WO2019077385A1 - Système de traitement et procédé de correction dynamique pour thérapie thermique - Google Patents

Système de traitement et procédé de correction dynamique pour thérapie thermique Download PDF

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Publication number
WO2019077385A1
WO2019077385A1 PCT/IB2017/001506 IB2017001506W WO2019077385A1 WO 2019077385 A1 WO2019077385 A1 WO 2019077385A1 IB 2017001506 W IB2017001506 W IB 2017001506W WO 2019077385 A1 WO2019077385 A1 WO 2019077385A1
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WIPO (PCT)
Prior art keywords
mask
applying
thermal therapy
image
phase
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PCT/IB2017/001506
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English (en)
Inventor
Alexandre BIGOT
Patrick Leonard
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Profound Medical Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Profound Medical Inc. filed Critical Profound Medical Inc.
Priority to CA3075454A priority Critical patent/CA3075454A1/fr
Priority to JP2020522012A priority patent/JP2021500126A/ja
Priority to CN201780095968.9A priority patent/CN111225609B/zh
Priority to PCT/IB2017/001506 priority patent/WO2019077385A1/fr
Publication of WO2019077385A1 publication Critical patent/WO2019077385A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
    • A61B5/015—By temperature mapping of body part
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4848—Monitoring or testing the effects of treatment, e.g. of medication
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N7/02—Localised ultrasound hyperthermia
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2218/00—Details of surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2505/00—Evaluating, monitoring or diagnosing in the context of a particular type of medical care
    • A61B2505/05—Surgical care
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2576/00—Medical imaging apparatus involving image processing or analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/43—Detecting, measuring or recording for evaluating the reproductive systems
    • A61B5/4375—Detecting, measuring or recording for evaluating the reproductive systems for evaluating the male reproductive system
    • A61B5/4381—Prostate evaluation or disorder diagnosis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/70—Means for positioning the patient in relation to the detecting, measuring or recording means
    • A61B5/704—Tables
    • G—PHYSICS
    • G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H30/00—ICT specially adapted for the handling or processing of medical images
    • G16H30/40—ICT specially adapted for the handling or processing of medical images for processing medical images, e.g. editing

Definitions

  • the present application relates to thermal therapy and/or other systems and methods that use temperature measurements derived from magnetic resonance imaging (MRI).
  • MRI magnetic resonance imaging
  • Temperature measurements derived from MRI methods are subject to errors or potential errors from a variety of sources. These errors or potential errors can create temperature measurement uncertainty and/or significantly reduce the accuracy of measuring temperature changes.
  • Unintended heating of other regions may require that thermal therapy be halted, at least temporarily, in order to allow such regions to cool. This can result in a less than optimal thermal therapy session from a patient comfort perspective, as well as less economical use of the MRI-thermal therapy facility, personnel and equipment.
  • At least some aspects disclosed herein have the ability to address noise from various sources, including: magnetic resonance (MR) artifacts, frequency drift, low SNR regions, non-uniform tissue structures and/or others.
  • MR magnetic resonance
  • a method comprises: receiving data indicative of at least one phase image captured using a magnetic resonance imaging (MRI) device during delivery of thermal therapy by a thermal therapy applicator to a target volume within a patient's body; and processing said at least one phase image; wherein said processing said at least one phase image comprises: applying a first mask; applying phase unwrap; and applying a second mask.
  • MRI magnetic resonance imaging
  • the first mask and the second mask each provide diminishment and/or enhancement of one or more pixels in a phase (or other) image relative to one or more other pixels in the phase (or other) image, sometimes referred to herein as subjugation of one or more pixels in a phase (or other) image.
  • the first mask and the second mask can each be categorized as either: (1 ) a static mask, which may be defined before
  • treatment begins, based on user-defined landmarks or otherwise, and is not expected to change during treatment or (2) a dynamic mask, which may be computed or otherwise determined for every dynamic (or otherwise) during treatment, and may change during treatment.
  • the method further comprises determining a treatment plan based at least in part on the processed at least one phase image; and delivering thermal therapy to the target volume within the patient's body based at least in part on said treatment plan using a thermal therapy applicator.
  • said applying phase unwrap comprises: applying said phase unwrap between said applying a first mask and said applying a second mask.
  • said thermal therapy comprises ultrasound thermal therapy; and said thermal therapy applicator comprises an ultrasound thermal therapy applicator.
  • said first mask is a static mask and said second mask is a dynamic mask.
  • said first mask and/or said second mask comprises a therapy applicator mask.
  • said therapy applicator mask is an ultrasonic applicator mask
  • said first mask and/or said second mask comprises a target region mask.
  • said target region mask is a prostate mask.
  • said first mask and/or said second mask comprises a restricted region mask.
  • said restricted region mask is a rectum mask.
  • said first mask and/or said second mask comprises a dynamic mask and wherein said dynamic mask comprises a sector mask.
  • said first mask and/or said second mask comprises a dynamic mask and wherein said dynamic mask comprises a noise mask.
  • a system comprises at least one computer hardware processor configured to perform the method.
  • At least one non-transitory computer readable storage medium stores processor-executable instructions that, when executed by at least one processor, result in the method.
  • FIG. 1 is a diagram of one type of system in which at least some of the methods disclosed herein are employed, in accordance with at least some
  • Fig. 2A is a diagram of an image-guided thermal therapy system, which may be used in the medical system of Fig. 1 , in accordance with at least some embodiments;
  • Fig. 2B is a schematic diagram of a portion of the image-guided thermal therapy system in one possible operating mode, in accordance with at least some embodiments;
  • FIG. 3 illustrates a cross section of a prostate and a therapy applicator inserted therein to allow thermal therapy, in accordance with at least some
  • Fig. 4 is a representation of MRI image data that may be captured, in accordance with at least some embodiments.
  • Fig. 5A is a visualization of an image, in accordance with at least some embodiments.
  • Fig. 5B is a visualization of an image, in accordance with at least some embodiments.
  • Fig. 6 is a representation of pixel values defining a portion of a pixel array, in accordance with some embodiments;
  • Fig. 7 is a representation of a mask, in accordance with some embodiments;
  • Fig. 8 is a representation of an application of a portion of a mask to a portion of an image, in accordance with some embodiments.
  • Fig. 9 is a representation of an AND operation performed on two masks; in accordance with some embodiments.
  • Fig. 10. is a table that identifies three different types of structural masks, in accordance with some embodiments.
  • Figs. 1 1 A-1 1 C are representations of masks shown in Fig. 10, in accordance with at least some embodiments;
  • Fig. 12. is a table that identifies three different types of dynamic masks, in accordance with at least some embodiments.
  • FIGs. 13A-13C are enlarged representations of masks shown in Fig. 12, in accordance with at least some embodiments;
  • Fig 14. is a table that shows five different types of dynamic corrections that may be employed, in accordance with at least some embodiments.
  • Fig. 15 is a flowchart of a method, in accordance with at least some embodiments.
  • Fig. 16A is a visualization of an image, in accordance with at least some embodiments.
  • Fig. 16B is a visualization of an image, in accordance with at least some embodiments;
  • Fig. 17 is a graphical representation of one type of phase wrap, in accordance with at least some embodiments;
  • FIG. 1 8 are representations of a current image and a corresponding reference image, in accordance with at least some embodiments
  • Fig. 19 is a visualization of an image, in accordance with at least some embodiments.
  • Fig. 20 is a flowchart of a method, in accordance with at least some embodiments.
  • FIG. 21 A-D illustrate flowcharts of a method, in accordance with at least some embodiments.
  • Fig. 22 is a block diagram of an architecture, in accordance with at least some embodiments.
  • At least some aspects disclosed herein have the ability to address noise from various sources, including: magnetic resonance (MR) artifacts, frequency drift, low SNR regions, non-uniform tissue structures and/or others.
  • MR magnetic resonance
  • Fig. 1 is one type of system 100 in which at least some of the dynamic correction methods disclosed herein are employed, in accordance with at least some embodiments.
  • the system 100 which is a medical system, includes a patient support 106 (on which a patient 108 is shown), a magnetic resonance system 102 and an image guided thermal therapy system 104.
  • the magnetic resonance system 102 includes a magnet 1 10 disposed about an opening 1 12, an imaging zone 1 14 in which the magnetic field is strong and uniform enough to perform magnetic resonance imaging, a set of magnetic field gradient coils 1 16 to acquire magnetic resonance data 1 14, a magnetic field gradient coil power supply 1 1 8 that supplies current to the magnetic field gradient coils 1 16 and is controlled as a function of time, a radio-frequency coil 120 to manipulate the orientations of magnetic spins within the imaging zone 1 14, a radio frequency transceiver 122 connected to the radio frequency coil 120, and a computer 124, which performs tasks (by executing instructions and/or otherwise) to facilitate operation of the MRI system 102 and is coupled to the radio frequency transceiver 122, the magnetic field gradient coil power supply 1 1 8, and the mage guided thermal therapy treatment system 104.
  • the image guided thermal therapy system 104 which will be further discussed below, performs image guided thermal therapy and implements one or more aspects and/or embodiments disclosed herein (or portion(s)) thereof to reduce the effects of errors and/or potential errors (including: magnetic resonance (MR) artifacts, frequency drift, low SNR regions, non-uniform tissue structures and/or others) and/or otherwise.
  • MR magnetic resonance
  • the computer 124 of the MRI system 102 and/or one or more other computing devices (not shown) in and/or coupled to the system 100 may also perform one or more tasks (by executing instructions and/or otherwise) to implement one or more aspects and/or embodiments disclosed herein (or portion(s)) thereof to reduce the effects of errors and/or potential errors (including: magnetic resonance (MR) artifacts, frequency drift, low SNR regions, non-uniform tissue structures and/or others) and/or otherwise.
  • MR magnetic resonance
  • Fig. 2A is a stylized diagram of an implementation of the image guided thermal therapy system 104, in accordance with at least some embodiments.
  • the image guided thermal therapy system 104 includes a system controller 200, a therapy apparatus controller 202 and a therapy apparatus 204.
  • the system controller 200 (which may comprise a portable PC, workstation, or any other type of processing device) may performs task (by executing instructions and/or otherwise) to facilitate operation of the image guided thermal therapy system 104 and to implement one or more aspects and/or embodiments disclosed herein (or portion(s)) thereof to reduce the effects of errors and/or potential errors (including: magnetic resonance (MR) artifacts, frequency drift, low SNR regions, non-uniform tissue structures and/or others) and/or otherwise.
  • MR magnetic resonance
  • the system controller 200 may include a display and/or user interface 210 to facilitate user control of and/or observation of the thermal therapy treatment process, and may be coupled to and supply signals to the therapy apparatus controller 202 via communication link 220.
  • the therapy apparatus controller 202 (which may be part of the system controller 200) may comprise analog and/or digital circuitry to determine and/or provide drive signals to be supplied to the therapy apparatus 204, and may be coupled to the therapy apparatus via a power or other communication link 240.
  • the therapy apparatus 204 (which may be maneuvered by a motor assembly coupled thereto), may comprise an ultrasound or other treatment apparatus configured to deliver a suitable dose of ultrasound or other energy to tissue in a diseased region of a patient's body.
  • the therapy apparatus 204 comprises an elongated transurethral prostate therapy applicator having a portion 255 to be inserted longitudinally into a patient's prostate to deliver
  • the computer 124 of the MR system 102 may provide real-time
  • the system controller 200 may use the images to monitor (in real time or otherwise) the progress or other status of the thermal therapy and may generate signals based at least in part thereon to control the therapy apparatus controller 202.
  • Information indicative of the progress or other status may also be provided to a clinical or other operator, who may provide input (to the system controller 200 and/or the therapy apparatus controller 202) to adjust or otherwise control the thermal therapy.
  • the system 104 may have various operating modes.
  • Fig. 2B is a schematic diagram of a portion of the system 104 in one possible operating mode, in accordance with at least some embodiments.
  • the portion of the system includes an error amplifier
  • the therapy apparatus 204 outputs ultrasonic (or other) energy based at least in part thereon to one or more regions of a patient undergoing thermal treatment. The energy raises temperatures within the region(s), which are imaged using MRI techniques.
  • the MRI imaging is mapped to MRI temperature data, which is fed back to the error amplifier, which may adjust the output to the therapy apparatus controller 202 based at least in part thereon and/or as appropriate in subsequent steps of the treatment.
  • This general method may be followed until treatment's goals are satisfied (e.g., a given temperature is reached in the treatment region) or an alarm or other action interrupts the process.
  • FIG. 3 illustrates a cross section of a prostate 30 and an elongated transurethral prostate therapy applicator 304 inserted longitudinally therein to allow performance of conformal thermal therapy 308 to the prostate 30 (or a portion thereof), shown at a time tO, in accordance with at least some embodiments.
  • the prostate 30 has an organ boundary 300.
  • a treatment boundary 302 (representing a desired treatment volume), may be defined, for example, in a treatment planning step prior to or during application of the thermal therapy treatment.
  • the thermal therapy 308 may be directionally emitted from an active face of applicator 304.
  • the location/direction of the thermal therapy 308 at any given point in time, and the location of the control point 309 at any given point in time may depend on the angular position of applicator 304.
  • the thermal therapy 308 is represented in the figure by a flame-shaped profile or zone (sometimes referred to herein as a treatment zone lobe) extending from the applicator 304, however the thermal therapy 308 is not limited and may instead have any suitable configuration.
  • the thermal therapy applicator 304 may be rotated about its axis using a computer-controlled motor so as to sweep through the treatment volume defined by the treatment boundary 302, as described in earlier patents and applications, including: U.S. Patent Nos. 6,589,174; 7,771 ,41 8; U.S. Pubs. 2007/0239062; 201 1 /0034833; U.S. Patent Application Publication Nos. 12/932,914; 12/932,923; 12/932,920; and 13/065,106, which are all hereby incorporated by reference.
  • the rotation 307 may be performed at any rate(s), which may be predetermined (e.g., planned) and/or determined dynamically during the therapy process.
  • applicator 304 rotates in a clockwise direction 307 as shown, but is not limited to such.
  • a treatment boundary is an intended boundary within which the energy of the thermal therapy process is substantially controlled to a set-point temperature (or thermal dose) ensuring rapid and sufficient cell death of diseased cells within the interior of the volume defined by the treatment boundary.
  • Heat can be conducted outside the treatment boundary out to the boundary of an organ (e.g., the prostate), which can be measured and controlled to achieve appropriate thermal therapy while reasonably avoiding damage to non- diseased tissues and organs proximal to said diseased locations. Tissues and organs outside the treatment boundary, even if heated, should not exceed lethal thermal dose or temperature limits.
  • Fig. 4 is a representation 400 of MRI image data that may be captured before, during and/or after thermal therapy, in accordance with at least some embodiments.
  • the MRI image data may be made up of or otherwise comprise sets of MRI image data, e.g., sets of MRI image data 402I-402M.
  • Each set of MRI image data may include N images, e.g., cross sections (sometimes referred to as slices) and may be captured from an MRI device during a respective one of a plurality of collection periods, e.g., collection periods 404I-404M.
  • a collection period for a set of MRI image data is sometimes referred to herein as a dynamic.
  • each set of MRI image data may comprise
  • the amount of time, sometimes referred to herein as a dynamic, needed to capture and/or receive the 12 or other specified number of slices in the set may average 6 seconds or other amount of time.
  • one or more sets of MRI image data corresponding to one or more dynamics may be captured prior to start of therapy and used in determining a set of reference images.
  • the set of reference images will include one reference image for each slice in a set of MRI image data.
  • each reference image (phase or otherwise) may be generated by taking the mean of five or other number of images (phase or otherwise).
  • an "image" is a representation (exact or otherwise (i.e., non-exact)) of one or more objects (e.g., a body (or portion(s) thereof) of a patient, data, or any other type of object(s)) and/or one or more characteristics thereof (e.g., temperature(s) and/or other physical characteristic(s)).
  • An image may have any form(s). For example, some images may have the form of data that may be machine readable but need not be visible to a human eye.
  • An image may be received from any source(s).
  • An " MRI image” is an image that is based at least in part on MRI data.
  • a " phase image " is an image that is based at least in part on phase data.
  • a " magnitude image " is an image based at least in part on magnitude data.
  • phase image and magnitude image are not mutually exclusive. Thus, in at least some embodiments, an image may be both a " phase image " and a " magnitude image.
  • an uncorrected temperature may be calculated or otherwise determined for each pixel (in any given measurement image) as a difference between a phase of the pixel in the measurement image and a phase of the pixel in the corresponding reference image, multiplied by a constant.
  • the phase differences that are determined for the plurality of pixels in any given measurement image are sometimes collectively referred to herein as a phase difference image (or a phase difference).
  • phase images collected during a dynamic may be processed to form a temperature map.
  • Each temperature map may be stored in a buffer that has a width of M temperature maps (corresponding to M dynamics) and may be used to hold a rolling window of M temperature maps that may be used to calculate a temperature uncertainty map.
  • the MR image data comprises
  • MR thermometry functions by measuring changes in temperature sensitive parameters. Examples of such parameters are: the proton resonance frequency shift, the diffusion coefficient, or changes in the T1 and/or T2 relaxation time may be used to measure the temperature using magnetic resonance.
  • PRF proton resonance frequency
  • the resonant frequency of the protons is temperature dependent. As temperature changes in a voxel (an element in an array of volume) the frequency shifts, which causes the measured phase of the water protons to change.
  • the temperature change between two phase images can therefore be determined.
  • This method of determining temperature has the advantage that it is relatively fast in comparison to the other methods.
  • the PRF method is discussed in greater detail than other methods herein. However, the methods and techniques discussed herein are also applicable to the other methods of performing thermometry with magnetic resonance imaging.
  • At least some embodiments may rely on the proton resonant frequency shift which is known to vary with temperature according to the formula:
  • T temperature in degrees
  • ⁇ 0 phase difference
  • a thermal shift coefficient (ppm/°C)
  • Bo magnetic field strength (Tesla)
  • ⁇ gyromagnetic ratio for H+ nuclei (MHz/Tesla)
  • TE echo time (sec)
  • BaseTemp base temperature.
  • thermometry formula is based on the PRF-sensitivity of water content in tissues, in at least some embodiments, lipid and bone tissues produces unreliable temperature measurements which can be excluded from the thermometry region of interest when making temperature-based decisions.
  • Fig. 5A is a visualization 500 of one of the images in one of the sets of
  • MRI images e.g., one image in the set of MRI images 402i , showing temperature information for a portion of the patient's body in the vicinity of the treatment volume at a given point in time during a thermal therapy, in accordance with at least some embodiments.
  • the visualization 500 employs a grayscale (i.e., different shades of gray) to indicate different temperatures.
  • a grayscale i.e., different shades of gray
  • the visualization 500 may be displayed on a visual output device such as a computer monitor screen or other display.
  • Fig. 5B is a visualization 550 that is similar to the visualization 500 except that: (i) the temperature information in the visualization 550 has had thresholding applied thereto (as a result, each shade in the visualization 550 corresponds to a wider temperature range than does each shade in the visualization 500) and pixels have been inverted (lowest temperatures are shown in white, increasingly higher temperatures are shown in increasingly darker shades, highest temperatures are shown in black) to assist in the teaching herein, reproduction and allow use of reference lines to point to aspects without a need for color, (ii) a border 560 has been added to identify the portion of the visualization 550 that represents a surface of the patient's body (e.g., the surface of the patient's abdomen) in the visualization 550, (iii) a border 562 has been added to identify the portion of the visualization 550 that represents a treatment boundary in the patient, and (iv) borders have been added around portions of the visualization 550 that are associated with a same temperature range (after
  • the visualization 550 may be displayed on a visual output device such as a computer monitor screen or other display.
  • each image may comprise an array of pixels.
  • the array may have a plurality of rows and a plurality of columns, e.g., 128 rows and 128 columns, sometimes referred to herein as a 128 x 128 array configuration.
  • Each pixel may define or be defined by, at least in part, a pixel value.
  • a " pixel" is an element in a picture or any other type of image, of any kind, and which may or may not be visible to the human eye.
  • Fig. 6 is a representation 600 of pixel values defining a portion of a pixel array, in accordance with some embodiments.
  • the portion of the pixel array has sixteen values arranged in four rows 602-608 and four columns 612-61 8.
  • the first row includes values 50, 52, 54, 60.
  • the first column includes values 50, 20, 40, 41 . And so on. Any given value is sometimes referred to herein as image value,, j, where i and j refer to the row in which the value is located and the column in which the value is located, respectively.
  • the mask may be defined, at least in part, by a plurality of mask values that define, at least in part, a mask array.
  • a mask array may have a plurality of rows and a plurality of columns, and in at least some
  • the array will have a configuration that matches the configuration of an image to which the array is to be applied, e.g., 128 x 128.
  • (second) image (sometimes referred to herein as a masked image) or other result based at least in part on the (first) image and the mask.
  • Fig. 7 is a representation 700 of a portion of a mask that may be applied to the portion of the image 600 (Fig. 6), in accordance with some embodiments.
  • the portion of the mask array has sixteen values arranged in four rows 702-708 and four columns 712-71 8.
  • the first row includes values 1 , 1 , 1 , 1 .
  • the first column includes values 1 , 0, 0, 0. And so on. Any given value is sometimes referred to herein as mask value,, s , where i and j refer to the row in which the value is associated and the column in which the value is associated, respectively.
  • Fig. 8 is a representation of an application of a mask to an image, in accordance with some embodiments.
  • a mask e.g., the mask 700
  • an image e.g., the image 600
  • a masked image (sometimes referred to herein as a result or output) 800.
  • the masked image 800 will have a configuration that is the same (i.e., same number of rows and same number of columns) as that of the image, e.g., image 600, prior to application of the mask, e.g., mask 700.
  • the masked image 801 has four rows 802-808 and four columns 81 2-81 8, which is the same configuration as that of the image 600. Any given value in the masked image is sometimes referred to herein as masked image value ⁇ , where i and j refer to the row in which the value is located and the column in which the value is located, respectively.
  • the application of the mask to the image comprises pixel by pixel multiplication.
  • the valuei, ij (50) in the masked image is determined as a product (multiplication) of the pixel valuei, ij (50) in the image 600 and mask valuei, ij (1 ) in the mask 700.
  • the val ue2, ij (0) in the masked image is determined as a product (multiplication) of the pixel val ue2, ij (20) in the image 600 and mask val ue2, ij (0) in the mask 700. And so on.
  • regions of the mask that have a value equal to 1 result in regions, within the masked image, where the image is the same as that of the input image (i.e., where the masked image shows the input image).
  • Regions of the mask that have a value equal to 0 result in regions, within the masked image, where the input image is removed (i.e., where the masked image does not show the original image).
  • a mask may have values of 1 and 0.0001 (e.g., or other values that are not 0 but are small relative to the value 1 ), and may be applied to an image using pixel by pixel multiplication followed by thresholding to replace any masked image values below a specified threshold (e.g., a threshold near 0) with the value 0.
  • a specified threshold e.g., a threshold near 0
  • Pixels that are subjugated relative to other pixels are sometimes referred to herein as excluded pixels.
  • Other pixels are sometimes referred to herein as included pixels.
  • a plurality of masks may be applied to an image.
  • the masks may be applied one after the other.
  • one mask may be applied to the image and a second mask may be applied to the result thereof.
  • two or more of the masks may be combined and the combined mask may be applied to the image.
  • Fig. 9 is a representation of one type of BOOLEAN operation that may be used to combine masks, in accordance with some embodiments.
  • values of a first mask may be ANDed with values of a second mask, e.g., a mask 900, to produce a combined mask 901 .
  • the combined mask 901 will have a configuration that is the same (i.e., same number of rows and same number of columns) as that of the first and second masks 700, 900, respectively.
  • the combined masked 901 has four rows 902-908 and four columns 91 2-91 8, which is the same configuration as that of the first and second masks 700, 900.
  • Any given value in the combined mask 901 is sometimes referred to herein as combined mask value,, j, where i and j refer to the row with which the value is associated and the column with which the value is associated, respectively.
  • the combining of the masks comprises value by value ANDing.
  • the valuei, ij (1 ) in the combined mask is determined by ANDing the mask valuei, ij (1 ) in the first mask 700 and mask valuei, ij (1 ) in the second mask 900.
  • the value2, ij (0) in the combined mask is determined by ANDing the mask val ue2, ij (0) in the first mask 700 and mask val ue2, ij (0) in the second mask 900. And so on.
  • the combined mask 901 includes the first mask 700 and the second mask 900.
  • a combined mask may be applied to an image in a similar manner as described above with respect to the first mask 700.
  • regions of a combined mask that have a value equal to 1 result in regions, within a masked image, where the image is the same as that of an input image (i.e., where the masked image shows the input image).
  • Regions of a combined mask that have a value equal to 0 result in regions, within the masked image, where the input image is removed (i.e., where the masked image does not show the original image).
  • the application of the combined mask 901 is in effect application of the first mask 700 and application of the second mask 900.
  • a mask may be a static mask or a dynamic mask.
  • a static mask may be defined before treatment begins, based on user-defined landmarks or otherwise, and is not expected to change during treatment.
  • a dynamic mask is computed or otherwise determined during treatment, and may change during treatment.
  • One type of static mask that may be employed is sometimes referred to herein as a temperature uncertainty (TU) mask that relates to a MRI thermometry method's finite ability to produce a temperature uncertainty map.
  • TU temperature uncertainty
  • a temperature uncertainty mask stores information identifying pixels that exhibit noise in excess of a noise threshold before the start of therapy.
  • a temperature uncertainty mask may be created by determining, for every pixel, a standard deviation of its pixel values across a given or other number of received images, and for each pixel for which the pixel values exceed a standard deviation of 2 °C or other noise threshold, setting or otherwise providing a flag or other indication in the mask to identify the pixel as a noisy pixel.
  • the mask value,,] corresponding to each noisy pixel,, j is set to or otherwise defined as 0, and mask values corresponding to other pixels are set to or otherwise defined as 1 .
  • each pixel identified as noisy will have its pixel values replaced.
  • the pixel value may be replaced with an estimated pixel value.
  • the pixel value may be replaced with an estimated value determined by linear or other interpolation based at least in part on the four neighboring pixels (up, down, left, right) of the pixel.
  • static mask Another type of static mask that may be employed is sometimes referred to herein as a structural mask.
  • static masks may be generated during treatment planning.
  • Fig 10. is a table 1000 that identifies three different types of structural masks, characteristics thereof and representations of examples thereof (reduced in size compared to the size of the visualizations in Fig. 5A-5B), in accordance with at least some embodiments.
  • Figs. 1 1 A-1 1 C are full size representations (compared to the size of the visualizations in Fig. 5A-5B) illustrating the different regions in each of the examples in Fig. 10, in accordance with at least some embodiments.
  • the three different types of structural masks are: (1 ) an ultrasound applicator (UA) (or other therapy applicator) mask 1 100, (2) a prostate (or other target region) mask 1 102, and (3) a rectum (or other restricted region) mask 1 104.
  • UA ultrasound applicator
  • a prostate or other target region
  • a rectum or other restricted region
  • the ultrasound applicator (UA) (or other therapy applicator) mask 1 100 excludes or otherwise subjugates pixels that are within a specified distance of the therapy applicator or portion(s) thereof.
  • the therapy applicator comprises an ultrasound therapy applicator having a center 1 106 and the mask 1 100 excludes or otherwise subjugates pixels in a region 1 108 within 40 mm of the center 1 106 of the ultrasound therapy applicator.
  • this mask 1 100 is slice independent.
  • the prostate (or other target region) mask 1 102 includes pixels within a contour of a prostate (or other target region) or portion(s) thereof and excludes or otherwise subjugates others.
  • the prostate (or other target region) mask 1 102 includes all pixels whose center is fully included in within a contour 1 1 10 of the prostate (or other target region) and excludes or otherwise subjugates others.
  • this mask 1 102 is slice dependent because the contour of the prostate (or target region) may be different in each slice of a dynamic.
  • the rectum (or other restricted region) mask 1 104 excludes or otherwise subjugates pixels within a region having a specified positional relationship to the rectum (or other restricted region) or portion(s) thereof.
  • the rectum (or other restricted region) mask 1 104 excludes pixels that are within a region 1 1 12: (1 ) below the therapy applicator and (2) laterally within 15mm (i.e., +/- 15 mm) of a center 1 106 of the therapy applicator.
  • the above structural masks are based at least in part on the position of the center of the ultrasound applicator (UA) or other therapy applicator. Consequently, if the center of the ultrasound applicator (UA) or other therapy applicator is modified during the treatment (either by the user or because of image shift - discussed below), these structural masks will have to be generated again.
  • a mask may also be a dynamic mask, which may be computed or otherwise determined for every dynamic (or otherwise) during treatment, and may change during treatment.
  • Fig 12. is a table 1200 that identifies three different types of dynamic masks, characteristics thereof and representations of examples thereof (reduced in size compared to the size of the visualizations in Fig. 5A-5B), in accordance with at least some embodiments.
  • Figs. 13A-13C are full size representations (compared to the size of the visualizations in Fig. 5A-5B) illustrating the different regions in each of the examples in Fig. 12, in accordance with at least some embodiments.
  • a sector (or boiling detection) mask 1300 includes pixels within a sector (or other region) or portion(s) thereof receiving energy from the therapy applicator at a current (or other) point in time.
  • the sector (or boiling detection) mask 1300 includes pixels within a polygon 1308 having four sides 1310, 1312, 1314, 1316.
  • the first side 1310 is defined by a prostate (or other target region) boundary 131 8.
  • the second side 1312 is defined by a circle 1320 having a center 1322 at the center 1 106 of the therapy applicator and a radius of 6mm (or other positional relation to the therapy applicator).
  • the third and fourth sides 1314, 1316 are defined by lines that are disposed on opposite sides of a current therapy beam centerline 1324 (e.g., a line at the center of the thermal therapy beam and extending from the therapy applicator 304 in a direction at which the center of the thermal therapy beam is emitted a current point in time) and angularly displaced therefrom by angles 1326, 1328 of +15 degrees and - 15 degrees, respectively, or some other angles.
  • the signal to noise ratio (SNR) mask 1302 and the stability mask 1304 are sometimes referred to herein as noise masks.
  • these masks are used to filter out pixels that did not appear noisy (did not exceed a noise threshold or other criteria for a noisy pixel) prior to the start of the treatment but appear noisy during the treatment.
  • each of these masks is cumulative, meaning that if a pixel is masked at a given dynamic, it will remain masked as such throughout the treatment.
  • the mask used in a given dynamic will be based at least in part on the mask used in the prior dynamic.
  • the stability mask 1304 is used to store information identifying any pixels that are outside the target region and/or other heating volume and exhibit large temperature variations or other noise in excess of a noise threshold after treatment is started.
  • the stability mask 1304 for a given dynamic may be created by determining, for pixels outside the target region or other heating volume, a difference between its temperature in that dynamic and its temperature in a prior dynamic (e.g., temperature of pixel,, j of slicek for dynamic CU rrent - temperature of pixel,, j of slicek for dynamic CU rrent-i) , and for each of such pixels for which the temperature difference exceeds 10 °C (or other difference threshold) or other noise criteria, setting or otherwise providing a flag or other indication in the stability mask to identify the pixel as a noisy pixel.
  • the mask value,, j corresponding to each noisy pixel,, j is set to or otherwise defined as 0, and mask values corresponding to other pixels are set to or otherwise defined as 1 . See for example mask values in a region 1340 corresponding to noisy pixels and set to 0, and mask values in a region 1342 corresponding to other pixels and set to 1 .
  • the pixels outside of the target region or other heating volume will be those pixels that are not included in or are otherwise subjugated in the prostate (or other target region) mask.
  • the stability mask 1304 will be based at least in part on a prostate (or other target region) mask.
  • the stability mask 1304 is cumulative, meaning that if a pixel is masked at a given dynamic, it will remain masked as such throughout the treatment.
  • the stability mask 1304 used in a given dynamic will be based at least in part on the stability mask 1304 used in the prior dynamic.
  • a stability mask 1304 for a given dynamic is made cumulative by determining the stability mask 1304 as described above and multiplying it by the stability mask 1304 used in the prior dynamic.
  • each pixel identified as a noisy pixel will have its pixel values replaced and/or ignored. If it is to be replaced, it may be replaced with an estimated pixel value determined by linear or other interpolation based at least in part on the values of the four neighboring pixels (up, down, left, right) of the pixel.
  • the SNR mask 1302 identifies pixels that have a satisfactory SNR (e.g., an SNR that satisfies an SNR criteria).
  • the SNR mask 1302 is generated by thresholding magnitude images using Otsu's method.
  • the mask value,, j corresponding to a pixel,, j having a satisfactory SNR is set to or otherwise defined as 1 , and mask values corresponding to other pixels are set to or otherwise defined as 0.
  • the SNR mask 1302 is cumulative, meaning that if a pixel is masked as having unsatisfactory SNR at a given dynamic, it will remain masked as such throughout the treatment.
  • the SNR mask 1302 used in a given dynamic will be based at least in part on the SNR mask 1302 used in the prior dynamic.
  • a SNR mask 1302 for a given dynamic is made cumulative by
  • each pixel identified as having unsatisfactory SNR will have its pixel values replaced and/or ignored. If it is to be replaced, it may be replaced with an estimated pixel value determined by linear or other interpolation based at least in part on the values of the four neighboring pixels (up, down, left, right) of the pixel.
  • At least some aspects disclosed herein employ one or more dynamic correction methodologies during thermal treatment or other procedure.
  • Fig 14. is a table 1400 that shows five different types of dynamic corrections that may be employed, characteristics thereof and representations of examples thereof (reduced in size compared to the size of the visualizations in Fig. 5A- 5B), in accordance with at least some embodiments.
  • Drift correction is used to compensate, at least in part, for drift in the Larmor frequency of the MRI scanner, and thereby reduce the effects thereof, at least in part.
  • the Larmor frequency of the MRI scanner may drift over time.
  • the measured phase values which are expected to be constant on unheated regions, may drift over time, which appears as temperature increase (sometimes referred to herein as artificial heating).
  • Fig. 15 is a flowchart of a method for drift correction to compensate, at least in part, for drift in the Larmor frequency of the MRI scanner over time, and thereby reduce the effects thereof, at least in part, in accordance with at least some embodiments.
  • the method includes determining a drift correction mask for each slice (e.g., 12 slices) in a current dynamic.
  • the mask for each slice may be determined by combining the following masks: (i) the thermal (ultrasound or otherwise) applicator mask, (ii) the rectum (or other restricted region) mask, (iii) the stability mask for the slice and (iv) the SNR mask for the slice as follows:
  • the method may further include, for each slice of the current dynamic, applying the combined mask for the slice to the phase difference image for the slice.
  • the combined mask for a slice may be applied to the phase difference image for the slice using pixel by pixel multiplication as follows:
  • the method may further include, for each slice of the current dynamic, determining a geometric fit or other approximation (sometimes referred to herein as an estimation or estimate) based at least in part on the masked phase difference image for the slice.
  • the geometric fit will be a plane fit or a parabola fit, depending on a correction order (sometimes referred to herein as an order of correction) that may be needed and/or chosen, which in at least some embodiment may be based at least in part on the type of scanner being used. For instance, if a second-order correction is to be used, an estimate ⁇ based on
  • W here X is the Vandermonde matrix.
  • the method may further include determining a corrected phase image based at least in part on a difference between the surface and a current phase image. In at least some embodiments, this may be performed by subtracting the surface to the current phase image as follows:
  • Fig. 16A is a full-size visualization 1600 (compared to the size of the visualizations in Fig. 5A-5B) of the example of drift correction shown in Fig. 14, in accordance with at least some embodiments.
  • Figs. 16B is a visualization 1650 that is similar to the visualization 1600 except that: (i) the temperature information in the visualization 1650 has had thresholding applied thereto (as a result, each shade in the visualization 1650 corresponds to a wider temperature range than does each shade in the visualization 1600) and pixels have been inverted (lowest temperatures are shown in white, increasingly higher temperatures are shown in increasingly darker shades, highest temperatures are shown in black) to assist in the teaching herein, reproduction and allow use of reference lines to point to aspects without a need for color, (ii) a border 1660 has been added to identify the portion of the visualization 1650 that represents a surface of the patient's body (e.g., the surface of the patient's abdomen) in the visualization 1650, and (iii) borders have been added around portions of the
  • the visualization 1600 and/or the visualization 1650 may be displayed on a visual output device such as a computer monitor screen or other display.
  • phase unwrap a second type of dynamic correction that may be employed is sometimes referred to herein as phase unwrap. Phase values are bound to a range between - ⁇ (-1 80 degrees) and + ⁇ (+1 80 degrees). As a result, a change in temperature can result in what is sometimes referred to as " phase wrap" .
  • Fig. 17 is a graphical representation 1700 of one type of a phase wrap, in accordance with at least some embodiments.
  • a first phase measurement 1702 has a first phase of -175 degrees representing a first temperature 1704.
  • a second phase measurement 1708 representing a second temperature 1710 (which is relatively close to the first temperature 1704), has a second phase of +175 degrees (which is disproportionately greater than the first phase of -175).
  • the process of determining whether phase unwrap has occurred, and if it has, compensating for such is sometimes referred to herein as " phase unwrap" .
  • the occurrence of phase wrap is detected based at least in part on the change that a pixel phase value has undergone between two successive dynamics.
  • a change of more than ⁇ (in either direction) in a pixel phase value is used as an indication that phase wrap has occurred, and if phase wrap has occurred, it is compensated for by applying an offset of +2 ⁇ or - 2 ⁇ (depending on the direction of the change) in accordance with the following:
  • a third type of dynamic correction that may be employed is sometimes referred to herein as temperature corrections.
  • temperature correction may be carried out as follows. For every pixel in the phase image, if phase unwrap causes the temperature value of the pixel to fall outside the range [0;120] °C (i.e., outside the normal physiological range), or outside some other expected range, the phase is not unwrapped. For the range of [0;120] °C, this may be implemented as follows:
  • O(d) ⁇ ⁇ 0 ⁇ , O(d) O(d) + 2 ⁇
  • O e and ( Do°c are the phase values corresponding to the temperatu 120°C and 0°C respectively.
  • a fourth type of dynamic correction that may be employed is sometimes referred to herein as spatial co-registration (or image shift correction). If the amount of MRI scanner drift is significant over the course of the treatment, it is necessary (or at least desirable) to perform spatial co-registration between the received dynamics and the reference image, taken at the beginning of the treatment.
  • Fig. 1 8 is a representation 1 800 showing a current image 1 802 and a corresponding reference image 1804 prior to any spatial drift, and an alternative current image 1 812 as a result of spatial drift 1814, in accordance with some embodiments.
  • the amount of spatial drift between the current dynamic and the reference image is determined every Y dynamics (or if not periodically, at least from time to time).
  • the amount of spatial drift may be determined by calculating or otherwise determining a measure of similarity between the current dynamic and the reference image, which may be determined by calculating or otherwise determining a cross-correlation between a Fourier-transform of the current dynamic and a Fourier- transform of the reference image.
  • the result of the cross-correlation is an image that contains a peak, the location of which is equal to or otherwise defines the amount of spatial shift between the two images. If the amount of the spatial shift is greater than 0.1 pixel (or other chosen threshold), it is necessary (or at least desirable) to spatially register the current dynamic and the reference image. If the amount of spatial shift is less than 1 pixel, spatially registering the current dynamic and the reference image will require interpolation.
  • Fig. 1 8 shows (a) a compensated reference image 1 824 after compensation 1 826 thereto and a compensated current image 1 822 as a result of the compensation to the reference image, corresponding to the first approach, and (b) a compensated current image 1 832 as a result of compensation 1 836 thereto without any change to the reference image 1 804, corresponding to the second approach, in accordance with some embodiments.
  • Fig. 19 is a full-size visualization 1900 (compared to the size of the visualizations in Fig. 5A-5B) of the example of boiling detection shutoff shown in Fig. 14, in accordance with at least some embodiments.
  • a fifth type of dynamic correction that may be employed is sometimes referred to herein as boiling detection shutoff.
  • it is critical or at least desirable to correctly detect temperature approaching 100°C in tissue.
  • at least some embodiments employ a boiling detection shutoff method and/or mechanism to reduce the risk of tissue boiling.
  • the method and/or mechanism are based at least in part on the sector mask discussed above, which as discussed above, the positioning of which may be primarily (or at least in part) a function of the current beam angle.
  • the method and/or mechanism shut off at least a portion of (or otherwise reduce) the power to the therapy applicator if at any time, any one or more pixels within the sector mask has a temperature that is greater than a threshold or satisfies other criteria.
  • Fig. 19 shows an example of pixels within an example of a sector mask (i.e., an example of pixels within the polygon 1308 (Fig. 13A).
  • the threshold is selected as an indication that a boiling temperature is approached.
  • the threshold is a temperature chosen from a range of from 86 °C to 90 °C. In at least some
  • the threshold is 86 °C. In at least some embodiments, the threshold is adjustable during therapy. In at least some embodiments, the adjustable threshold is adjustable to any temperature in the range of from 86 °C to 90°C. In at least some embodiments, at least a portion the at least one element that is shut off includes one or more elements supplying energy to a region of the patient associated with the one or more pixels that are within the sector mask and have a temperature that is greater than the threshold or satisfies the other criteria.
  • power to the therapy applicator is reduced by shutting off power to one, some or all elements of the therapy applicator that supply energy to a region of the patient associated with the one or more pixels that are within the sector mask and have a temperature that is greater than the threshold or satisfies the other criteria.
  • any one or more of the embodiments (or feature(s) thereof) disclosed herein may be used in association with any other embodiment(s) (or feature(s)) disclosed herein.
  • Fig. 20 is a flowchart of a method 2000 that employs a plurality of the methods disclosed herein or portion(s) thereof and may be employed in delivery of therapy, in accordance with at least some embodiments.
  • one or more portions of the method may be used in performing dynamic correction(s).
  • the dynamic correction(s) may improve accuracy and/or reduce uncertainty.
  • the method may be performed using one or more portions of one or more other methods disclosed herein.
  • any method (or one or more portions thereof) disclosed herein may be performed using one or more portions of one or more other methods disclosed herein.
  • the method (or one or more portion(s) thereof) may be performed in performance of one or more portions of one or more other methods disclosed herein.
  • any method (or one or more portions thereof) disclosed herein may be performed in performance of one or more portions of one or more other methods disclosed herein.
  • the method (or one or more portion(s) thereof) may be performed by system controller 200 (Figs. 1 -2).
  • the method may include receiving data indicative of at least one phase image captured using a magnetic resonance imaging (MRI) device during delivery of thermal therapy by a thermal therapy applicator to a target volume within a patient's body.
  • MRI magnetic resonance imaging
  • the data may have any form(s) and may be received from any source(s) (internal and/or external).
  • the thermal therapy comprises ultrasound thermal therapy and the thermal therapy applicator comprises an ultrasound thermal therapy applicator.
  • the method may further include applying a first mask.
  • the first mask may comprise any mask, or any combination of masks, disclosed below or otherwise herein.
  • the method may further include applying phase unwrap.
  • the method may further include applying a second mask.
  • the second mask may comprise any mask, or any combination of masks, disclosed below or otherwise herein.
  • the first mask and the second mask may be combined with one another into a combined mask that is subsequently applied such that the first mask and second mask are applied at the same time as one another.
  • the first mask, phase unwrap and the second mask may be applied in any suitable order.
  • the applying of the phase unwrap may be between the applying of the first mask and the applying of the second mask.
  • this may comprise applying the first mask to a first phase image to generate a first result image, applying the phase unwrap to the first result image to generate a second result image, and applying the second mask to the second result image to generate a third result image.
  • intermediate processing need not be excluded.
  • the applying of the phase unwrap between the applying of the first mask and the applying of the second mask may comprise: applying the first mask to a phase image to generate a first result image, applying the phase unwrap to a phase image that is based at least in part on the first result image to generate a second result image, and applying the second mask to a phase image that is based at least in part on the second result to generate a third result image.
  • the applying of the phase unwrap may be prior to the applying of the first mask and the applying of the second mask. In at least some embodiments, the applying of the phase unwrap may be after the applying of the first mask and the applying of the second mask. As indicated above, in at least some embodiments, intermediate processing need not be excluded. [00186] The method may further include determining a treatment plan after processing the at least one phase image.
  • the method may further include delivering thermal therapy to the target volume within the patient's body based at least in part on said treatment plan using a thermal therapy applicator.
  • Figs. 21 A-21 D are a flowchart 2100 of another method that employs a plurality of the methods disclosed herein or portion(s) thereof and may be employed in delivery of therapy, in accordance with at least some embodiments.
  • the method reduces the effects of errors and/or potential errors in MRI guided thermal therapy.
  • one or more portions of the method may be used in performing dynamic correction(s).
  • the dynamic correction(s) may improve accuracy and/or reduce uncertainty.
  • one or more portions of any method (or system) disclosed herein may be used without one or more other portions of such method (or system).
  • references below to static masks, dynamic masks, temperature uncertainty masks, structural masks, ultrasound applicator masks, rectum masks, prostate masks, sector masks, noise masks, SNR mask, stability mask, drift correction, phase unwrap, temperature corrections, spatial co-registration (image shift correction), boiling detection and/or boiling detection shutoff (and so on) refer to the static masks, dynamic masks, temperature uncertainty masks, structural masks, ultrasound applicator masks, rectum masks, prostate masks, sector masks, noise masks, SNR mask, stability mask, drift correction, phase unwrap, temperature corrections, spatial co-registration (image shift correction), boiling detection and/or boiling detection shutoff (and so on), respectively, described above with respect to Figs. 1 -20.
  • the method (or one or more portion(s) thereof) may be performed by system controller 200 (Figs. 1 -2).
  • the method may include receiving information associated with a new patient 2102, calculating a pre-treatment TU map 2104, identifying any pixels that are within the prostate (or other region) and have a standard deviation greater than 2 °C (or other threshold or other criteria) 2106, and storing a TU mask generated based at least in part on the results thereof 2108.
  • the method further includes starting treatment 21 10, calculating structural masks (i.e., UA mask, rectum mask and prostate mask and/or other structure mask(s))) 21 12, storing the structural masks 21 14, receiving a new dynamic 21 16 and determining whether more than 5 dynamics have been received 21 18.
  • structural masks i.e., UA mask, rectum mask and prostate mask and/or other structure mask(s)
  • the method returns to 21 16. Otherwise, the method proceeds to calculate a reference phase image 2120, store the reference phase image as a reference phase 2122 and determine whether a current dynamic is a multiple of 100 at 2124.
  • the method proceeds to calculate phase difference between a current phase image and the reference plane 2126. Otherwise, the method stores the next 5 dynamics 2128, evaluate image shift 2130 and determine if the image shift is more than 0.1 pixel 2132.
  • the method returns to 2124. Otherwise, the method proceeds to apply special co- registration 2134, recalculate structural masks 2136, and calculate phase difference between a current phase image and the reference plane 2126.
  • phase unwrap 2138 After calculating the phase difference between a current phase image and the reference plane at 2126, the method proceeds to apply phase unwrap 2138, identify pixels with low magnitude SNR 2140, and storing a SNR mask generated based at least in part on the results thereof 2142.
  • the method further includes identifying pixels whose temperature changed by greater than 10 °C (or other threshold or other criteria) between two dynamics, storing a stability mask generated based at least in part on the results thereof 2146, multiplying current SNR and stability masks with previous SNR and stability masks 2148, applying drift correction to masked phase images (UA & rectum & SNR and stability) 2150, applying phase unwrap 2152, applying temperature correction 2154, converting phase to temperature 2156, calculating sector mask based on current beam angle 2158, and storing a sector mask generated based at least in part on the results thereof 2160.
  • a stability mask generated based at least in part on the results thereof 2146 multiplying current SNR and stability masks with previous SNR and stability masks 2148, applying drift correction to masked phase images (UA & rectum & SNR and stability) 2150, applying phase unwrap 2152, applying temperature correction 2154, converting phase to temperature 2156, calculating sector mask based on current beam angle 2158, and
  • the method further includes determining whether any pixels are within the sector mask and above a threshold indicating that the temperature is approaching a boing temperature (or other temperature reference) 2162. If at 2162 it is determined that no pixels are within the sector mask and above a threshold indicating that the temperature is approaching a boing temperature (or other temperature reference), the method proceeds to apply controller decisions 2164. Otherwise, the method shuts off the element 2166 and then proceeds to apply controller decisions at 2164. Execution may then return to 21 16.
  • inventive concepts may be embodied as a computer readable storage medium (or multiple computer readable storage media) (e.g., a computer memory, one or more floppy discs, compact discs, optical discs, magnetic tapes, flash memories, circuit
  • the computer readable medium or media may be transportable, such that the program or programs stored thereon may be loaded onto one or more different computers or other processors to implement various ones of the aspects described above.
  • computer readable media may be non- transitory media.
  • one or more computer programs that when executed perform methods of the present application need not reside on a single computer or processor, but may be distributed in a modular fashion among a number of different computers or processors to implement various aspects of the present application.
  • Computer-executable instructions may be in many forms, such as program modules, executed by one or more computers or other devices.
  • program modules include routines, programs, objects, components, data structures, etc. that perform particular tasks or implement particular abstract data types.
  • functionality of the program modules may be combined or distributed as desired in various embodiments.
  • a computer may be embodied in any of a number of forms, such as a rack-mounted computer, a desktop computer, a laptop computer, or a tablet computer, as non-limiting examples. Additionally, a computer may be embedded in a device not generally regarded as a computer but with suitable processing capabilities, including a Personal Digital Assistant (PDA), a smart phone or any other suitable portable or fixed electronic device.
  • PDA Personal Digital Assistant
  • Fig. 22 is a block diagram of a computer architecture 2200 according to some embodiments.
  • one or more of the systems (or portion(s) thereof), apparatus (or portion(s) thereof) and/or devices (or portion(s) thereof) disclosed herein may have an architecture that is the same as and/or similar to one or more portions of the architecture 2200.
  • one or more of the methods (or portion(s) thereof) disclosed herein may be performed by a system, apparatus and/or device having an architecture that is the same as or similar to the architecture 2200 (or portion(s) thereof).
  • the architecture may be implemented as a distributed architecture or a non- distributed architecture.
  • the architecture 2200 may include one or more processors 2210 and one or more articles of manufacture that comprise non-transitory computer-readable storage media (e.g., memory 2220 and one or more non-volatile storage media 2230).
  • the processor 2210 may control writing data to and reading data from the memory 2220 and the nonvolatile storage device 2230 in any suitable manner, as the aspects of the disclosure provided herein are not limited in this respect.
  • the storage media may store one or more programs and/or other information for operation of the architecture 2200.
  • the one or more programs include one or more instructions to be executed by the processor 2210 to provide one or more portions of one or more tasks and/or one or more portions of one or more methods disclosed herein.
  • other information includes data for one or more portions of one or more tasks and/or one or more portions of one or more methods disclosed herein.
  • the processor 2210 may execute one or more processor-executable instructions stored in one or more non-transitory computer-readable storage media (e.g., the memory 2220), which may serve as non- transitory computer-readable storage media storing processor-executable instructions for execution by the processor 2210.
  • program or “software” are used herein in a generic sense to refer to any type of computer code or set of computer-executable instructions that may be employed to program a computer or other processor to implement various aspects as described above. Additionally, it should be appreciated that according to one aspect, one or more computer programs that when executed perform methods of the present application need not reside on a single computer or processor, but may be distributed in a modular fashion among a number of different computers or processors to implement various aspects of the present application.
  • Computer-executable instructions may be in many forms, such as program modules, executed by one or more computers or other devices.
  • program modules include routines, programs, objects, components, data structures, etc. that perform particular tasks or implement particular abstract data types.
  • functionality of the program modules may be combined or distributed as desired in various embodiments.
  • data structures may be stored in computer-readable media in any suitable form.
  • data structures may be shown to have fields that are related through location in the data structure. Such relationships may likewise be achieved by assigning storage for the fields with locations in a computer-readable medium that convey relationship between the fields.
  • any suitable mechanism may be used to establish a relationship between information in fields of a data structure, including through the use of pointers, tags or other mechanisms that establish relationship between data elements.
  • the software code may be executed on any suitable processor or collection of processors, whether provided in a single computer or distributed among multiple computers.
  • a computer may be embodied in any of a number of forms, such as a rack-mounted computer, a desktop computer, a laptop computer, or a tablet computer, as non-limiting examples. Additionally, a computer may be embedded in a device not generally regarded as a computer but with suitable processing capabilities, including a Personal Digital Assistant (PDA), a smart phone or any other suitable portable or fixed electronic device.
  • PDA Personal Digital Assistant
  • a computer may have one or more communication devices 2240, which may be used to interconnect the computer to one or more other devices and/or systems, such as, for example, one or more networks in any suitable form, including a local area network or a wide area network, such as an enterprise network, and intelligent network (I N) or the Internet.
  • networks may be based on any suitable technology and may operate according to any suitable protocol and may include wireless networks or wired networks.
  • a computer may have one or more input devices 2250 and/or one or more output devices 2260. These devices can be used, among other things, to present a user interface. -Examples of output devices that may be used to provide a user interface include printers or display screens for visual presentation of output and speakers or other sound generating devices for audible presentation of output.
  • Examples of input devices that may be used for a user interface include keyboards, and pointing devices, such as mice, touch pads, and digitizing tablets.
  • a computer may receive input information through speech recognition or in other audible formats.
  • some aspects may be embodied as one or more methods.
  • the acts performed as part of the method may be ordered in any suitable way. Accordingly, embodiments may be constructed in which acts are performed in an order different than illustrated, which may include performing some acts
  • a computing device is any type of device that includes at least one processor.
  • a processing device is any type of device that includes at least one processor.
  • a processing system is any type of system that includes at least one processor.
  • a mobile (or portable) computing device includes, but is not limited to, any computing device that may be carried in one or two hands and/or worn.
  • a processor may comprise any type of processor.
  • a processor may be programmable or non-programmable, general purpose or special purpose, dedicated or non-dedicated, distributed or non- distributed, shared or not shared, and/or any combination thereof.
  • a processor may include, but is not limited to, hardware, software (e.g., low-level language code, high- level language code, microcode), firmware, and/or any combination thereof.
  • a program may include, but is not limited to, instructions in a high-level language, low-level language, machine language and/or other type of language or combination thereof.
  • a "communication link” may comprise any type(s) of communication link(s), for example, but not limited to, wired links (e.g., conductors, fiber optic cables) or wireless links (e.g., acoustic links, radio links, microwave links, satellite links, infrared links or other electromagnetic links) or any combination thereof, each of which may be public and/or private, dedicated and/or shared.
  • a communication link may employ a protocol or combination of protocols including, for example, but not limited to the Internet Protocol.
  • information may include data and/or any other type of information.
  • terms such as, for example, " in response to” and “ based on “ mean “ in response (directly and/or indirectly) at least to " and “ based (directly and/or indirectly) at least on " , respectively, so as not to preclude
  • references to "A and/or B", when used in conjunction with open-ended language such as “comprising” may refer, in one embodiment, to A only (optionally including elements other than B); in another embodiment, to B only (optionally including elements other than A); in yet another embodiment, to both A and B (optionally including other elements); etc.

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Abstract

Selon un aspect, un procédé de la présente invention consiste à : recevoir des données indicatives d'au moins une image de phase capturée à l'aide d'un dispositif d'imagerie par résonance magnétique (IRM) pendant l'administration d'une thérapie thermique par un applicateur de thérapie thermique à un volume cible à l'intérieur du corps d'un patient ; et traiter ladite au moins une image de phase ; ledit traitement de ladite au moins une image de phase comprenant : l'application d'un premier masque ; l'application d'un non-enroulement de phase ; et l'application d'un second masque.
PCT/IB2017/001506 2017-10-19 2017-10-19 Système de traitement et procédé de correction dynamique pour thérapie thermique WO2019077385A1 (fr)

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CA3075454A CA3075454A1 (fr) 2017-10-19 2017-10-19 Systeme de traitement et procede de correction dynamique pour therapie thermique
JP2020522012A JP2021500126A (ja) 2017-10-19 2017-10-19 熱治療のための処理システムおよびダイナミック補正方法
CN201780095968.9A CN111225609B (zh) 2017-10-19 2017-10-19 用于热疗法的处理系统和动态校正方法
PCT/IB2017/001506 WO2019077385A1 (fr) 2017-10-19 2017-10-19 Système de traitement et procédé de correction dynamique pour thérapie thermique

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2021062532A1 (fr) * 2019-10-01 2021-04-08 Profound Medical Inc. Procédé de filtrage de pixels erronés dans un système de commande de thérapie thermique

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US11457896B2 (en) * 2020-09-23 2022-10-04 GE Precision Healthcare LLC Ultrasound imaging system and method for generating an enhanced image to enhance a shadow region
FR3121345B1 (fr) * 2021-03-31 2024-07-05 Univ Bordeaux Ensemble de traitement thermique

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070230757A1 (en) * 2006-04-04 2007-10-04 John Trachtenberg System and method of guided treatment within malignant prostate tissue
US20120070058A1 (en) * 2009-06-02 2012-03-22 Koninklijke Philips Electronics N.V. Mr imaging guided therapy
US20150258353A1 (en) * 2012-10-12 2015-09-17 Koninklijke Philips N.V. Multi-foci sonications for hyperthermia treatments using magnetic resonance-guided focused ultrasound
US20170059682A1 (en) * 2014-05-08 2017-03-02 The Arizona Board Of Regents Of Behalf Of The University Of Arizona Mri with reconstruction of mr phase image

Family Cites Families (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2889871B1 (ja) * 1998-03-11 1999-05-10 技術研究組合医療福祉機器研究所 磁気共鳴診断装置
JP3998814B2 (ja) * 1998-06-16 2007-10-31 株式会社日立メディコ 磁気共鳴イメージング装置
WO2000063717A1 (fr) * 1999-04-20 2000-10-26 Koninklijke Philips Electronics N.V. Procede de traitement de l'image
JP4251763B2 (ja) * 2000-08-11 2009-04-08 株式会社日立メディコ 磁気共鳴イメージング装置
JP3907944B2 (ja) * 2000-12-28 2007-04-18 株式会社日立メディコ 磁気共鳴イメージング方法及び装置
JP2004290266A (ja) * 2003-03-25 2004-10-21 Olympus Corp 処置装置
JP4192184B2 (ja) * 2006-03-20 2008-12-03 株式会社東芝 超音波治療装置
CN100565498C (zh) * 2008-05-05 2009-12-02 南京大学 基于相位不连续区域检测的最小不连续二维相位展开方法
JP5629101B2 (ja) * 2010-03-09 2014-11-19 株式会社日立メディコ 治療支援装置及び治療支援システム
WO2011115664A2 (fr) * 2010-03-14 2011-09-22 Profound Medical Inc. Moteur compatible irm et système de positionnement
JP2012045198A (ja) * 2010-08-27 2012-03-08 Hitachi Medical Corp 治療支援装置及び治療支援システム
EP2489407A1 (fr) * 2011-02-15 2012-08-22 Koninklijke Philips Electronics N.V. Appareil thérapeutique de réchauffement d'un sujet
CN103327891B (zh) * 2011-01-17 2016-08-17 株式会社日立制作所 磁共振成像装置及流体增强图像取得法
US9102776B1 (en) * 2012-03-05 2015-08-11 Flir Systems, Inc. Detection and mitigation of burn-in for thermal imaging systems
EP2642310A1 (fr) * 2012-03-22 2013-09-25 Koninklijke Philips N.V. Estimations de dose thermique tridimensionnelles interpolées à l'aide de l'imagerie par résonance magnétique
DE102012205222B4 (de) * 2012-03-30 2020-08-13 Siemens Healthcare Gmbh Verfahren zur Ermittlung eines artefaktreduzierten dreidimensionalen Bilddatensatzes und Röntgeneinrichtung
US9750466B2 (en) * 2014-04-29 2017-09-05 Koninklijke Philips N.V. Device and method for tomosynthesis imaging
DE102014210778B4 (de) * 2014-06-05 2016-01-14 Siemens Aktiengesellschaft Erzeugung einer Parameterkarte in der Magnetresonanztechnik

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070230757A1 (en) * 2006-04-04 2007-10-04 John Trachtenberg System and method of guided treatment within malignant prostate tissue
US20120070058A1 (en) * 2009-06-02 2012-03-22 Koninklijke Philips Electronics N.V. Mr imaging guided therapy
US20150258353A1 (en) * 2012-10-12 2015-09-17 Koninklijke Philips N.V. Multi-foci sonications for hyperthermia treatments using magnetic resonance-guided focused ultrasound
US20170059682A1 (en) * 2014-05-08 2017-03-02 The Arizona Board Of Regents Of Behalf Of The University Of Arizona Mri with reconstruction of mr phase image

Non-Patent Citations (3)

* Cited by examiner, † Cited by third party
Title
AGNELLO, L ET AL.: "Smart Techniques for Fast Medical Image Analysis and Processing", DOCTORAL THESIS, UNIVERSITY OF PALERMO, 31 December 2015 (2015-12-31), XP055597614 *
RIEKE, V ET AL.: "MR Thermometry", JMRI, vol. 27, no. 2, 24 January 2008 (2008-01-24), pages 376 - 390, XP002604875, DOI: doi:10.1002/JMRI.21265 *
ROUJOL, S ET AL.: "Real-time MR-thermometry and dosimetry for interventional guidance on abdominal organs", MAGNETIC RESONANCE IN MEDICINE, vol. 63, no. 4, 29 March 2010 (2010-03-29), XP055015969 *

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2021062532A1 (fr) * 2019-10-01 2021-04-08 Profound Medical Inc. Procédé de filtrage de pixels erronés dans un système de commande de thérapie thermique
US11442128B2 (en) 2019-10-01 2022-09-13 Profound Medical Inc. Method for filtering erroneous pixels in a thermal therapy control system

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