Library of Congress Cataloging-in-Publication Data Karzmark, C. J. Medical electron accelerators 1 C.J. Karzmark, Craig S. Nunan, and Eiji Tanabe. p. cm. : Medical Electron Accelerators: ** Signed gift inscription by co-author Craig Nunan to the previous owner on front endpaper **; Very. Medical Electron Accelerators by Karzmark, C. J.; Nunan, Craig S.; Tanabe, Eiji and a great selection of related books, art and collectibles available now at.

Author: Kijora Tojajinn
Country: Nicaragua
Language: English (Spanish)
Genre: Finance
Published (Last): 4 October 2018
Pages: 277
PDF File Size: 1.85 Mb
ePub File Size: 12.62 Mb
ISBN: 435-9-75850-663-5
Downloads: 42707
Price: Free* [*Free Regsitration Required]
Uploader: Zubei

Books by Clarence J. J. Karzmark

The mean current, spatial, and energy distributions were evaluated to assess suitability of the beam for radiotherapy treatments. This refers to electrons which are accelerated back toward the cathode, where they deposit unwanted power. In this scenario, more precise alignment would be required.

The bunch power indicates the mean power delivered per bunch, and steadily rises before reaching a steady state. As the sources of loss losses to the conducting walls and to the beam are very similar to previously published work, the required input power will also be similar to this—around 2. As such, current MRI-Linac systems require magnetic shielding, which can degrade MR image quality and limit system flexibility. These values are all well within the capabilities of modern tungsten dispenser cathodes.

The ideal accelerator for in-line MRI-Linac systems would be robust to operation in a range of field strengths without magnetic shielding.

Medical Electron Accelerators – C. J. Karzmark, Craig S. Nunan, Eiji Tanabe – Google Books

This is because magnetic force on a charged particle is minimized when the particle is travelling in the same direction as the magnetic field lines to be precise, the magnitude of magnetic force is zero when a particle travels parallel to a magnetic karxmark, and maximal when it acceleratros perpendicular. The first is to redesign the optics of the electron gun taking the presence of in-line magnetic fields into account such that the modified gun functions within these fields.


Redesign of the gun optics requires a bespoke gun design for each different field it is to be used in. Please review our privacy policy. The bunch segmentation is indicated by the dots along the horizontal axis.

Books by Clarence J. J. Karzmark (Author of Medical Electron Accelerators)

Figure 9 A shows the target current as a function of SID within the fringe field of the 1 T superconducting magnet—for comparison purposes, the current of the conventional diode gun is also plotted. Further optimization of this structure would be needed for a physical system, but this simple implementation was sufficient for the present work.

Median energy is 5. Remember acceleratosr on this computer. The mean target current of the RF based source is An estimate of the total space charge limited contribution to the current can be obtained as follows: Citations are based on reference standards. A10—21 Find a copy in the library Finding libraries that hold this item If not compensated for, this can cause severe aberrations in the Linac behavior, up to and including complete beam loss.

Both these effects need be explored in more detail in future work.

However, from speaking to industry representatives this appears to be an area to which each accelerator manufacturer has devoted substantial in-house effort. In reality, perfect alignment is not possible. It is important to note that none of the models tested here were actually designed to mitigate back-bombardment.

A novel electron accelerator for MRI-Linac radiotherapy

Exactly the same geometry as in Sec. We have also shown that such a system is far more robust than conventional systems to the presence of in-line magnetic fields, and as such could emdical an ideal solution for next generation in-line MRI-Linac systems.

Higher fields further limit the impact of space kzrzmark. Radiofrequency field calculation The electromagnetic field solution is shown in Fig. We have utilized the basic S band cavity design presented by St.


The maximum value of the interquartile range is 0. Aubin are also included. However, formatting rules can vary widely between applications and fields of interest or study. The remainder of the pulse, which is considered space charge limited, is spilt into 10 bins, and in each bin the space charge limited current is calculated according to Eq.

The E-mail message field is required. Create lists, bibliographies and reviews: First, because they are operated in a space charge limited mode of emission as opposed to temperature limited the impact of additional heating during the pulse should be smaller. As the name implies, instead of the steady state fields used to produce an acceelrators beam in conventional systems, RF electron guns utilize RF fields Fig.

A small ring like structure was added around the cathode in order to increase the radial focusing fields at the point of emission. Note that the SID is approximately mm mecical than the cathode to isocenter distance.

C were exported to matlab for further analysis. For each step, the beam assessment was repeated. CST contains a built-in interface for adding a magnetic field in this manner which was utilized.

Aubin and found to be small even for exaggerated misalignments. We have assumed perfect alignment of the accelerator with the magnetic field in this work. For small offsets, this will result in a shift in the focal spot, whilst for large enough offsets, partial or full beam loss could result. Through the computational simulations, we have shown that such a system is capable of generating an electron beam suitable for therapeutic applications.