Explore all your imported and calculated items in My Work.

My Work:

Open MY WORK in the menu. Alternatively, click on the Radiochromic.com logo to open My Work.

List of items:

Select a list of items according to study type, study, and category.

Archive / Restore a study:

Archive studies by clicking on and restore them by clicking on . Archived studies are only accessible in My Work. Check the checkbox to see them.

Edit a study:

Rename a study by clicking on .

Delete a study:

Click on Delete to remove a study permanently.

Delete an item:

On an item, click on Delete to remove an item permanently.

Edit an item:

On an item, click on Edit to modify Study, Item, or Comment.

Open an Item:

On an item, click on Edit to examine it. Series will open in Image / Analysis, while other items will open in My Item.

In My Item:

Open the item in Analysis, Download it, print a Report, or ask for Support on this specific item.

To import images into Radiochromic.com, a subscription is required. For more information, please contact us.

Radiochromic.com does not record or use patient data. Do not enter patient data to identify items or studies.

Import film scans to Radiochromic.com.

Step 1:

Open IMPORT in the menu.

Step 2:

Click on Film.

Step 3:

Select an existing Study or create a new one.

Step 4:

Name the Item.

Step 5 (optional):

Introduce film statistics. Statistics assist you in describing your films. Furthermore, they are processed to improve the accuracy of your results.

Step 6 (optional):

Include comments if desired.

Step 7:

Upload one or several repeated film scans taken after irradiation. Up to five images can be imported, with a maximum of 20MB or 3M pixels for each image.

Step 8 (optional):

Upload one or several repeated film scans taken before irradiation. Scans taken before and after irradiation should be registered, meaning they should have the same scanning area and dimensions. Up to five images can be imported, with a maximum of 20MB or 3M pixels for each image.

Step 9:

Select film orientation. This is CRITICAL if lateral corrections are applied. Click on the arrows ( or ) to select the direction of movement of the scanner lamp on the film scans.

Step 10:

Click on Upload. The average film scans will be calculated and uploaded. They will be saved in My Work.

Import dose planes or image maps (e.g., EPID images) to Radiochromic.com.

Step 1:

Open IMPORT in the menu.

Step 2:

Click on Image 2D.

Step 3:

Select an existing Study or create a new one.

Step 4:

Name the Item.

Step 5:

Choose the format of your image file. Currently supported image formats are:

• DICOM-RT dose 3D slice
• DICOM-RT dose 2D
• DICOM-RT image
• TIFF single channel
• Comma Separated Values
• XiO and Monaco (Elekta)
• iPlan (Brainlab)
• ADAC Pinnacle (Philips)
• OmniPro I'mRT (IBA) .opg file

If you need to import an unsupported image format, please contact user support.

Step 6 (DICOM-RT dose 3D slice only):

If you select DICOM-RT dose 3D slice, you must specify a plane in the 3D dose matrix. Provide the DICOM coordinates of the plane, including the axis and position.

Step 7 (optional):

Include comments if desired.

Step 8:

Add the image file. Images can be up to 20MB or 3M pixels, except for DICOM-RT dose 3D matrices, which can be up to 100MB. Only square pixels are currently supported.

Step 9:

Click on Upload. The image will be uploaded and saved in My Work. Files are anonymized upon uploading.

Import dose distributions in CSV format

Import dose distributions in comma-separated values format. Doses should be in Gy and positions in mm. Follow the format of the example below:

Comma-separated values format

Import several DICOM files together to Radiochromic.com.

Step 1:

Open IMPORT in the menu.

Step 2:

Click on Series.

Step 3:

Select an existing Study or create a new one.

Step 4:

Name the Item.

Step 5 (optional):

Include comments if desired.

Step 6:

Add the image files. Up to 400 images can be imported, with a maximum of 5MB for each image.

Step 7:

Click on Upload. The image will be uploaded and saved in My Work. Files are anonymized upon uploading.

Many different protocols for radiochromic film dosimetry can be applied with Radiochromic.com. Here, we present our recommended protocol for accurate radiochromic film dosimetry. This protocol is based on:

Méndez, I., et al. "A protocol for accurate radiochromic film dosimetry using Radiochromic.com." Radiology and Oncology 55.3 (2021): 369-378.

The dosimetry system for radiochromic film dosimetry consists of:

• Gafchromic radiotherapy/radiology films
• a flatbed scanner
Our first option in terms of accuracy would be the Epson Expression 10000-12000XL, followed by the Epson Perfection V700-850 models, all of which have been extensively studied in the literature.
• scanner software
• Radiochromic.com

The recommended accessories are:

• gloves
• a guillotine
• a frame to center the film on the scanner
• a transparent compression (glass) sheet, when scanning in transmission mode
Technical drafts for frames and compression sheets for the Epson Expression 10000-12000XL and Epson Perfection V700-850 scanners can be found here.

The dosimetry system

A calibration is necessary to convert the response of the dosimetry system into a dose distribution.

Convert film pixel values into doses.

Step 1:

Calibrate the film lot.

Step 2:

Irradiate, scan and upload the film.

Step 3:

Open FILM in the menu.

Step 4:

Click on Dosimetry.

Step 5:

Select an existing Study or create a new one.

Step 6:

Name the Item.

Dosimetry: input

Step 7:

Select study and item of the film that you imported for dosimetry.

Step 8:

Select study and item of the calibration.

Step 9:

Select Noise reduction filter. Noise reduction applies a square median filter to the dose distribution to reduce the noise (a 3 × 3 filter is recommended).

Step 10:

Click on Response correction.

Dosimetry: response correction

Step 11 (optional):

Inter-scan correction (optional):

Select an unexposed ROI in order to correct inter-scan variations. Use the central part of the scan to avoid the lateral artifact. The unexposed film fragment from the calibration can be used to correct inter-scan variations. To do so, you may keep this fragment in the same position when scanning every film until a new calibration is made.

Dose rescaling (optional):

Rescale doses in order to match the film dose with the known dose of a ROI. To apply dose rescaling, before the irradiation, cut a strip from the film to measure. This strip should be irradiated with a known homogeneous dose and scanned together with the rest of the film. Finally, select a ROI of the exposed strip centered on the scan and introduce its dose.

In Radiochromic.com, the re-calibration correction is optional and composed of inter-scan correction and dose rescaling.

Step 12:

Click on Request dosimetry. The dosimetry will be calculated and saved in My Work.

Dosimetry: result

Analyze imported and calculated images.

Step 1:

Open IMAGE in the menu.

Step 2:

Click on Analysis.

Step 3 (Image selection):

Select one or two images or one series for display. Alternatively, you can open an Item for Image Analysis from My Work.

Step 4 (Display):

Manipulate and analyze your images, export them as DICOM-RT dose/image, export profiles, etc.

Image handlers:

Manipulate Image A, B, and Image Calculator. Image Calculator offers the possibility to calculate the image which is the difference (i.e., \(A - B\)), relative difference (i.e., \(100 \frac{A - B}{B}\)), or addition (i.e., \(A + B\)) of images A and B.

Image analysis: image handler

Image index:

Select an image in a Series

LUT:

Choose between different color lookup tables.

Pixel units:

Pixel values can be indicated using units, such as Gy or cGy.

Alpha:

Select the level of transparency/opacity of the image.

Transform:

Apply affine transformations on the image. The order of transformations is: first Flip, then Rotation, and finally Translation. Math will multiply each pixel in Image A by the first parameter and add the second parameter. Rotate in 90º steps by clicking on . Calculate the complement image by clicking on .

Export:

Export the image as DICOM-RT dose/image. If a ROI is selected, only the ROI is exported.

Range and Histogram:

Select the range of values of interest. Examine the distribution of values with the histogram and the statistical analysis. If a ROI is selected, only the points inside the ROI are included in the analysis.

Display buttons:

Customize the display.

Image analysis: display buttons

ROI:

Select Region of Interest with the left mouse button or by clicking the ROI button .

Zoom:

Zoom/unzoom using the right mouse button or the zoom buttons: .

Isodoses/isolines:

Show isodoses/isolines on the images with the Isodoses button .

Grid:

Show a grid on the canvas with the Grid button .

Information:

Show image file names with the Information button .

Sync Image B range to Image A range:

Sync Image B range to Image A range with the Sync button .

Canvas:

Visualize and analyze the image.

Image analysis: canvas

Drag:

Use the middle mouse button to drag the Image A.

Cursor:

Read pixel values under the cursor. Lock the cursor by clicking on .

Profiles:

Vertical and horizontal profiles for both images are shown. Image A is in red, Image B is in green, and Image calculator is in blue. To export a profile, lock the cursor, select the Profile export step on the Image handler, and click on the Export button to export it in CSV format.

Average profiles:

Select a ROI and click on the Average button to obtain the average profile. Click on the Export button to export it in CSV format.

Control area:

Visualize pixel coordinates and pixel values in the control area. You can also move the cursor to a specific position by entering the coordinates in the control area.

Register two images automatically.

Step 1:

Open IMAGE in the menu.

Step 2:

Click on Registration.

Step 3 (Image selection):

Select two images for display.

Step 4:

Pre-register both images by flipping, translating, and rotating Image A.

Step 5 (Inputs):

Enter the inputs for the calculation:

Apply Relative dosimetry:

The registration translates and rotates Image A. By applying Relative dosimetry, it will also change the Math factor that multiplies A pixel values.

ROI (optional):

Select the region that will be included in the registration with a ROI. Otherwise, the registration will use all the pixels on both images.

Step 6:

Click on Calculate. After a few seconds, the registration will apply an affine transformation to Image A to register both images.

Troubleshooting 1:

If the images are too far apart from each other, or the rotation between them is too large, the registration will fail. Pre-register both images beforehand.

Troubleshooting 2:

The rotation may fail if one image has perfect circular symmetry.

Troubleshooting 3:

The registration expects similar dose distributions (in absolute or relative values). Registering images with similar shapes but completely different pixel values may lead to failure.

Compare dose distributions by evaluating the 2D γ-index.

Step 1:

Open IMAGE in the menu.

Step 2:

Click on Gamma.

Step 3:

Select the evaluation (Image A) and reference (Image B) dose distributions.

Step 4:

Pre-register both images by flipping, translating, and rotating Image A.

Step 5:

If necessary, scale or increment the doses of Image A by a fixed value with Transform / Math. For example, if you are using a dose plane calculated by the TPS, you can input the daily output of the linac as dose scaling factor. If you are using a dose plane measured with a 2D dosimeter, you can introduce the necessary dose scaling factor to correct for the distance between the film plane and the dosimeter's measurement plane.

Step 6 (Inputs):

Enter the inputs for the calculation:

Gamma: input

Study:

Select an existing Study or create a new one.

Item:

Name the Item.

Normalization:

Choose between global and local gamma normalization. Global gamma can be normalized at Dmax or at a specified Dnorm.

Tolerance Dose:

Select dose tolerance as a percentage of Dmax or Dnorm (for global normalization) or of the local dose (for local normalization).

Tolerance Distance:

Insert the distance tolerance in mm.

Threshold:

Specify the threshold dose. Points with doses lower than the threshold dose are excluded. The threshold dose is a percentage of Dmax or Dnorm.

Tolerance Distribution:

Select the distribution from which global gamma dose tolerances and the threshold dose are calculated. You can use either the reference or the evaluation dose distribution.

Fine registration:

If selected, the automatic fine registration will improve your manual registration.

Relative dosimetry:

If selected, the application will consider that the images contain relative doses. To optimize the γ-index results, doses in Image A will be scaled.

Maximum gamma:

The maximum gamma value restricts the search space around each reference point. (Default: 2.0)

ROI (optional):

The edges of the reference dose distribution have misleadingly high γ-index values. They are excluded by default with the automatic ROI. Alternatively, you can manually select a different ROI.

Comments (optional):

Include comments if desired.

Step 7:

Click Calculate. The gamma calculation is in progress. The result will be saved in My Work.

Step 8:

You can adjust Gamma inputs to initiate several Gamma Index calculations in parallel. For example, you can modify tolerances, apply relative dosimetry, and more, then click Calculate again.

In My Work:

Click on the Retry button to re-evaluate Gamma Index comparisons.

Fast Gamma

References:

• Low, D. A., et al. "A technique for the quantitative evaluation of dose distributions." Medical physics 25.5 (1998): 656-661.

Locate and obtain the dimensions of the radiation isocenter by analyzing a Starshot test.

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on Starshot.

Step 3:

Select an image of a Starshot test.

Step 4:

The axes of the star should have lower values than the background. If this is not the case, click on the Complement button to calculate the complementary image.

Starshot: complement

Step 5 (Inputs):

Enter the inputs for the calculation:

Starshot: input

Fiducial:

Lock the cursor and align it with the fiducial/laser isocenter if marked on the image. Otherwise, lock the cursor in a position close to the center of the star.

ROI (optional):

Prevent labels and other artifacts from interfering in the calculation by selecting a ROI.

Comments (optional):

Include comments if desired.

Step 6 (Outputs):

Click on Calculate. The results will show after a few seconds:

Starshot: output

Detected beams:

Number of detected beams.

Isocenter coordinates:

Position of the radiation isocenter.

Isocenter radius:

Radius of the radiation isocenter.

Distance fiducial-isocenter:

Distance between fiducial and radiation isocenter.

Starshot: result

Step 7:

Click on Report to get the results in a PDF file.

Troubleshooting 1:

The axes of the star have higher values than the background. Click on the Complement button to calculate the complementary image.

Starshot: error

Troubleshooting 2:

The cursor is far from the center of the star. Lock the cursor in a position closer to the isocenter.

Troubleshooting 3:

Excessive noise, large beam widths, beams too close to each other, image artifacts, etc., can induce errors in the location of the beams.

References:

• Depuydt, T., et al. "Computer-aided analysis of star shot films for high-accuracy radiation therapy treatment units." Physics in Medicine & Biology 57.10 (2012): 2997
• Gonzalez, A., et al. "A procedure to determine the radiation isocenter size in a linear accelerator." Medical physics 31.6 (2004): 1489-1493

Check the accuracy of MLC positions with the Picket Fence test.

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on Picket Fence.

Step 3:

Select an image of a Picket Fence test.

Step 4:

The beam lines should be horizontal and have higher values than the background. If this is not the case, transform the image by rotating it and/or calculating the complementary image.

Picket Fence: prepare the image

Step 5 (Inputs):

Enter the inputs for the calculation:

Picket Fence: input

MLC:

Select the MLC model.

Auto-correct Translation:

Automatically correct any small offset of the isocenter position on the x-axis.

Auto-correct Rotation:

Automatically correct any small rotation of the beam lines.

Isocenter:

Introduce the position of the isocenter on the X-axis either manually or by locking the cursor near the center of the MLC on the X-axis. Use this field to introduce EPID offsets with respect to the isocenter.

Distance scaling:

Introduce distance scaling (i.e., Source to Imager Distance / Source to Axis Distance).

Tolerance:

Tolerance for errors of leaf positions.

Leaf end threshold:

By default, the leaf end is located at the position of the 50% isodose between the peak of the signal and the background (i.e., the FWHM), which is appropriate when working with doses. You can change the threshold level to locate the leaf end more accurately when pixel values do not correspond to doses (e.g., with EPIDs).

ROI (optional):

Delineate the ROI (i.e., the MLC region).

Comments (optional):

Include comments if desired.

Step 6 (Outputs):

Click on Calculate. The results will show after a few seconds:

Picket Fence: output

Passing rate:

Percentage of leaf positions within tolerance.

Mean absolute error:

Mean absolute leaf position error.

Maximum absolute error:

Maximum absolute leaf position error.

Picket Fence: result

Step 7:

Click on Report to get the results in a PDF file.

Troubleshooting 1:

The beam lines are vertical. Transform the image by rotating it.

Troubleshooting 2:

The beam lines have lower values than the background. Click on the Complement button to calculate the complementary image.

Troubleshooting 3:

In the report, the Aperture is not accurate. When pixel values do not correspond to doses (e.g., with EPIDs), you may need to adjust the Leaf End Threshold Level to more accurately locate the leaf end.

The accuracy of the results depends on the image resolution and the signal-to-noise ratio. Better resolution and less noise produce more accurate results.

References:

• LoSasso, T. "IMRT delivery system QA." Intensity modulated radiation therapy: the state of the art. Madison, WI: Medical Physics Publishing (2003): 561-91

Evaluate the impact of gravity on the MLC by measuring the output at multiple gantry angles.

This test corresponds to Varian RapidArc QA Test 0.1: DMLC Dosimetry ("RapidArc QA Test Procedures for TrueBeam." Varian Medical Systems, Inc. (2014)).

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on MLC Dosimetry.

Step 3:

Select a Series with a MLC Dosimetry test.

Step 4 (Inputs):

Enter the inputs for the calculation if they are not automatically populated from the DICOM file or if they are incorrect. Uncheck the images that you want to exclude from the calculation. The inputs include:

MLC Dosimetry: input

Gantry angle:

Introduce the gantry angle for each image.

ROI:

Select the ROI inside the field where the output will be measured.

Comments (optional):

Include comments if desired.

Step 5 (Outputs):

Click on Calculate. The results will show after a few seconds:

MLC Dosimetry: output

Summary:

Mean and maximum absolute percentage deviation.

Image N: ROI. Deviation:

Percentage deviation between the mean of the image and the mean of the means of all images.

Image N: ROI. Mean, median, maximum, minimum, and standard deviation:

Mean, median, maximum, minimum, and standard deviation of the pixel values inside the ROI of Image N.

Step 6:

Click on Report to get the results in a PDF, CSV, or JSON file.

References:

• "RapidArc QA Test Procedures for TrueBeam." Varian Medical Systems, Inc. (2014)

Analyze the control accuracy of dose rate, gantry speed, and leaf speed during RapidArc delivery.

This test corresponds to Varian RapidArc QA Tests 2 and 3 ("RapidArc QA Test Procedures for TrueBeam." Varian Medical Systems, Inc. (2014)).

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on MLC RapidArc.

Step 3:

Select a Series with a MLC RapidArc test.

Step 4 (Inputs):

Enter the inputs for the calculation:

MLC RapidArc: input

Image MLC:

Select the image with a field delivered using the MLC.

Image OPEN:

Select the image with an open field.

ROI configuration:

Select predefined ROI settings or customize your own.

MLC first ROI:

Select the first ROI on the left where the output will be measured.

Number of ROIs:

Select the number of ROIs to measure.

Space between ROIs:

Select the distance between two consecutive ROIs.

Comments (optional):

Include comments if desired.

Step 5 (Outputs):

Click on Calculate. The results will show after a few seconds:

MLC RapidArc: output

Summary:

Mean and maximum absolute percentage deviation.

ROI N. Deviation:

Percentage deviation between the normalized mean of the ROI and the mean of the normalized means of all ROIs.

ROI N. Normalized mean:

Normalized mean (N) defined as:

$$N = 100 \frac{MLC_{mean}}{OPEN_{mean}}$$

ROI N. Image MLC:

Mean, standard deviation, maximum, and minimum of the pixel values inside the ROI N of the Image MLC.

ROI N. Image OPEN:

Mean, standard deviation, maximum, and minimum of the pixel values inside the ROI N of the Image OPEN.

Step 6:

Click on Report to get the results in a PDF, CSV, or JSON file.

References:

• "RapidArc QA Test Procedures for TrueBeam." Varian Medical Systems, Inc. (2014)

Verify the coincidence of light and radiation field.

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on Light and radiation field coincidence.

Step 3:

Select an image of a Light and radiation field coincidence test.

Step 4 (Inputs):

Enter the inputs for the calculation:

Light-radiation: input

Field definition:

Select between Inflection points and FWHM. The FWHM follows the standard definition of radiation field as delimited by the 50% isodose of the beam profile. However, this definition requires that films are converted into dose distributions. When working with pixel values, an approximation to the radiation field can be obtained by the inflection points of the profiles.

Nominal field size:

Introduce the nominal dimensions of the field on each semiaxis.

System of coordinates for QA tests

Light points:

Introduce the points that mark the limits of the light field on each semiaxis. Enable them in Inputs and place them on the canvas. Light points shall correspond to the correct semiaxis and be located on the crosshair.

ROI:

Select a ROI that encompasses the radiation field.

Comments (optional):

Include comments if desired.

Light-radiation: canvas

Step 5 (Outputs):

Click on Calculate. The results will show after a few seconds:

Light-radiation: output

Light-radiation angle:

Rotation between light and radiation field.

Light-radiation displacement:

Distance between radiation and light field. It is positive/negative when the radiation field is larger/smaller than the light field.

Crosshair-light distance:

Light field dimensions on each semiaxis.

CAX coordinates (symmetric nominal field sizes only):

For symmetric nominal field sizes only: central axis coordinates of the radiation field.

Light-radiation: result

Step 6:

Click on Report to get the results in a PDF file.

Troubleshooting 1:

The light points shall correspond to the correct semiaxis and be located on the crosshair.

Troubleshooting 2:

The ROI shall encompass the radiation field, not extend beyond the image, and avoid labels and other artifacts.

Troubleshooting 3:

There shall not be any mark on the radiation field apart from the 4 light points. Do not mark the center or the corners of the field.

Analysis of the radiation field, including field size, central dose statistics, flatness, symmetry, penumbra, etc. It can analyze rectangular and circular fields (e.g., cones) of WFF photons, FFF photons, and electron beams.

It is the QA test of choice for also measuring small fields and output factors.

Available protocols for flatness and symmetry:

Photons WFF:

• WFF IEC / Elekta:   "IEC 60976. Medical electrical equipment - Medical electron accelerators - Functional performance characteristics." IEC (2007).
• WFF TG45 / Varian:   Nath, R., et al. "AAPM code of practice for radiotherapy accelerators: report of AAPM Radiation Therapy Task Group No. 45." Medical Physics 21 (1994): 1093.

Photons FFF:

• FFF Elekta:   "Versa HD Product Data." Elekta AB.
• FFF Varian:   "TrueBeam System Specifications." Varian Medical Systems, Inc. (2011)
• FFF AERB of India:   Sahani, G., et al. "Acceptance criteria for flattening filter-free photon beam from standard medical electron linear accelerator: AERB task group recommendations." Journal of Medical Physics/Association of Medical Physicists of India 39.4 (2014): 206.

Electrons:

• Electrons IEC / Elekta:   "IEC 60976. Medical electrical equipment - Medical electron accelerators - Functional performance characteristics." IEC (2007).
• Electrons TG45 / Varian:   Nath, R., et al. "AAPM code of practice for radiotherapy accelerators: report of AAPM Radiation Therapy Task Group No. 45." Medical Physics 21 (1994): 1093.

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on Radiation field.

Step 3:

Select an image with a dose distribution of a rectangular or circular radiation field.

Step 4 (Inputs):

Enter the inputs for the calculation:

Radiation field: input

Protocol for flatness and symmetry:

If you want to calculate flatness and symmetry, select one of the available protocols.

Field geometry:

Select between rectangular and circular field.

Nominal field size:

Nominal field size dimensions.

Field definition isodose:

Isodose that delimits the radiation field.

Central dose diameter:

Central dose statistics are measured for a circle with this diameter centered on the field.

Averaging area:

Side of the area that averages pixel values for flatness and symmetry calculations.

Field rotation:

Measure the rotation of the radiation field. Do not apply rotations on fields with circular symmetry (e.g., cones and very small fields).

Volume averaging correction:

Calculate the volume averaging correction (kvol) that should multiply the measured central dose to take into account the dimensions of the central dose diameter. Calculated following the procedure of:

Casar, B., et al. "A novel method for the determination of field output factors and output correction factors for small static fields for six diodes and a microdiamond detector in megavoltage photon beams." Medical physics 46.2 (2019): 944-963.

Diagonal normalized flatness (optional):

Introduce the distance to the center to calculate the diagonal normalized flatness, as defined in:

Gao, S., et al. "Measurement of changes in linear accelerator photon energy through flatness variation using an ion chamber array" Medical physics 40.4 (2013): 042101.

Crosshair coordinates (optional):

Lock the cursor and align it with the crosshair if the crosshair is marked on the image.

ROI (optional/mandatory):

Select a ROI that encompasses the radiation field. This input is mandatory when applying the FFF AERB protocol.

Comments (optional):

Include comments if desired.

Step 5 (Outputs):

Click on Calculate. The results will show after a few seconds:

Radiation field: output

Radiation field center:

Coordinates of the center of the radiation field.

Radiation field size:

Dimensions of the radiation field.

Field rotation:

Rotation of the radiation field.

Central dose statistics:

Statistics of the distribution of values within the central dose diameter.

CAX distance to crosshair:

If the crosshair is introduced: distance between the crosshair and the central axis.

Crosshair-field distance:

If the crosshair is introduced: distance between the crosshair and the field on each semiaxis.

Penumbras:

For rectangular fields except for FFF Elekta and FFF Varian: distance between the 80-20% isodoses on each semiaxis.

Flatness and Symmetry:

According to the different protocols, the outputs for flatness and symmetry are:

• Photons WFF IEC / Elekta:   flatness, symmetry, and maximum ratio of absorbed dose.
• Photons WFF TG45 / Varian:   flatness and symmetry, in both cases on the X and Y axes and both diagonals.
• Photons FFF Elekta:   symmetry and isodose values on each semiaxis at different distances from the CAX.
• Photons FFF Varian:   flatness, symmetry, isodose values on each semiaxis at different distances from the CAX, distances from the CAX to different isodoses on each semiaxis.
• Photons FFF AERB of India:   symmetry and distances from the CAX to different isodoses on each semiaxis.
• Electrons IEC / Elekta:   flatness (i.e., distance between the 90% isodose and the edge on each semiaxis and the diagonals), symmetry, and maximum ratio of absorbed dose
• Electrons WFF TG45 / Varian:   flatness and symmetry, in both cases on the X and Y axes and both diagonals.

Volume averaging correction:

Volume averaging correction factor (kvol), if selected.

Diagonal normalized flatness:

Diagonal normalized flatness (F_DN), if the distance to the center is specified.

Radiation field: result

Step 6:

Click on Report to get the results in a PDF, CSV, or JSON file.

Troubleshooting 1:

The image must contain a dose distribution. If the image is a film scan, pixel values should be converted into doses.

Troubleshooting 2:

Rotation recognition may fail if the field has circular symmetry.

Troubleshooting 3:

The sample of central dose pixels may be empty if the central dose diameter is too small. As a consequence, the program will return an error.

Troubleshooting 4:

If introduced, the crosshair coordinates should be within the ROI.

References:

• "IEC 60976. Medical electrical equipment - Medical electron accelerators - Functional performance characteristics." IEC (2007).
• Nath, R., et al. "AAPM code of practice for radiotherapy accelerators: report of AAPM Radiation Therapy Task Group No. 45." Medical Physics 21 (1994): 1093.
• Sahani, G., et al. "Acceptance criteria for flattening filter-free photon beam from standard medical electron linear accelerator: AERB task group recommendations." Journal of Medical Physics/Association of Medical Physicists of India 39.4 (2014): 206.
• Casar, B., et al. "A novel method for the determination of field output factors and output correction factors for small static fields for six diodes and a microdiamond detector in megavoltage photon beams." Medical physics 46.2 (2019): 944-963.
• Gao, S., et al. "Measurement of changes in linear accelerator photon energy through flatness variation using an ion chamber array" Medical physics 40.4 (2013): 042101.

Verify the coincidence of the mechanical and radiation isocenters.

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on Winston-Lutz.

Step 3:

Select a series with a Winston-Lutz test. Up to 90 images can be analized.

Step 4 (Inputs):

Enter the inputs for the calculation if they are not automatically populated from the DICOM file or if they are incorrect. The DICOM tags follow the IEC 61217 coordinate system. If necessary, input angles according to this coordinate system. Uncheck the images that you want to exclude from the calculation. The inputs include:

Winston-Lutz: input

SID/SAD:

Source to Imager Distance / Source to Axis Distance for each image.

Couch angle:

Introduce the couch angle for each image.

Collimator angle:

Introduce the collimator angle for each image.

Gantry angle:

Introduce the gantry angle for each image.

ROI (optional):

Crop your image using a ROI to facilitate the detection of the radiation field when it covers less than 1% of the image.

Comments (optional):

Include comments if desired.

IEC 61217 coordinate system

Step 5 (Outputs):

Click on Calculate. The results will show after a few seconds:

Winston-Lutz: output

BB phantom displacement:

Couch shift needed to align the BB phantom with the radiation isocenter. The displacement is expressed in IEC 61217 coordinates. The magnitude of the displacement (i.e., the distance between the mechanical and radiation isocenters) is also provided.

Image offsets:

Offset at SID of each image between the radiation and mechanical isocenters.

Step 6:

Click on Report to get the results in a PDF, CSV, or JSON file.

Troubleshooting 1:

Crop your image using a ROI to facilitate the detection of the radiation field when it covers less than 1% of the image.

References:

• Low, D. A., et al. "Minimization of target positioning error in accelerator‐based radiosurgery." Medical physics 22.4 (1995): 443-448.

Measure CT and CBCT image quality with automatic Catphan phantom analysis. This test is compatible with Catphan models 500, 503, 504, 600, and 604.

Step 1:

Open MACHINE QA in the menu.

Step 2:

Click on Catphan.

Step 3:

Select a series with a CT or CBCT scan of a Catphan phantom.

Step 4:

Enter the inputs for the calculation:

Catphan: input

Phantom:

Select the model of the phantom under analysis.

Image contrast:

Choose between different definitions of contrast:

• HU difference: $$C = HU_{ROI} - HU_{background}$$
• Weber: $$C = \frac{HU_{ROI} - HU_{background}}{HU_{background}}$$
• Michelson: $$C = \frac{HU_{ROI} - HU_{background}}{HU_{ROI} + HU_{background}}$$

High resolution (optional):

Optionally, enter the maximum number of line pairs per centimeter that you can discern.

Low contrast - measured (optional):

The application automatically analyzes the low contrast module. However, you can also input the dimensions of the targets that you can distinguish across different noise levels.

Comments (optional):

Include comments if desired.

Step 5 (Outputs):

Click on Calculate. The results will show after a few seconds:

Catphan: output

Origin of phantom:

DICOM coordinates of the center of the sensitometry module.

Phantom orientation:

Rotations of the phantom in each axis.

Pixel spacing:

Pixel dimensions according to the DICOM files and those calculated by the application (Experimental).

Slice thickness:

Slice thickness according to the DICOM files and those calculated by the application (Experimental).

Uniformity:

Mean and standard deviation of the Hounsfield Units (HUs) measured in the center of the phantom and in four off-center positions along each semiaxis. The diameter of the ROIs is 10% of the phantom's diameter.

Noise:

Standard deviation of the HUs measured in the center of the phantom. The diameter of the ROI is 40% of the phantom's diameter.

Uniformity index:

The uniformity index (UI) is characterized by the maximum discrepancy between the mean HUs of the peripheral ROIs and the central ROI of the Uniformity module. $$UI = 100 \frac{HU_{periphery} - HU_{center}}{HU_{center} + 1000}$$

Integral non-uniformity:

Integral non-uniformity (IN) is defined as: $$IN = \frac{HU_{max} - HU_{min}}{HU_{max} + HU_{min} + 2000}$$ where \(HU_{max}\) and \(HU_{min}\) are the maximum and minimum mean HUs in the five ROIs of the Uniformity module.

Low contrast:

Measured image contrast and contrast-to-noise ratio (CNR) from the Low contrast module. CNR is defined as: $$CNR = \frac{HU_{ROI} - HU_{background}}{\sqrt{\frac{1}{2} (\sigma^2_{ROI} + \sigma^2_{background})}}$$

Low contrast - calculated:

Calculation of the minimum diameters of targets that can be detected at various noise levels. If no target is detectable at a certain noise level, the output will not be displayed.

MTF:

Spatial frequencies for different values of the modulation transfer function.

Sensitometry:

Analysis of the sensitometry module, including Contrast scale, Effective energy, and mean HU values of the target materials.

CT number linearity:

Slope, intercept, and coefficient of determination (R²) of the linear fitting of CT numbers as a function of attenuation coefficients of the sensitometry target materials.

Step 6:

Click on Report to get the results in a PDF, CSV, or JSON file.

Troubleshooting 1:

The analysis may fail or produce nonsensical results if the selected phantom model is incorrect.

Troubleshooting 2:

The slice thickness should not exceed 5 mm.

Troubleshooting 3:

Jpeg2000 compression is not supported.

References:

• Catphan 503 Manual. The Phantom Laboratory, Inc. (2017)
• Catphan 500 and 600 Manual. The Phantom Laboratory, Inc. (2015)
• Catphan 604 Manual. The Phantom Laboratory, Inc. (2015)
• Catphan 504 Manual. The Phantom Laboratory, Inc. (2013)
• Elstrøm, U. V., et al. "Evaluation of image quality for different kV cone-beam CT acquisition and reconstruction methods in the head and neck region." Acta Oncologica 50.6 (2011): 908-917.
• Anam, C., et al. "Automated MTF measurement in CT images with a simple wire phantom." Polish Journal of Medical Physics and Engineering 25.3 (2019): 179-187.
• Yin, F-F., et al. "Measurement of the presampling modulation transfer function of film digitizers using a curve fitting technique." Medical physics 17.6 (1990): 962-966.