisa Ann Hampton
Cessionnaire d'origine Varian Medical Systems, Inc.
Citations de brevets (211), Citations hors brevets (202), Référencé par (15), Classifications (39), Événements juridiques (2)
US 8788020 B2
acquiring image data of at least a part of an object,
calculating an image phase value, and
assigning the image phase value for the image data using a processor, wherein the act of assigning results in binning of the image data;
calculating an image phase value,
assigning the image phase value for the image data to thereby bin the image data,
acquiring additional image data, wherein the image data and the additional image data are acquired at different times,
calculating an additional image phase value, and
assigning the additional image phase value for the additional image data,
wherein the image phase value is different from the additional image phase value, thereby resulting the image data and the additional image data being binned in different respective first and second groups.
17. The system of claim 16, wherein the processor is further configured for
generating a first volumetric image using the image data binned in the first group; and
generating a second volumetric image using the additional image data binned in the second group.
FIG. 13 b illustrates sample trains according to an embodiment of the invention.
According to one embodiment, one or more passive markers 114 are located on the patient in the area to be detected for movement. Each marker 114 preferably comprises a reflective or retro-reflective material that can reflect light, whether in the visible or invisible wavelengths. If the illumination source is co-located with camera 108, then marker 114 preferably comprises a retro-reflective material that reflects light mostly in the direction of the illumination source. Alternatively, each marker 114 comprises its own light source. The marker 114 is used in place of or in conjunction with physical landmarks on the patient's body that is imaged by the camera 108 to detect patient movement. Markers 114 are preferably used instead of body landmarks because such markers 114 can be detected and tracked more accurately via the video image generated by camera 108. Because of the reflective or retro-reflective qualities of the preferred markers 114, the markers 114 inherently provide greater contrast in a video image to a light detecting apparatus such as camera 108, particularly when the camera 108 and illumination source are co-located.
According to one embodiment of the invention, physiological gating is performed by sensing physiological motion, e.g., respiration motion, using video tracking of retro-reflective markers attached to a marker block. One embodiment of the marker block 1471 utilizes two markers 1473 and 1475 on a rigid hollow and light plastic block 1477 measuring about 6 Cm×4 Cm×4 Cm as shown in FIG. 14 c. The two markers 1473 and 1475 are preferably placed at a fixed distance of three centimeter on the side of the block that will face the tracking camera. The fixed distance between the two markers 1473 and 1475 is known and is used to calibrate the motion of the block in the direction of the line connecting the two markers.
FIG. 15 depicts a flowchart of a process for tracking a marker block (e.g., marker blocks shown in FIG. 14 a or 14 b) using a single camera according to an embodiment of the invention. At step 1502, the coordinates of the markers on the marker block are accurately surveyed in a coordinate system affixed to the marker block. This survey data is stored as reference data, and provides the known relative positioning and distances between markers on the marker block. At step 1504, the geometric calibration model of the overall imaging chain is obtained and stored. The parameters of this model relate the position of a point in 3-dimensional reference coordinates of the room or treatment area where the patient is located to the 2-dimensional image coordinates of the corresponding pixel in the digital image. This calibration model for both steps 1502 and 1504 can be derived offline, e.g., after the camera is mounted rigidly in the room, and is preferably repeated occasionally as a check.
In addition, in alternative embodiments, the above described method for retrospective gating can also include the step of assigning a confidence number to each target phase interval or time bin. For example, any of the systems and methods described herein can be used to detect a deviation from periodicity of a physiological movement (e.g., due to coughing). In such case, the higher the degree of deviation detected within a target phase interval, the lower the confidence number is assigned to the target phase interval. In one embodiment, the confidence number can be calculated based on a degree of match between the measured physiological movement and a reference motion data representative of a normal or expected physiological movement. In some embodiments, a patient's breathing can be regulated using any of the systems and methods described herein to increase the confidence number for one or more target phase intervals.
During the planning phase of the radiation treatment, gating simulations can be performed to determine the optimum boundaries of the treatment intervals. FIG. 12 a depicts a system 1200 that can be employed to perform gating simulation. As with the system 100 shown in FIG. 1, system 1200 comprises a camera 108 that is directed at a patient on a treatment table 104. The output signals of camera 108 are sent to a computer 110 for processing. System 1200 additionally includes an imaging system capable of generating images of internal structures within the patient's body. In an embodiment, system 1200 comprises a digital fluoroscopic imaging system having an x-ray source 1202 and fluoroscopic x-ray detection apparatus 1204. The resulting fluoro video can be displayed on a fluoro display device 1206. In addition, the output signals from the fluoroscopic x-ray detection apparatus 1204 can be sent to the computer 110.
During gating simulation, the movement of one or more landmarks or markers 114 on the patient's body is optically measured using camera 108. The detected motion of the landmark or marker 114 results in the generation of motion signals according to the process discussed with reference to FIG. 2. While motion data is being collected, the fluoroscopic video system generates imaging data for the tumor or tissue that is targeted for irradiation. The present invention records the fluoroscopic image data and the marker motion data simultaneously on a common time base. In an embodiment, the positional geometry of the fluoroscopic imaging system is configured to correspond to the projection geometry of the radiation beam source that will be used in applying radiation beams for treatment. This allows accurate simulation of the target volume to be achieved during actual treatment.
FIG. 18 illustrates how the invention can be used to position a patient 106 among multiple medical devices. For the purposes of illustration, consider a common scenario for performing radiation therapy. A first phase of radiation therapy is a setup or treatment planning operation that consists of performing scanning or imaging procedures upon the patient to accurately locate and define the area of the patient body to be treated, e.g., using CT, MRI, SPECT, or PET procedures. The image data is used to develop a radiation treatment plan. The treatment plan often comprises the dosage level and treatment volume of radiotherapy to apply to the patient. The treatment planning phase may also comprise a simulation procedure to verify the appropriateness of the treatment plan. Once the treatment plan is developed, the second phase involves moving the patient to a radiation therapy device to implement the treatment plan. To optimize this procedure, the patient's relative position to the radiation therapy device should be consistent relative to the patient's imaging position for the image data used to develop the treatment plan.
According to an embodiment of the invention, the optical position and motion monitoring system of the present invention is usable to accurately and consistently position a patient among multiple medical devices. Shown in FIG. 18 is a patient 106 co-located with a marker block 114. During setup operations, the patient is scanned or imaged using an imaging device, such as MRI device 1802 or a CT system. During patient setup, a first video camera 108 a provides images of the patient to record the position and orientation of the marker block 114. The 3-dimensional position or machine isocenter coordinates of the marker block 114 for the imaging session at the MRI device 1802 is stored as reference data.
FIG. 21 shows an interface window for controlling a CT gating and monitoring system. A control portion 2102 is used to turn on or off CT gating. The control portion 2106 sets a threshold value for determining deviation from periodicity of the breathing cycle, e.g., as used for the process of FIG. 13 a. The control portion 2108 determines whether gating is performed based upon either amplitude or phase. The control portion 2104 allows entry of the known or estimated CT scanner delay and scan length parameters for the CT scanners that do not have a feedback interface for automatic sensing of these parameters. These parameters are used to show the best estimate of the CT scan period on the breathing chart. In an embodiment of the invention the portion of breathing chart corresponding to the CT scan period is drawn in color green. For example in a therapy application this allows selection of gating thresholds that result in the best match of the beam-on period and the CT image acquisition interval, i.e., the user tries to match the beam-on period with the green portions of the breathing chart.
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35 European Office Action Dated Jun. 14, 2012 for EP Application No. 04793980.6.
36 European Office Action dated Jun. 5, 2012 for EP Application No. 04783114.4.
37 European Office Action Dated Mar. 12, 2012 for EP Application 04782961.9.
38 European Office Action Dated Mar. 29, 2011 for EP Application 04782961.9.
39 European Office Action Dated Mar. 8, 2011 for EP Application 04793980.6.
40 European Office Action Dated Oct. 7, 2010 for EP Application 04783505.3.
41 European Office Action Dated Sep. 7, 2010 for EP Application 04782961.9.
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Classification internationale A61N5/10, A61B19/00, A61B5/055, A61B6/00, A61B5/11, A61B5/05, A61B6/03, A61N
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