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FRCR: Physics Lectures Diagnostic Radiology

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Presentation on theme: "FRCR: Physics Lectures Diagnostic Radiology"— Presentation transcript:

1 FRCR: Physics Lectures Diagnostic Radiology
The X-ray tube, the physics of X-ray production and ‘exposure factors’ Dr Tim Wood Clinical Scientist

2 Overview The X-ray tube Controlling the X-ray spectrum
Exposure factors Filtration X-ray beam uniformity The anode-heel effect

3 From last time…

4 X-ray Properties Electromagnetic photons of radiation
February 6, 2007 X-ray Properties Electromagnetic photons of radiation Emitted with various energies & wavelengths not detectable to the human senses Travel radially from their source (in straight lines) at the speed of light Can travel in a vacuum Display differential attenuation by matter The shorter the wavelength, the higher the energy and hence, more penetrating Can cause ionisation in matter Produce a ‘latent’ image on film/detector 4 4 4

5 Planar or three-dimensional?
Planar imaging is the most common technique used in diagnostic radiology General radiography e.g. PA chest Mammography screening Intra-oral dental radiography Fluoroscopy (but some modern ones can do 3D) The anatomy that is in the path of the beam is all projected onto a single image plane Tissues will overlap and may not be clearly visible – contrast is generally poorer than in 3D imaging techniques

6 X-ray interactions with matter
Contrast is generated by differential attenuation of the primary X-ray beam Attenuation is the result of both absorption and scatter interactions Scatter occurs in all directions, so conveys no information about where it originated – can degrade image quality, if it reaches film/detector Scatter increases with beam energy, and area irradiated

7 Interaction Processes
Elastic scattering Photoelectric effect Compton effect

8 Photoelectric Effect

9 Compton Effect

10 The Mass Attenuation Interaction Coefficient

11 The Mass Attenuation Interaction Coefficient

12 Maximising Radiographic Contrast
More Photoelectric absorption means higher patient dose Scatter rejection techniques attenuate the primary beam, so a higher patient dose is required for acceptable image receptor dose NEED TO BALANCE IMAGE QUALITY WITH PATIENT DOSE!!! Hence, the principle of ALARA (As Low As Reasonably Achievable) Use the highest energy beam that gives acceptable contrast, consistent with the clinical requirements

13 The X-ray tube

14 X-ray tube design - basic principles
Electrons generated by thermionic emission from a heated filament (cathode) Accelerating voltage (kVp) displaces space charge towards a metal target (anode) X-rays are produced when fast-moving electrons are suddenly stopped by impact on the metal target The kinetic energy is converted into X-rays (~1%) and heat (~99%)

15 Electron production in the X-ray tube
Applied voltage chosen to give correct velocity to the electrons kV + - mA Filament (heats up on prep.)‏ Target

16 Bremsstrahlung

17 Characteristic X-rays

18 The X-ray spectrum Combination of these yields characteristic spectrum.

19 The X-ray spectrum The peak of the continuous spectrum is typically one third to one half of the maximum kV The average (or effective) energy is between 50% and 60% of the maximum e.g. a 90 kVp beam can be thought of as effectively emitting 45 keV X-rays (NOT 90 keV) Area of the spectrum = total output of tube As kVp increases, width and height of spectrum increases For kVp, intensity is approximately proportional to kVp2 x mA

20 Controlling the X-ray spectrum -Exposure factors
Increasing kVp shifts the spectrum up and to the right Both maximum and effective energy increases, along with the total number of photons Increasing mAs (the tube current multiplied by the exposure time) does not affect the shape of the spectrum, but increases the output of the tube proportionately

21 Quality & Intensity Definitions:
Quality = the energy carried by the X-ray photons (a description of the penetrating power) Intensity = the quantity of x-ray photons in the beam An x-ray beam may vary in both its intensity and quality 21

22 Back to tube design…

23 X-ray tube design Heat generation is a significant problem for X-ray tubes, and is generally the limiting factor upon their use Hence, it is necessary to: Ensure efficient cooling mechanisms – take the heat away so it doesn’t build up with multiple exposures Have mechanisms to prevent over-heating – should it get too hot, have mechanisms in place to stop further exposures Minimise heat generation on a single point of the anode (stop it melting!)

24 X-ray tube cooling Generally, the tungsten target is mounted on a copper block/rotor (either directly or indirectly) that extends out of the evacuated glass envelope Heat is transferred from the target to the surrounding coolant (most often oil, but very occasionally water) via conduction and/or radiation, which in turn gives up its heat to the atmosphere (possibly through a heat exchanger) Expansion bellows can detect when the coolant is getting too hot (or by other means) and prevent further exposures BUT, what about spreading the heat generating processes over a larger area?...

25 The rotating anode Heat can be spread over a large area by rotating the anode during exposure Tungsten annulus set in a Molybdenum disk attached to a copper rotor The assembly is rotated via an induction motor Full rotation ~20 ms Takes about 1 s to get up to speed The prep phase (push the exposure switch down to the first stop until you can hear it whirring) before pushing down all the way to expose

26 X-ray tube design – The rotating anode

27 Geometric unsharpness and the focal spot
Spatial resolution is dependent upon (more on this next time…): Geometrical unsharpness Motion unsharpness Absorption unsharpness Geometric unsharpness is related to the fact that we cannot (and in fact do not want to) produce an ideal point source of X-rays The focal spot of the X-ray tube has a finite size that results in blurring across the edge of structures Can be reduced by using a smaller focal spot, decreasing the object-film distance (OFD) or using a longer focus-to-film distance (FFD)

28 Geometric unsharpness – The ideal point source
Ideal point source of X-rays FFD Object OFD Film/detector

29 Geometric unsharpness – A ‘real’ focal spot
Focal spot of finite size, f FFD Object OFD Film/detector Penumbra

30 Geometric unsharpness and the focal spot
So, to minimise geometric unsharpness, the smallest focal spot should be used… BUT, this would be at the expense of excess heating and reduced tube life The solution is to use an angled target as the source of X-rays Angle allows broad beam of electrons to give a smaller apparent focal spot Have multiple filaments for focal spot size selection – large focal spot for general use (tube lasts longer), and small focal spot where better resolution is required

31 X-ray tube design – dual focus

32 The focal spot Actual focal spot size

33 The focal spot Apparent focal spot size will vary across the film
Elongated on cathode side, contracted on anode side Target angles vary between 7 and 20° Steeper angles allow greater tube loading BUT, the useful X-ray field is smaller due to the anode-heel effect (more on this later) Hence, steep target angles suitable for applications with limited fields of view e.g. mammography, cardiology Typical focal spot sizes are mm for mammography mm for general radiography 0.6 mm for fluoroscopy mm for CT

34 Heat rating kV, mA and exposure time should be such that the temperature of the anode does not exceed its safe limit The control system is designed to prevent exposures that exceed the tube rating Require much higher tube ratings for CT and interventional fluoroscopy units

35 Shielding X-rays are emitted from the target in all directions, not just towards the patient Hence, Lead shielding is used in the tube housing to absorb X-rays not required for imaging of the patient Legal requirements on how much ‘leakage’ radiation is emitted from the tube during operation Medical Physics testing checks this during the Critical Examination of new installations

36 The diagnostic X-ray tube

37 The diagnostic X-ray tube

38 Factors Affecting Patient Dose
Tube Current (mA)/Exposure Factor (mAs) Double the mA/mAs, double the intensity Beam quality not affected Tube Voltage (kVp) Intensity α kVp2 Penetrating power increases with kVp Higher kVp reduces skin dose Filtration (mm Al) Focus-to-skin distance 38 38

39 Patient dose reduction – Filtration and beam hardening
‘Soft x-rays’ contribute to patient dose without contributing to image production Placing Al filters in the beam will increase beam quality – this is known as ‘Beam Hardening’ Alternative materials may be used for filtration in specialised applications e.g. mammography (Mo, Rh, Ag) and fluoroscopy (Cu) Lowest energy photons are most readily absorbed as photoelectric absorption dominates (proportional to the E3) As the beam passes the Al, the proportion of low energy photons is reduced, and the average photon energy increases

40 Filtration

41 Filtration

42 Patient dose reduction – Filtration and beam hardening
Hence, Patient dose is reduced with little affect on the radiation reaching the detector However; Radiographic contrast is reduced due to the higher mean energy of the beam Greater exposure factors required to yield satisfactory dose at film/detector (have to drive the tube harder, and hence tube life may be reduced) The X-ray beam is also filtered by the target that they are produced in, the coolant oil and the window of the housing ‘Inherent filtration’ equivalent to about 1 mm Al

43 Focus-to-skin Distance: The Inverse Square Law
For a point source, and in the absence of attenuation, intensity decreases as the inverse of the square of the distance This is a statement of the conservation of energy

44 The inverse square law Patient dose can be significantly reduced by increasing the distance to the X-ray tube FSD < 45 cm should not be used (<60 cm for chests – 180 cm used in practice)

45 X-ray beam uniformity The X-ray tube emits X-rays in all directions
A collimator system is used to adjust the beam to the required size Two pairs of parallel blades of high attenuation material that can be adjusted to define the required rectangular field size (has a light beam system for visualisation)

46 The anode heel effect Ideally, the X-ray beam defined by the jaws would be uniform across the whole image However, this is not the case due to the anode heel effect, which results from the combination of the angled anode and the depth at which X-rays are generated The steeper the target angle, the worse the effect Filtration differences at the edge of the field, the inverse square law and apparent focal spot size also influence beam uniformity, but to a lesser extent

47 The anode heel effect

48 The anode heel effect The electrons penetrate a few micrometres below the surface of the anode before generating X-rays Hence, the X-rays that are generated in the target may be attenuated on their way out X-rays travelling towards the anode edge of the field (A) will have to pass through more of the target before exiting the tube Hence, attenuation will be greater on this edge, and beam intensity will be lower than on the Cathode side of the field (B) Roughening of the anode surface as the tube ages make this effect worse

49 The anode heel effect Generally not noticeable on most films
This effect is corrected for in digital imaging through ‘flat-fielding’ the detector The anode heel effect is actively exploited in some modalities e.g. mammography (more on this later) Can be minimised by using greater focus-to-film distances, smaller fields and shallower target angles

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