ELECTRON BEAM THERAPY

 Electron beam radiation is a special type of
radiotherapy that consists of very tiny
electrically charged particles generated in a
machine called a linear accelerator and
directed towards the skin .

 Electron-beam therapy is advantageous because it
delivers a reasonably uniform dose from the surface
to a specific depth, after which dose falls off rapidly,
eventually to a near-zero value.
 Using electron beams with energies up to 20 MeV
allows disease within approximately 6 cm of the
surface to be treated effectively, sparing deeper
normal tissues.

Electrons are useful in treating cancer of the skin and
lips, upper-respiratory and digestive tract, head and
neck, breast.
 Skin: Eyelids, nose, ear, scalp, limbs.
 Upper-respiratory and digestive tract: Floor of mouth,
soft palate, retromolar trigone, and salivary glands.
 Breast: Chest-wall irradiation following mastectomy;
Nodal irradiation, Boost to the surgical bed.
 Other sites: Retina, orbit, spine (craniospinal irradiation),
Pancreas and other abdominal structures (intraoperative
therapy) ,Cervix (intracavitary irradiation)

 As electrons travel through a medium, they interact
with atoms by a variety of processes owing to
Coulomb force interactions.
The processes are
● Inelastic collisions with atomic electrons, resulting in
ionization and excitation of atoms and termed collisional
or ionizational loss;
● Elastic collisions with atomic nuclei, resulting in elastic
scattering that is characterized by a change in direction
but no energy loss;
● Inelastic collisions with atomic nuclei, resulting in
bremsstrahlung production and termed radiative loss;
● Elastic collisions with atomic electrons.

 The typical energy loss for a therapy electron
beam, averaged over its entire range, is about 2
MeV/cm in water and water-like tissues.
 The rate of energy loss for collisional interactions
depends on the electron energy and on the
electron density of the medium.
 The rate of energy loss per gram per square
centimetre, MeV/g·cm2 (called the mass stopping
power) is greater for low atomic number
materials than for high atomic number materials.

 When a beam of electrons passes through a medium
the electrons suffer multiple scattering, due to
Coulomb force interactions between the incident
electrons and predominantly the nuclei of the
medium.
 The scattering power of electrons varies
approximately as the square of the atomic number
and inversely as the square of the kinetic energy.
 For this reason high atomic number materials are
used in the construction of scattering foils used for
the production of clinical electron beams in a linac.

 Above Figure shows some representative electron-
beam depth–dose curves for a range of energies
from 6 MeV to 18 MeV. General features of these
curves are that, as energy increases.
 The relative surface dose increases.
 The depth of dose maximum* increases over the
lower energies, but less strongly, if at all, at higher
energies. This characteristic can vary with machine
and does not necessarily vary in a monotonic way
with energy

 The penetration increases, as reflected in the
values of therapeutic range, R50, and practical
range Rp.
 The steepness of the falling part of the curve is
roughly constant at the lower energies, but
decreases at the higher energies.
 The x-ray tail increases

 Three energy values are used to specify an electron
beam spectrum, two of them being used mostly for
the purposes of dose measurements.
1 . The mean energy at the surface E0
E0= 2.33 R50
2.The most probable energy at the surface, Ep,0,
Ep,0 =0.22+1.98Rp+00025R2p
3 .The mean energy at depth z, Ez.
Ez=Eo (1-z/Rp) where z and Rp are measured for the same
material.

 Oblique incidence has an effect on the depth–
dose distribution due to changes in the
effective penetration of the electrons and
changes in scatter.
 A simplistic approach to correct for this is to
apply the inverse square law to calculate the
change of dose due to changing distance from
the source at oblique angles.

 This approach assumes that at a point where the
SSD is increased compared to the SSD on the
central axis, the dose rate is reduced in proportion
to the inverse square of the ratio of the SSDs and
vice versa for a reduced SSD.
 The dose at the depth of maximum dose increases
and becomes greater than the zero angle
maximum when the angle becomes steep, due to
scatter from upstream excess of tissue

DOSE SPECIFICATIONAND REPORTING .
SMALL FIELD SIZES.
ISODOSE CURVES.
ELECTRON APPLICATORS.
SHIELDINGAND CUT-OUTS
INTERNAL SHIELDING
BOLUS.
INHOMOGENEITYCORRECTIONS

 Electron beam therapy is usually applied for the
treatment of superficial or subcutaneous disease.
 Treatments are usually delivered with a single direct
electron field at a nominal SSD of 100 cm.
 The dose specification for treatment is commonly
given at a depth that lies at, or beyond, the distal
margin of the disease, and the energy chosen for the
treatment depends on the depth of the lesion to be
treated.

 To maximize healthy tissue sparing beyond the tumor,
while at the same time providing relatively
homogeneous target coverage, treatments are usually
prescribed at either zmax, R90 or R80.
 If the treatment dose is specified at either R80 or R90,
the skin dose will often be higher than the prescription
dose.
 The maximum dose to the patient could be up to 20%
higher than the prescribed dose.
 The maximum dose should therefore always be reported
for electron beam therapy.

 Isodose curves are lines passing through points of
equal dose.
 Isodose curves are usually drawn at regular intervals
of absorbed dose and are expressed as a percentage
of the dose at a reference point, which is normally
taken as the zmax point on the beam central axis.
 As an electron beam penetrates a medium, the beam
expands rapidly below the surface, due to scattering.
 However, the individual spread of the Isodose
curves varies depending on the Isodose level,
energy of the beam, field size and beam collimation.

 A particular characteristic of electron beam
Isodose curves is the bulging of the low value
curves (<20%) as a direct result of the increase
in electron scattering angle with decreasing
electron energy.
 At energies above 15 MeV, electron beams
exhibit a lateral constriction of the higher
value Isodose curves (>80%).

 Normally the photon beam collimators on the
accelerator are too far from the patient to be
effective for electron field shaping.
 After passing through the scattering foil, the
electrons scatter sufficiently with the other
components of the accelerator head, and in the
air between the exit window and the patient, to
create a clinically unacceptable penumbra.

 Electron beam applicators or cones are usually
used to collimate the beam, and are attached to
the treatment unit head such that the electron
field is defined at distances as small as 5 cm
from the patient.
 Several cones are provided, usually in square
field sizes ranging from 5 × 5 cm2 to 25 × 25
cm2

 For a more customized field shape, a lead or metal
alloy cut-out may be constructed and placed on the
applicator as close to the patient as possible.
 Standard cut-out shapes may be preconstructed and
ready for use at the time of treatment.
 Custom cut-out shapes may also be designed for
patient treatment. Field shapes may be determined
from conventional or virtual simulation, but are most
often prescribed clinically by the physician prior to
the first treatment.

 For certain treatments, such as treatments of
the lip, buccal mucosa, eyelids or ear lobes, it
may be advantageous to use an internal shield
to protect the normal structures beyond the
target volume.

 The lead thickness required for the shielding
of various electron energies with transmissions
of 50%, 10% and 5% .
 As a rule of thumb, simply divide the
practical range Rp by 10 to obtain the
approximate thickness of lead required for
shielding (<5% transmission).

 For certain treatments, such as treatments of
the lip, buccal mucosa, eyelids or ear lobes, it
may be advantageous to use an internal shield
to protect the normal structures beyond the
target volume.
 Care must be taken to consider the dosimetric
effects of placing lead shielding directly on
the patient’s surface.

 Aluminium or acrylic materials have been used
around lead shields to absorb the backscattered
electrons. Often, these shields are dipped in
wax to form a 1 or 2 mm coating around the
lead.
 This not only protects the patient from the toxic
effects of the lead, but also absorbs any
scattered electrons, which are usually low in
energy

Bolus, made of a tissue equivalent material such
as wax, is often used in electron beam therapy for
the following purposes.
To increase the surface dose;
To flatten out irregular surfaces;
To reduce the electron beam penetration In
some parts of the treatment field.

 For very superficial lesions, the practical range of
even the lowest energy beam available from a
linac may be too large to provide adequate healthy
tissue sparing beyond the tumour depth.
 Bolus may also be used to define more precisely
the range of the electron beam. The difference
between the available electron beam energies from
alinac is usually no less than 3 or 4 MeV.
 If the lower energy is not penetrating enough and
the next available energy is too penetrating, bolus
may be used with the higher energy beam to fine
tune the electron beam range.

 Bolus can also be used to shape isodose lines to
conform to tumour shapes.
 Sharp surface irregularities, where the electron
beam may be incident tangentially, give rise to a
complex dose distribution with hot and cold spots.
 Tapered bolus around the irregularity may be used
to smooth out the surface and reduce the dose
inhomogeneity.
 Although labour intensive, the use of bolus for
electron beam treatments s very practical, since
treatment planning software for electron beams is
limited and empirical data are normally collected
only for standard beam geometries.

 Electron arc therapy is a special radio
therapeutic technique in which a rotational
electron beam is used to treat superficial
tumour volumes that follow curved surfaces.
 While the technique is well known and
accepted as clinically useful in the treatment
of certain tumours, it is not widely used
because it is relatively complicated and its
physical characteristics are poorly understood.

 The calculation of dose distributions in
electron arc therapy is a complicated
procedure and usually cannot be performed
reliably with the algorithms used for standard
stationary electron beam treatment planning.

ELECTRON BEAM THERAPY

More Related Content

What's hot

Similar to ELECTRON BEAM THERAPY

Recently uploaded

ELECTRON BEAM THERAPY