Dr hab. Zbigniew Serafin, MD, PhD [email protected] · Medical Image Properties Spatial Resolution or...
Transcript of Dr hab. Zbigniew Serafin, MD, PhD [email protected] · Medical Image Properties Spatial Resolution or...
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Medical Image Properties
mainly based on:
R. Dickinson: RSNA & AAPM Physics Curriculum: Module 7. 2
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Medical Image Properties
Spatial Resolution or High Contrast Resolution
2D projection medical images have three dimensions:
• length
• width
• gray scale
Spatial Resolution = ability to perceive two distinct objects in the spatial
dimensions of an image
→ are the objects still resolved as two distinct objects if they are smaller in
size or closer together spatially?
Ideal PSF Actual PSF 3
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Medical Image Properties
Spatial Resolution or High Contrast Resolution
the resolution of an imaging system is measureable and limited
4 lp/cm
5 lp/cm
6 lp/cm
7 lp/cm
8 lp/cm
9 lp/cm
10 lp/cm
12 lp/cm
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Medical Image Properties
Spatial Resolution or High Contrast Resolution
Blurring – due to specific mechanisms of an imaging system
motion – voluntary vs. involuntary (cardiac motion); best controlled by
acquisition time
CT imaging – slice thickness and partial volume averaging; structures that
are not perpendicular to slice plane will be blurred (amount of blur is
proportional to slice thickness and angle relative to slice plane)
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Medical Image Properties
Spatial Resolution or High Contrast Resolution
Matrix Size and Field of View (FOV)
if FOV is constant: increases
the matrix size improves resolution
if matrix size is constant: decreasing
the FOV improves resolution
pixel size = FOV / # pixels
6 6
10242 pixels 642 pixels
322 pixels 162 pixels
C.F. Bushberg, et al. The Essential Physics of Medical
Imaging, 2nd ed., pp. 82.
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Medical Image Properties
Noise
noise is the random (stochastic)
component in the image
as signal increases, the noise also
increases but at a slower rate,
therefore, the relative noise decreases
with increasing signal
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Medical Image Properties
Noise
Signal-to-noise (SNR = „image quality”) is the inverse of the relative
noise; thus, as the signal increases, the SNR increases
• if the signal is doubled, the dose is also doubled, but the SNR (or
the QUALITY of the image) only increases by sqrt(2)
• to double the SNR, you must increase the dose to the patient by
a factor of 4
120 kVp 140 kVp
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Medical Image Properties
Contrast
= the difference in the image
grayscale between two closely
adjacent regions on the image
contrast in an image is a direct
result of image acquisition,
processing, and display
contrast between two structures
increases if there is:
• difference in thickness
• difference of linear attenuation
coefficients of tissues /
materials
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Medical Image Properties
Contrast
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Medical Image Properties
EXERCISE
How to get good quality CT images in obese patients?
Try to describe CT examination of the highest radiation dose.
What will be CT# of a pineal calcification using 0.6 mm and 5.0 mm
slice?
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computers, PACS & RIS
mainly based on:
E. Samei, et al.: AAPM/RSNA Tutorial on Equipment Selection: PACS Equipment Overview. General
Guidelines for Purchasing and Acceptance Testing of PACS Equipment. RadioGraphics 2004.
Brent K. Steward: Computers in Medical Imaging – Chapter 4, Computer Networks, PACS and
Teleradiology – Chapter 17. 12
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computers, PACS & RIS
digital storage of images
images are usually stored as a 2D array (matrix) of addressable
data, I(x,y): I(1,1), I(2,1), … I(n,m-1), I(n,m); n = column, m = row
each addressable location of the image is called a pixel (picture
element) represented by one value (e.g., digital value, gray level or
Hounsfield unit)
total number of bytes/image = pixels/image ∙ bits/pixel‡ ∙ (1 byte/8
bits)
c.f.: Bushberg, et al., The Essential Physics of
Medical Imaging, 2nd ed., p. 71.
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computers, PACS & RIS
medical image processing
addition or subtraction, e.g., digital subtraction angiography (DSA)
spatial filtering
• smoothing (removing quantum mottle – noise)
• edge enhancement, e.g., computed radiography (CR)
reconstruction from projections
• back-projection, e.g., computed tomography (CT), single photon
and positron emission tomography (SPECT and PET)
• Fast Fourier Transform, e.g., magnetic resonance imaging (MRI)
calculation of physiological performance indices, e.g., nuclear
medicine
generation and manipulation of volumetric data sets, e.g., MIPs
image co-registration (“fusion”), e.g., CT and PET
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computers, PACS & RIS
Computer-Aided Diagnosis (CAD)
computer program that uses specific image processing algorithms
and decision threshold parameters to detect features in an image
likely to be of clinical significance in images
assist as a secondary reader to call attention to objects that might
have been overlooked
first implemented in mammography:
• masses
• microcalcification clusters
• architectural distortions
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computers, PACS & RIS
teleradiology
= transmission of images for viewing at sites remote from where
they are acquired and reporting back
not a medical procedure in EU
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computers, PACS & RIS
PACS – Picture Archiving and Communication System
inter- and intrainstitutional computational system that manages the
acquisition, transmission, storage, distribution, display, and
interpretation of medical images
image file standard – Digital Imaging and Communications in
Medicine (DICOM)
administrative system – Radiology Information System (RIS)
administrative system – Hospital Information System (HIS)
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computers, PACS & RIS
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computers, PACS & RIS
Storage
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computers, PACS & RIS
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computers, PACS & RIS
EXERCISE
What is the best way to export medical images to the referring
physician?
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Characteristics of Sound
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mainly based on:
Ultrasound. RSNA & AAPM Physics Curriculum: Module 15 by Renée Dickinson
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Characteristics of Sound
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The basics – how ultrasound images are formed?
Mechanical energy is transmitted into tissue producing vibrations
Energy propagates through the tissue
Time between pulse emission and echo return determines depth
Amplitude of the echo determines grey scale
“call and response” pulse-echo imaging
c.f. Dowsett, et al. The Physics of Diagnostic Imaging, 2nd ed., p. 512.
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Characteristics of Sound
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Propagation of Sound
Sound is mechanical energy
Particles in the medium transfer the mechanical energy (small back
and forth displacement); vibrational motion produces
Compression (high pressure = high amplitude signal)
Refraction (low pressure = low amplitude signal)
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Characteristics of Sound
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Wave parameters
Wavelength (λ) [mm or μm] – distance between compression and refraction
(distance b/w two repeated points on a sine wave)
Frequency (f) [cycles per second = Hertz (Hz)] – number of times the wave
oscillates through a cycle each second
o Infrasound – sound wave f < 15 Hz
o Audible – 15 Hz < f < 20 kHz
o Ultrasound – f > 20 kHz (generally, medical ultrasound is 2-10 MHz)
Period (1/f) [seconds] – time duration of one wave cycle
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Characteristics of Sound
26 EZ
constf
fc
Ec
material c [m/s] Z
air 330 0,0004
water 1495 1,49
adipose tissue 1450 1,38
liver 1550 1,64
blood 1570 1,66
muscles 1620 1,72
bones 4080 3,75
c – speed of propagation
E – volume elasticity
ρ – density
λ – wavelength
Z – acoustic impedance
f – frequency
Important Concept:
a higher frequency beam has a shorter wavelength
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Characteristics of Sound
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Wave parameters
The wavelength and frequency determine resolution and attenuation.
o High frequency (small wavelength) → improved spatial resolution,
however, depth of penetration is reduced
o Low frequency (long wavelength) → increased depth of
penetration, but resolution is degraded
Constructive and destructive interference – mostly dependent on the
wave phase
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Characteristics of Sound
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Wave parameters
Pressure, intensity, dB Scale
Recall: mechanical energy
causes particle
displacements, which alter
local pressure in propagation
medium
Pressure amplitude – peak
max or min value from the
average pressure in the
absence of a sound wave
c.f. Bushberg, et al. The Essential Physics of Medical Imaging, 2nd ed., p. 471.
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Characteristics of Sound
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Wave parameters
Relative intensity and power are described in units terms decibel (dB)
In diagnostic U/S, the intensity of the incident pulse can be up to 1
million times more than the echo pulse
The log function “compresses” the large ratios and “expands” the
small ratios into a more manageable range
o A change in 10 dB → an order magnitude (10x) change in
intensity
o A change in 20 dB → two orders magnitude (100x) change in
intensity
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Interactions of Ultrasound
with Matter
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mainly based on:
Ultrasound. RSNA & AAPM Physics Curriculum: Module 15 by Renée Dickinson
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Interactions of Ultrasound with Matter
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Interactions are dependent on acoustic properties of matter
Acoustic Impedance
Interactions
o Reflection – occurs at tissue boundaries (acoustic impedance of
adjacent materials)
o Refraction – change in direction of transmitted energy
o Scattering – occurs by reflection or refraction; energy diffuses in
many direction (affects texture and grey scale of acoustic image)
o Absorption – acoustic energy is converted into heat (sounds
energy is lost)
o Attenuation – loss of intensity from absorption and scattering
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Interactions of Ultrasound with Matter
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Acoustic Impedance (Z)
Similar to the stiffness and flexibility of spring
Dependent on medium density and speed of sound
SI Units is 1 kg per m2 per second
material c [m/s] Z
air 330 0,0004
water 1495 1,49
adipose tissue 1450 1,38
liver 1550 1,64
blood 1570 1,66
muscles 1620 1,72
bones 4080 3,75
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Interactions of Ultrasound with Matter
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Acoustic Impedance (Z)
For the energy transfer between two adjacent mediums:
o A large difference in the impedance results in a large reflection of
energy
o A minor difference in the impedance allows continued propagation
of energy (little reflection at the interface)
o Example: soft tissue to air-filled lung – large ΔZ, beam almost
entirely reflected
o …whereas if Z1 ~ Z2, then only minor reflections occur
Important concept:
acoustic impedance gives rise to difference in transmission and reflection of U/S energy (basis for pulse echo imaging)
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Interactions of Ultrasound with Matter
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Acoustic Impedance (Z)
small Z difference
large Z difference
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Interactions of Ultrasound with Matter
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Reflection
Result of acoustic impedance
Reflection coefficient –
describes fraction of sound
intensity incident on a interface
that is reflected
Note: reflection depends on
angle of incidence
c.f. Bushberg, et al. The Essential Physics of Medical Imaging, 2nd ed., p. 478.
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Interactions of Ultrasound with Matter
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Reflection
for perpendicular
incidence: Intensity
reflection coefficient
RT
ZZ
ZZ
I
IR r
1
2
21
21
0
I – wave intensity
Z – acoustic impedance
R – reflected energy
T – transmitted energy
material c [m/s] Z
air 330 0,0004
water 1495 1,49
adipose tissue 1450 1,38
liver 1550 1,64
blood 1570 1,66
muscles 1620 1,72
bones 4080 3,75
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Interactions of Ultrasound with Matter
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Refraction
As with light, sound is refracted if the incident sound is not
perpendicular to an medium interface
U/S frequency does not change at the boundary
Speed of the sound (both transmitted and reflected) changes
Angles (measured relative to normal incidence at the boundary) of
transmission and reflection are determined by the change in the
speed of sound
c.f. Bushberg, et al. The Essential Physics of Medical Imaging, 2nd ed., p. 478.
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Interactions of Ultrasound with Matter
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Refraction
No refraction if…
o Angle of incident is normal
o Speed of sound is the same in
both mediums
Straight line propagation is assumed
in ultrasound
o Refraction ‘artifacts’ cause
shadows and enhancements
because the sound waves are
bent from their expected paths
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Interactions of Ultrasound with Matter
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Scattering
Smooth boundary between media; uniform medium
Irregular surfaces or media
Reflects fewer echoes directly back to the transducer
Can cause diminished strength (amplitude) in echoes because of
destructive interference
c.f. Bushberg, et al. The Essential Physics of Medical Imaging, 2nd ed., p. 480.
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Interactions of Ultrasound with Matter
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Scattering
Two cases for scattering:
o At the boundary – smaller
wavelengths cause the
boundary to become
‘rough’ and the reflections
become diffuse
o Or small object reflectors
in tissue – diffuse
scattering patterns are
characteristic of specific
organ or tissue structure
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Interactions of Ultrasound with Matter
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Scattering
Scatter from diffuse reflectors affects the signal amplitude
Scatter depends on:
o Number of scatters (small objects) per unit volume
o Acoustic impedance difference
o Size of the scatters
o Ultrasonic frequency (because frequency is relate to wavelength)
Hyperechoic – high scatter amplitude relative to avg background signal
Hypoechoic – lower scatter amplitude relative to avg background signal
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Interactions of Ultrasound with Matter
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Scattering
Hyperechoic
Hypoechoic
Isoechoic
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Interactions of Ultrasound with Matter
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Attenuation
Attenuation is the loss of acoustic energy (signal amplitude), results
from scatter and absorption (heat)
Absorbed acoustic energy
o Attenuation coefficient, μ [dB per cm], is relative intensity lost per
centimeter of travel
o U/S attenuation is approximately proportional to frequency
o Since the dB scale is logarithmic, the signal intensity is attenuated
exponentially with distance
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Interactions of Ultrasound with Matter
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Attenuation
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Image Acquisition
45
mainly based on:
Ultrasound. RSNA & AAPM Physics Curriculum: Module 15 by Renée Dickinson
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Image Acquisition
46
Ultrasound System
Beam former – generation of electronic
delays for individual transducer elements in
an array to achieve transmit/receive
focusing and beam steering
Pulser (transmitter) – electrical voltage for
exciting piezoelectric (PZT) elements;
controls output transmit power by an
applied voltage
Transmit/receive switch – synchronized
electronically with pulser
Scan converter / image memory
Display
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Image Acquisition
47
Modes of Operation
A-mode: amplitude
o Single pulse echo
o Clinical Application – ophthalmology
B-mode: brightness
o Brightness is proportional to the signal amplitude
o Used in M-mode and 2D grey-scale imaging
o Generates a 2D image; covers a plane of interest rather than on single
line of transmit/receive
M-mode: motion
o Fixed transducer position and beam direction – measure of motion
patterns for anatomy along a single line
o Recent developments in Doppler U/S replaced the need for M-mode
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Image Acquisition
48
Modes of Operation
A-mode: amplitude
o Single pulse echo
o Clinical Application – ophthalmology
B-mode: brightness
o Brightness is proportional to the signal amplitude
o Used in M-mode and 2D grey-scale imaging
o Generates a 2D image; covers a plane of interest rather than on single
line of transmit/receive
M-mode: motion
o Fixed transducer position and beam direction – measure of motion
patterns for anatomy along a single line
o Recent developments in Doppler U/S replaced the need for M-mode
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Image Acquisition
49
A-mode
B-mode
M-mode
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Image Acquisition
50
Transducers or Probes
A transducer produces and detects the U/S waves
Ceramic elements with electro-mechanical
properties
o Transmit – converts electrical energy (applied
voltage) to mechanical energy
o Receive – converts mechanical energy to
electrical energy
Major parts of a transducer
o Piezoelectric (PZT) elements – functional
component of the transducer
o Matching layer – reduces acoustic impedance
o Backing (damping) block – absorbs backwards
directed waves
c.f. Bushberg, et al. The Essential Physics of Medical Imaging, 2nd ed., p. 484.
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Image Acquisition
51
Transducers or Probes
Piezoelectric elements – functional component of the transducer
The piezoelectric effect
o Transmit mode – electrical energy is converted to mechanical (sound)
energy by physical deformation of the crystal structure
• Applying an alternating current to the crystal of a transducer causes it
to expand and contract (vibrate), producing sound at that vibrational
frequency
o Receive mode – conversely, mechanical pressure applied to the surface
of the crystal during receive mode is converted into electrical energy
• On reception of a sound echo, the crystal vibrates at the sound
frequency of the echo and produces an electrical current
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Image Acquisition
52
Transducers or Probes
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Image Acquisition
53
Image Quality
Spatial Resolution – 3 distinct measures
o Axial – depth resolution
• Minimal distance between objects is ½ the spatial pulse length
• Depends on frequency & damping factor
o Lateral – resolution perpendicular to the beam path
• Depends on beam diameter (since beam diameter varies with depth,
the lateral resolution varies withdepth) and mechanical/electronic
focusing
o Elevational (slice thickness)
• Typically worst resolution for array transducers
• Volume averaging of acoustic details
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Additional Techniques
54
mainly based on:
Ultrasound by Kalpana Kanal
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Additional Techniques
55
Harmonic Imaging
Degrades axial resolution
Improves lateral spatial resolution
Best used in abdominal imaging, use lower frequency to begin with, then
switch to higher frequency harmonics for better image quality and less clutter
adjacent to the transducer
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Additional Techniques
56
Contrast Imaging
High frequencies also arise due to:
o The vibration of encapsulated gas bubbles used as contrast agents
o The responses of microbubble contrast agents under low and high
pressure reveal nonlinear compression and expansion of the bubble
radius
SF6
SF6
SF6
SF6
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Additional Techniques
57
Contrast Imaging
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Additional Techniques
58
Doppler Ultrasound
Based on shift in frequency in an US wave caused by a moving reflector
(blood cells)
Objects moving toward the transducer - higher frequency and shorter
wavelength
Objects moving away from the transducer - lower frequency and longer
wavelength
If object moving perpendicular to the transducer, no change in the observed
frequency or wavelength
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Additional Techniques
59
cos2 001 c
vffff
f – wave frequency
v – blood velocity
c – wave velocity
α – angle wave / blood flow
c.f. Bushberg, et al. The Essential Physics of Medical Imaging, 2nd ed., p. 532.
Doppler Ultrasound
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Additional Techniques
60
Doppler Ultrasound
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Additional Techniques
61
Color Doppler Ultrasound
CD imaging provides a 2D visual display of
moving blood in the vessels, superimposed
on the conventional gray-scale image
Typically, flow toward the transducer is
assigned red and flow away from the
transducer blue
The color intensity varies with flow intensity
Color Doppler can detect flow in vessels too
small to be seen by imaging alone
Spatial resolution of the color image is
much lower than that of gray-scale image
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Additional Techniques
62
Power Doppler Ultrasound
PD permits detection and interpretation of
slow blood flow but sacrifices directional and
quantitative flow information
It uses the return Doppler signal strength
alone
It is more sensitive than standard color flow
imaging
The image signal does not vary with the
direction of flow
Enchanced sensitivity in the PD acquisition –
in areas perpendicular to the beam direction,
where the signal is lost in CD
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Additional Techniques
63
Spectral Doppler Ultrasound
Plot of Doppler shift frequency spectrum versus time
Amplitude is encoded as gray-scale variation
The spectral waveform - audible signal and provides information about
o the direction of the flow
o how fast the flow is traveling (velocity)
o the quality of the flow (normal vs. abnormal)
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Additional Techniques
64
Spectral Doppler Ultrasound
Pulsatility Index (PI) increases as flow is impeded by e.g. a stenosis proximal
to the site of measurement
Resistivity Index (RI) reflects the resistance to blood flow caused by
microvascular bed distal to the site of measurement. RI is altered by both
vascular resistance and vascular compliance
systolic
diastolicsystolic
mean
diastolicsystolic
mean
v
vv
v
vvRI
v
vv
v
vvPI
max
minmax
minmax
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Additional Techniques
65
Doppler Ultrasound
Duplex / Triplex Scanning
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Additional Techniques
66
3D / 4D Imaging
Duplex / Triplex Scanning
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Applications
67
mainly based on:
Ultrasound by Kalpana Kanal
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Applications
68
Contraindications
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Applications
69
Safety
The intensity at a specific point during a single pulse is the spatial peak pulse
average intensity (ISPPA), W/cm2
The intensity at a specific point averaged over a long period (many pulses) is
the spatial peak temporal average intensity (ISPTA), W/cm2
No bioeffects have been shown below an ISPTA of 100 mW/cm2
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Applications
70
Safety
At high power levels, ultrasound can cause:
Likelihood of Cavitation (Mechanical Index, MI)- the creation and collapse of
microscopic bubbles
Small-scale fluid motions called microstreaming
Tissue heating occurs as a result of energy absorption and is the basis of
using ultrasound for hyperthermia treatment
Thermal Index, TI is the ratio of the acoustic power produced by the
transducer to the power required to raise tissue in the beam area by 1 deg C
mode Pressure amplitude [MPa] ISPTA [W/cm2]
B-scan 1.68 19
M-mode 1.68 73
PD 2.48 1 140
CD 2.59 234
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Applications
71
Safety
At high power levels, ultrasound can cause:
Mechanical damage – cavitation the creation and collapse of microscopic
bubbles. Effects: capillary hemorrhage in lung and intestinal hemorrhage in
neonates and preterm babies
Tissue heating occurs as a result of energy absorption and is the basis of
using ultrasound for hyperthermia treatment
Thermal Index, TI is the ratio of the acoustic power produced by the
transducer to the power required to raise tissue in the beam area by 1 deg C
o Scan mode
o Exposure duration
o Tissue sensitivity
Non human experiments found that increases of ≥ 40 C for > 5 minutes can
cause developmental abnormalities in fetal tissues
ALARA
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Applications
72
Common indications
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Applications
73
TCD
CNS
trans-fontanel us
spine
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Applications
74
carotids
neck
lymph nodes
thyroid
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Applications
75
thymus
chest
pleural cavity
ribs
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Applications
76
kidney
abdomen
spleen
pancreas
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Applications
77
pregnancy
pelvis
testicles
TVU
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Applications
78
knee
MSK
muscles
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Applications
79
What structures cannot be diagnosed with US?
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