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Transcript of Tecnologias mn
Tecnicas de Medicina
Nuclear
Bases y fundamentos
Procedimiento de obtención de imágenes médicas
Gammagrafía
Tomografia Computarizada por Emision de Fotones
Simples (SPECT)
Tomografía por Emisión de Positrones . PET
Aprender conceptos básicos sobre cómo se generan
las imágenes de Medicina Nuclear: gammagrafías,
SPECT y PET
La Medicina Nuclear (MN) utiliza sustancias
radiactivas: isótopos (iso = igual; topos = lugar)
Fines: diagnósticos, terapéuticos y de
investigación.
Estas sustancias radiactivas (radionúclidos o
trazadores) se introducen (in vivo) en la parte
del cuerpo que se quiere estudiar y se hace la
imagen detectando la radiación que emite.
Es mínimamente invasiva (inyección).
Es una técnica funcional: no estudia la
anatomía sino su funcionamiento.
Abarca en la practica, la totalidad del
organismo.
El nivel de radiación es similar al de
otras técnicas radiológicas (ej. RX)
Radionúclido Energía
(keV)
T(1/2) Estudios
99mTc131I
67Ga133Xe201Tl
140
364
39
81
30-140
6 horas
8´04 días
3´25 días
5´3 días
72 horas
Cerebro, tiroides, riñón, pulmón
Tiroides y riñon
Tumores y abscesos
Pulmón
Estudios cardíacos
INTRODUCCIÓN
Algunos de los elementos más usados en MN:
Fines diagnósticos:
Renograma isotópico de un
paciente con HTA
secundaria, que muestra una
atrofia renal derecha
Imágenes de Medicina nuclear
normales.
Diferencias (MN, rayos X):
•MN usa radiación gamma ():
Energías Frecuencias
MN: [104 - 107 eV] [1019 - 1022 Hz] Rayos X: [10 - 104 eV] [1015 - 1019 Hz]
•En MN la fuente de radiación es interna (en el interior del
cuerpo del paciente), en rayos X es externa.
•Trazador con radiofármaco: permite obtener una representación
morfológica o información funcional o dinámica. (En rayos X
contraste)
INTRODUCCIÓN
Esquema básico de un sistema de
IMN
Sustanciaradiactiva
órganoseleccionado
Radiación
Cristal decentelleo
Analizadorde amplitud
Contador deimpulsos
Gammagrafía
Colimador
Tubofotomultiplicador
Imágenes en Medicina Nuclear
Uso de Rx, radionucleidos y de
radiofarmacos en obtención de imágenes
Con las imagnes de Medicina Nuclear pueden observarse procesos fisiologicos,
como asimismo de Estructuras anatomicas.
En estas tecnicas se inyectan en los pacientes por via
Intravenosa, drogas radiactivas (Radiofarmacos) que emiten rayos gamma
Una vez que son captados por el tejido, organo o sistema de interes.
La cantidad de radionucleidos inyectados, se encuentran en el orden de
concentraciones
de nano a picomolar, de manera de disminuir los riesgos para los pacientes
Durante el estudio de los procesos fisiologicos delos mismos.
El semiperiodo fisico de estos materiales radiactivos es de solo unos pocos
Minutos a semanas. The time course of the
process being studied and the radiation dose to the target are
considered. The nuclear camera then, in effect, takes a time-exposure
"photograph" of the pharmaceutical as it enters and concentrates in
these tissues or organs. By tracing this blood flow activity, the
resulting nuclear medicine image tells physicians about the biological
activity of the organ or the vascular system that nourishes it. Nuclear
Medicine has a wide variety of uses, including the diagnosis of cancer,
studying heart disease, circulatory problems, detecting kidney
malfunction, and other abnormalities in veins, tissues and organs.
Medicina Nuclear: camara gamma
O N NH COOEt EtOOC
99mTc
S S
Aplicacion: perfusion cerebral
Radiofarmacos
Imagen nuclear de
Cuerpo completo
SPECT esta basada en una tecnica convencional de imagenes nucleares
Y usando ademas la tecnica y metodos de reconstruccion tomografica.
SPECT: single photon emission
computerized tomography
Collimator
NaI(Ti)
crystal
PMT
a
b c
d
Electronics
X
Y
Counts/pixel
Resolución Espacial – Es la medida del grado de detalles provistos por la
imagen final reconstruida y por lo tanto del tamaño de lesiones que
potencialmente pueden ser detectadas. En otras palabras: cual es el grado
de detalle en el cual puede ser Observada una imagen o cuanto puede ser
resuelta o separada.
Sensibilidad, tiempo muerto – describe de que manera y con que eficiencia
se Detectan los decaimientos radiactivos y la distribucion del trazador, para
Formar finalmente la imagen.
Una fuente isotropica irradia en forma igual hacia todas las direcciones del
espacio. Los detectores, recolectan parte del total de los decaimientos,
dentro de un angulo Solido limitado por los colimadores.
Algunos de estos eventos se pierden debido a que el sistema necesita de
un tiempo de procesamiento entre la deteccion de un evento y el siguiente.
(dead time o Tiempo Muerto).
Características de Rendimiento de los
sistemas de imágenes de Medicina Nuclear
Signal to Noise ratio (SNR) - The relative strength of the information
and the noise. If the lesion is small compared with the spatial resolution
the contrast is reduced because the high lesion activity blurred into the
neighborhood by the detector response.
Uniformity, Linearity - The image of an object should be independent
of its position in the field of view. This is not true in real systems.
This can be assessed in calibration measurements to derive correction
factors. This reduces non-uniformity from 10% to 3%.
The conventional nuclear medicine imaging process.
Typical radionuclides used are 140 KeV Tc-99m and 70 KeV photons
from Tl-201.
The gamma ray photons emitted from the radiopharmaceutical
penetrate through the patient body and are detected by a set of
collimated radiation detectors. The emitted photon experience
interaction within the body by the photoelectric effect which stops
their emergence from the body or compton scattering which
transfers part of the energy to free electrons and the photon is
scattered into a new direction. These photons are also detected
by the camera and cause blurring of the image if un-treated with
image reconstruction and processing tools.
Pixel I
Activity ai
Intersected area fi
r
P(r,q)
q
In 2-D tomographic imaging, the 1D detector array rotates around
the object distribution f(x,y) and collects projection data from various
projection angles q. The integral transform of the object distribution
to its projections is given by:
Ç
Which is called the Radon transform. The goal of image
reconstruction is to solve the inverse Radon transform. The solution
is the constructed image estimate f(x,y) of the object distribution
f(x,y).
The measured projection data can be written as the integral of
radioactivity along the projection rays.
p t c I x y dst' ( , ) exp[ ( , ) ]q
z0
The measured projection data can be written as the integral of
radioactivity along the projection rays.
In SPECT attenuation coefficient is not so important, so it can
be considered as constant in the body region under inspection.
l(x,y) is the pathlength between the point (x,y) and the edge of the
attenuator (or patient’s body) along the direction of the projection
ray.
The image reconstruction problem is further complicated by the non
stationary properties of the collimator detector and scatter response
functions and their dependence on the size and composition of the
patient’s body.
p t c x y dse( , ) ( , )q
z
p t c x y l x y dse( , ) ( , ) exp[ ( , )]q
z
Cristal de centelleo (Yoduro de sodio con talio-INa(Ta))
Transductor de energía en energía luminosa.
El cristal está acoplado a un conjunto de fotomultiplicadores de sección exagonal.
Transductor de energía luminosa en electrones. Salida del fotomultiplicador: impulsos eléctricos amplitud proporcional a la energía de la
radiación
y número proporcional a la actividad del elemento radiactivo en el punto analizado.
Llevando estas señales a un circuito de posicionamiento, obtenemos las coordenadas X e Y, que indican la posición donde se ha detectado
el fotón.
C
PROCEDIMIENTO DE OBTENCIÓN DE IMÁGENES MÉDICAS
Colimador tipo pinhole.
La imagen es invertida y el
tamaño dependiente dela
distancia al plano objeto.
Colimadores de múltiples
orificios paralelos, convergentes y divergentes
PROCEDIMIENTO DE OBTENCIÓN DE IMÁGENES MÉDICAS
Gammagrafía
SPECT
PET
Es la técnica mas simple.
Su funcionamiento es similar al de las radiografías, una sola imagen por volumen.
Varios tipos dependiendo de la zona: › Osea (tumores de hueso)
› Pulmonar (trombos en las arterias pulmonares)
› Tiroidea (nódulos en la tiroides)
› Renal (función de los riñones)
Gammagrafía de un
adenoma suprarrenal
causante de hipertensión
arterial secundaria
Renograma isotópico de un
paciente con HTA secundaria,
que muestra una clara atrofia
renal derecha. La pequeña
cantidad de contraste isotópico
que se observa ha llegado por
vía del pedículo suprarrenal.
Gammacámara que puede realizar movimientos de rotación alrededor del cuerpo del paciente o anillo.
Imagen de la distribución del trazador en 3D utilizando la combinación de imágenes obtenidas desde diversas orientaciones. Pueden obtenerse imágenes de cortes axiales, sagitales, coronales.
Mediante los algoritmos de retroproyección, similares a los TC, se puede reconstruir la imagen.
Ejemplo de un escáner de SPECT
Detectores de
radiación
Positrón
fotón
fotón
Detección de positrones mediante dos gammacámaras
Tipos de cámaras PET:
a) un par
b) un anillo hexagonal giratorio alrededor del paciente
c) Anillo circular que rodea al paciente
PET generates images depicting the
distributions of positron-emitting nuclides in
patients
In the typical scanner, several rings of
detectors surround the patient
PET scanners use annihilation coincidence
detection (ACD) instead of collimation to
obtain projections of the activity distribution
in the subject
Positrons emitted in matter lose most of their
kinetic energy by causing ionization and
excitation
When a positron has lost most of its kinetic
energy, it interacts with an electron by
annihilation
The entire mass of the electron-positron pair
is converted into two 511-keV photons,
which are emitted in nearly opposite
directions
If both annihilation photons interact with
detectors, the annihilation occurred close
to the line connecting the two interactions
Circuitry within the scanner identifies
interactions occurring at nearly the same
time, a process called annihilation
coincidence detection
Circuitry of the scanner then determines the
line in space connecting the locations of
the two detector interactions
ACD establishes the trajectories of the
detected photons, a function performed by
collimation in SPECT systems
Much less wasteful of photons than
collimation
Avoids degradation of spatial resolution
with distance from the detector that occurs
when collimation is used to form projection
images
A true coincidence is the simultaneous interaction of emissions resulting from a single nuclear transformation
A random coincidence, which mimics a true coincidence, occurs when emissions from different nuclear transformations interact simultaneously with the detectors
A scatter coincidence occurs when one or both of the photons from a single annihilation are scattered, but both are detected
Scintillation crystals coupled to PMTs are
used as detectors in PET
Signals from PMTs are processed in pulse
mode to create signals identifying the
position, deposited energy, and time of
each interaction
Energy signal is used for energy
discrimination to reduce mispositioned
events due to scatter and the time signal is
used for coincidence detection
Early PET scanners coupled each
scintillation crystal to a single PMT
› Size of individual crystal largely determined
spatial resolution of the system
Modern designs couple larger crystals to
more than one PMT
Relative magnitudes of the signals from the
PMTs coupled to a single crystal used to
determine the position of the interaction in
the crystal
Material must emit light very promptly to
permit true coincident interactions to be
distinguished from random coincidences
and to minimize dead-time count losses
at high interaction rates
Must have high linear attenuation
coefficient for 511-keV photons in order
to maximize counting efficiency
Most PET systems use crystals of bismuth germanate (Bi4Ge3O12, abbreviated BGO) › Light output 12% to 14% that of NaI(Tl), but
greater density and average atomic number give it higher efficiency at detecting 511-keV photons
Other inorganic scintillators being investigated: lutetium oxyorthosilicate and gadolinium oxyorthosilicate – faster light emission than BGO produces better performance at high interaction rates
Energy signals sent to energy discrimination
circuits which can reject events in which
the deposited energy differs significantly
from 511 keV to reduce effect of photon
scatter in patient
Energy window may be adjusted to include
part of the Compton continuum, increasing
sensitivity but also increasing the number of
scattered photons detected
Time signals of interactions not rejected by the energy discrimination circuits are used for coincidence detection
When a coincidence is detected, the circuitry or computer of the scanner determines a line in space connecting the two interactions › PET system collects data for all projections
simultaneously
Projection data used to produce transverse images of the radionuclide distribution as in x-ray CT or SPECT
In 2D (slice) data acquisition, coincidences are detected and recorded within each detector ring or small groups of adjacent detector rings
PET scanners designed for 2D data acquisition have thin annular collimators (typically tungsten) to prevent most radiation emitted by activity outside a transaxial slice from reaching the detector ring for that slice
Fraction of scatter coincidences reduced because of the geometry
Coincidences within one or more pairs of
adjacent detector rings may be added to
improve sensitivity
Data from each pair of detector rings are
added to that of the slice midway between
the two rings
Increasing the number of adjacent rings
used in 2D acquisition reduces the axial
spatial resolution
In 3D (volume) data acquisition, axial
collimators are not used and
coincidences are detected between
many or all detector rings
Greatly increases the number of true
coincidences detected; may permit
smaller activities to be administered to
patients
For the same administered activity, the increased interaction rate increases random coincidence fraction and dead-time count losses › 3D acquisition may require less activity to be
administered
Scatter coincidence fraction is much larger and number of interactions from activity outside the FOV is increased › Activity outside the FOV causes few true
coincidences, but increases rate of random coincidences and dead-time count losses
3D acquisition may be most useful in low-
scatter studies, such as pediatric and
brain studies
Some PET systems are equipped with
retractable axial collimators, permitting
them to perform 2D or 3D acquisition
For 2D data acquisition, image reconstruction methods are similar to SPECT
For 3D data acquisition, special 3D analytic or iterative reconstruction techniques are required
In PET, the correction for nonuniform attenuation can be applied to the projection data before reconstruction; in SPECT, the correction for nonuniform attenuation is intertwined with and complicates the reconstruction process
Whole-body PET systems achieve a spatial
resolution slightly better than 5 mm FWHM in the center of the detector ring
Spatial resolution limited by:
a) intrinsic spatial resolution of detectors
b) distance traveled by positrons before annihilation
c) the fact that annihilation photons are not emitted in
exactly opposite directions from each other
Intrinsic resolution of detectors most significant
Spatial resolution of PET is best in the center
of the detector ring and decreases slightly
with distance from the center
This occurs because of detector thickness
and inability to determine the depth in the
crystal where an interaction occurs
Uncertainty in depth of interaction causes
uncertainty in the line of response for
annihilation photons that strike the
detectors obliquely
Distance traveled by positron before annihilation also degrades the spatial resolution
Distance is determined by maximal positron energy of the radionuclide and density of the tissue
Radionuclide that emits lower energy positrons yields superior resolution
Activity in denser tissue yields higher resolution than activity in less dense tissue
Although positrons lose nearly all of their
momentum before annihilation, the positron
and electron possess some residual
momentum when they annihilate
Conservation of momentum predicts that
the resultant photons will not be emitted in
exactly opposite directions
This causes a small loss of resolution, which
increases with the diameter of the detector
ring
Point source of positron-emitting radionuclide in air
midway between two identical detectors
True coincidence rate is
where A is the activity of the source, G is the
geometric efficiency of either detector, and is the
intrinsic efficiency of either detector
Because the rate of true coincidences detected is
proportional to the square of the intrinsic efficiency,
maximizing the intrinsic efficiency is very important
22 AGRT
Differs in PET from SPECT, because both
annihilation photons must escape the
patient to cause a coincidence event to
be registered
Probability of both photons escaping the
patient without interaction is the product
of the probabilities of each escaping:
) ) ) dxdx eee
For a 20-cm path in soft tissue, the chance
of both annihilation photons of a pair
escaping the tissue without interacting is
about 15%
Attenuation causes a loss of information
and, because the loss is not the same for all
lines of response, causes artifacts in the
reconstructed transverse images
Loss of information also contributes to
statistical noise in the images
Some PET systems provide one or more retractable positron-emitting sources to measure the transmission of annihilation photons through the patient › Gamma-ray emitting source (Cs-137) may be
used
Sources revolve around the patient so attenuation is measured along all lines of response through the patient
Attenuation correction cannot compensate for increased statistical noise; increases imaging time
SPECT with high-energy collimators or
multihead SPECT cameras with
coincidence detection capability
› Less acceptable for brain imaging or evaluation
and staging of neoplasms
Dedicated PET systems that are less
expensive than those with full rings of BGO
detectors, but which provide better
coincidence detection sensitivity than
double-head scintillation cameras
PET scanner more efficient than scintillation camera due to use of annihilation coincidence detection instead of collimation; also yields superior spatial resolution
Spatial resolution in SPECT deteriorates from edge toward center; PET is relatively constant across transaxial image, best at center
Attenuation less severe in SPECT; accurate attenuation correction possible in PET (with transmission source)
Cost: SPECT ~US$500,000; PET ~US$1M - $2M
Main factors limiting availability of PET are
the relatively high cost of a dedicated PET
scanner and, in many areas, the lack of
local sources of F-18 FDG
Multihead SPECT cameras with coincidence
circuitry and SPECT cameras with high-
energy collimators provide less expensive,
although less accurate, alternatives for
imaging FDG
PET enables physicians to assess chemical or physiological changes
related to metabolism. Since the origins of many diseases are
biochemical in nature, these functional changes often predate or exceed
structural change in tissue or organs. PET imaging utilizes a variety of
radiopharmaceuticals, called "tracers," to obtain images. PET tracers
mimic the natural sugars, water, proteins, and oxygen found in our
bodies. These tracers are injected into a patient and collect in various
tissues and organs. The PET system takes a time-exposure of the tracer
and generates a "photo" of cellular biological activities. PET images
can be used to measure many processes, including sugar metabolism,
blood flow and perfusion, receptor-ligand binding rates, oxygen
utilization and a long list of other vital physiological activities.
PET scanning uses artificial
radioactive tracers and
radionuclides. Their lifetime is
usually rather short, thus they
need to be produced on site.
Some examples of such materials are:
Radionuclide Half life Application Carbon-11 20.3 min Positron emitter for metabolism studies
Copper –64 12.8 hours clinical diagnostic agent for cancer and
metabolic disorder
Iodine –122 3.76 min Positron emitter for blood flow study
Iodine –131 8.1 days Diagnose thyroid disorders including cancer
Iron - 52 8.2 hours Iron tracer for PET bone marrow imaging
Nitrogen – 13 9.9 min Positron emitter used as 13NH for heart
perfusion studies
Strontium – 85 64 days Study of bone formation metabolism
Oxygen – 15 123 sec Positron emitter used for blood flow
Technetium – 99m 6 hours The most widely used radiopharmaceutical
In nuclear medicine
PET has a million fold sensitivity advantage over MRI in tracer study
and its chemical specificity, PET is used to study neuroreceptors in
the brain and other body tissues. It is efficient in the nanomolar range
where much of the receptor proteins in the body. Clinical studies
include tumors of the brain, breast, lung, lower GI tract. Additional
study of Alzheimer’s disease, Parkinson’s disease, epilepsy and
coronary artery disease affecting heart muscle metabolism and flow.
PET studies has immeasurably added to the understanding of oxygen
utilization and metabolic changes that accompany disease.
PET imaging starts with the injection of metabolically active tracer – a biologic
molecule that carries with it a positron emitting isotope. Over a few minutes the
isotope accumulates in an area of the body for which the molecule has an affinity.
i.e. glucose labeled with 11C or glucose analogue labeled with 18F, accumulates in the
brain or tumors, where glucose is used as the primary source of energy. The
radioactive nuclei then decay by positron emission. In positron (positive electron) ,
a nuclear proton changes into a positive electron and a neutron. The atom maintains
its atomic mass but decreases its atomic number by 1. The ejected positron combines
with an electron almost instantaneously, and these 2 particles undergo the process of
annihilation. The energy associated with the masses of the positron and electron
particles is 12.022MeV in accordance with E=MC2 . This energy is divided equally
between 2 photons which fly away from one another at 1800 angle. Each photon has
an energy of 511 keV. These high energy gamma rays emerge from the body in
opposite directions and recorded simultaneously by pair of detectors.
The annihilation event that gave rise to them must have occurred somewhere
along the line connecting the detectors. Of course if one of the photons is scattered,
then the line of coincidence will be incorrect. After 100,000 or more annihilation
events are detected, the distribution of the positron-emitting tracer is calculated by
tomographic reconstruction procedures. PET reconstructs a 2 dimensional image
from the one dimensional projections seen at different angles. 3-D reconstructions
can be done using 2D projections from multiple angles.
Tungsten
septum
Scintillator
Lead
shield
P P
N
+
-
Positron annihilation
photons (1800
0.250)
Tagged
metabolic
activity
11C nucleus
Detector crystal width
Anger logic
Photon noncolinarity
Positron range
Reconstruction algorithm
Acquisition
Calibration data
Correction data
Reconstruction
Sinogram
Counts/ray
Image
SA reconstructed slices
• Blood volumes
• Oxygen consumption
• Perfusion
• Glucose consumption
CENTELLEADOR
FOTOMULTIPLICADOR
ELECTRÓNICA
2 RAYOS γ
COLINEALES
RADIOISÓTOPOS
β+ DE
VIDA CORTA
CICLOTRÓN
Radioisótopos
β+
Reconstrucción
de la
Imagen
Radioisótopo
+
Trazador
Inyección
al
Paciente
Decaimiento β+
y Aniquilación (2γ)
Detección
de
Coincidencias
IMAGEN FUNCIONAL:
DISTRIBUCIÓN DEL TRAZADOR
EN EL ORGANISMO
APLICACIONES:
-DETECCIÓN DE TUMORES
- FUNCIÓN CEREBRAL
-EFICIENCIA DEL DETECTOR
- SENSIBILIDAD DEL SISTEMA
- RESOLUCIÓN TEMPORAL
- RITMO DE RECUENTO
- RESOLUCIÓN ESPACIAL
Punto
Paralelepípedo
Esfera
¿Dentro
de Esfera?
Rayo
Θ,φ
Intersección
Detectores-Rayo
Detector
¿Dentro
de
planos?
Numeración
Detectores
Guardar datos
n veces
No
Sí
No
Sí
PROGRAMA DE
SIMULACIÓN
MÉTODO
MONTECARLO
Datos
DETECTOR IDEAL
2γ COLINEALES LOR
EJE X
EJE Y
EJE X EJE Y
π/3
π/3
x
φ
y
F1
F2
υx
υy
υxr
υxr
EQUIVALENTES
dxpedxWedyxf r
xi
rxx
xi
x
rrx
rr
rrx
r
0
22),()(),(
f(x,y)
φ
xr
0
0
xr
φ
dxdyxysenxyxfxP rr )cos(),(),(
Transformada de Radon
PROYECCIÓN RETROPROYECCIÓN
Δφ
Δυxr
Sobremuestreo en el
origen de frecuencias
υx
υy
υ 0
Filtro rampa
Ventana Hamming
Tipos de Filtros
)2cos( rN x
p(xr,φ)
xr xr
p·cos
φ
υxr
xr
(x, z)
1
2
2
3
4
5
5
4
3
1
2
dxpedxWedyxf r
xi
rxx
xi
x
rrx
rr
rrx
r
0
22),()(),(
xr = x·cosφ +y·senφ
6 mm 4 mm 3 mm
FWHM ≈ 3 mm
φ (rad)
xr (cm)
CORREGIDA
POR
NORMALIZACIÓN
φ (rad)
xr (cm)
CORREGIDA
POR
NORMALIZACIÓN
CONCLUSIONES:
- Reconstrucción de Imágenes con FBP en
Modo 2D.
- Estudios Realizados: Resolución,
Normalización, Filtros.
- Simulación de la Emisión y Detección de
Gammas en P.E.T.
Imágenes PET de un cerebro activo en varios estados, tras inyección intravenosa de 18F, con deoxy-glucosa. (de Shung-92)
Low Pet Scan of Patient.
The Positron Emission Tomography
Lab at Mount Sinai Medical
Center is located in New York City.
We are dedicated to the study of
Alzheimers, Schizophrenia and
general questions regarding how
the brain changes with age. This
research is accomplished through
the co-registration of PET and MRI
modalities. We have developed
software in order to better aid in
this research
http://neurosurgery.mgh.harvard.edu/pet-hp.htm
Parkinson's Disease
http://neurosurgery.mgh.harvard.edu/pet-hp.htm
Huntington's disease
Sitio caliente: sala de preparación de
radiofármacos
Sala de pacientes
Sala de exploraciones
Sala de almacenamiento de residuos
radiactivos
Equipo humano: Especialista y técnico