The physics US and MRI. Prof. Peter Bogner

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1 The physics US and MRI Prof. Peter Bogner

2 Sound waves mechanical disturbance, a pressure wave moves along longitudinal wave compression rarefaction zones c = nl, (c: velocity, n: frequency, l: wavelength diagnostic range: MHz

3 Ultrasound Production Transducer produces ultrasound pulses (transmit 1% of the time) These elements convert electrical energy into a mechanical ultrasound wave Reflected echoes return to the scanhead which converts the ultrasound wave into an electrical signal

4 Characteristics of ultrasound velocity 1540 m/s in soft tissues frequency depends on trancducer wavelength 2.25 MHz = 0,6 micron 5.0 MHz = 0,31 micron 10 MHz = 0,15 micron amplitude intensity of ultrasound

5 Frequency vs. Resolution The frequency also affects the QUALITY of the ultrasound image The HIGHER the frequency, the BETTER the resolution The LOWER the frequency, the LESS the resolution A 12 MHz transducer has very good resolution, but cannot penetrate very deep into the body A 3 MHz transducer can penetrate deep into the body, but the resolution is not as good as the 12 MHz Low Frequency 3 MHz High Frequency 12 MHz

6 Image Formation Electrical signal produces dots on the screen Brightness of the dots is proportional to the strength of the returning echoes Location of the dots is determined by travel time. The velocity in tissue is assumed constant at 1540m/sec Distance = Velocity Time

7 Ultrasound velocity Relaitvely low in gases higher in solids Velocity changes with the wavelength, frequency remains approx. constant c = E/ (E ~ elasticity, ~ density) Variation in velocity artifacts

8 Interactions of Ultrasound with Tissue Reflection Refraction Transmission Attenuation

9 Interactions of Ultrasound with Tissue Reflection The ultrasound reflects off tissue and returns to the transducer, the amount of reflection depends on differences in acoustic impedance acoustic impedance ~ density + elasticity (similarly to velocity) The ultrasound image is formed from reflected echoes transducer

10 Interactions of Ultrasound with Tissue Transmission Some of the ultrasound waves continue deeper into the body These waves will reflect from deeper tissue structures transducer

11 Interactions of Ultrasound with Tissue Attenuation Defined - the deeper the wave travels in the body, the weaker it becomes -3 processes: reflection, absorption, refraction Air (lung)> bone > muscle > soft tissue >blood > water

12

13 Reflected Echo s Strong Reflections = White dots Diaphragm, tendons, bone Hyperechoic

14 Reflected Echo s Weaker Reflections = Grey dots Most solid organs, thick fluid isoechoic

15 Reflected Echo s No Reflections = Black dots Fluid within a cyst, urine, blood Hypoechoic or echofree

16

17 Transducer

18 What determines how far ultrasound waves can travel? The FREQUENCY of the transducer The HIGHER the frequency, the LESS it can penetrate The LOWER the frequency, the DEEPER it can penetrate Attenuation is directly related to frequency

19 Ultrasound Beam Profile Beam comes out as a slice Beam Profile Approx. 1 mm thick Depth displayed user controlled Image produced is 2D tomographic slice assumes no thickness You control the aim 1mm

20 Accomplishing this goal depends upon... Resolving capability of the system axial/lateral resolution spatial resolution contrast resolution temporal resolution Processing Power ability to capture, preserve and display the information

21 Types of Resolution Temporal Resolution the ability to accurately locate the position of moving structures at particular instants in time also known as frame rate

22 Types of Resolution Contrast Resolution the ability to resolve two adjacent objects of similar intensity/reflective properties as separate objects - dependent on the dynamic range

23 Presentation modes A(mplitude) B(rightness) M(otion) doppler A B

24 Presentation modes M doppler

25 MRI - magnetic resonance imaging Sir Peter Mansfield Paul C. Lauterbur The Nobel Prize in Medicine 2003

26 Damadian R Tumor detection by nuclear magnetic resonance. Science 1971, 171:

27

28 Hydrogen without magnetic field Normally, spins are randomly oriented No net magnetization (M=0)

29 Hydrogen in magnetic field Two possible orientations Paralell: lower-energy state Anti-paralell: higher-energy state Natural systems tend to have minimal energy Thermal agitation : only small imbalance

30 Hydrogen in magnetic field At 1.5 T only 1 spin in a contribute to the net magnetization (M) M

31

32 Larmor equation w=gxb 0

33 Excitation

34 Signal detection

35 Signal detection

36 Relaxation in z direction: T1

37 Relaxation in the x-y plane: T2

38 spin echo (SE) pulse sequence

39 sequence parameters TR 90º TE TR: time to repeat TE: time to echo

40 Basis of imaging : spatial localization

41 Gradient magnetic field Magnetic field gradients are used to change the strength of the main magnetic field (B0) Different spatial locations become associated with different precession frequencies

42 Spatial encoding It is done using magnetic gradients Slice selection - z Frequency encoding - x Phase encoding - y

43 Slice selection Based on Larmour equation: ω 0 =γb 0 The central frequency of RF pulse determines the particular location excited Different slice positions are achieved by changing the central frequency Hydrogen nuclei located outside the slice plane are not excited, they will not emit a signal

44 Frequency encoding It causes range of Larmor frequencies to exist in the direction in which it is applied

45 Frequency encoding Fourier transform to separate the different frequencies out after the signal detection

46 Phase encoding Protons located at different positions in the phase encoding direction experience different amounts of phase shift. Repeating the signal detection multiple times with different amplitude of phase-encoding gradient.

47 Review: Image Formation Fourier transform k y k x k-space image space Data gathered in k-space (Fourier domain of image) Gradients change position in k-space during data acquisition (location in k-space is integral of gradients) Image is Fourier transform of acquired data

48 The timing of spin echo sequence

49 Magnet types in MRI In Permanent magnets the magnetic field is always there and always at full strength (<0,5T). Resistive magnets are made from many coils of wire wrapped around a cylinder through which an electric current is passed. This generates a magnetic field. When the electricity is shut off, the magnetic field dies. Superconducting magnets are somewhat similar to resistive magnets - coils of wire with a passing electrical current create the magnetic field. The important difference is that in a superconducting magnet the wire is continually bathed in liquid helium. Always on at full strength.

50

51

52 MR safety!

53 MR safety!

54 Coils

55 MR contrast, methods T1W pre- and post-contrast T2W T1/T2W mixed Fat or water sturation (pl. FLAIR, STIR, Dixon ) Diffusion weighted (DWI, DTI) Susceptibility weighted T2* (SWI, fmri) Flow-sensitive MR angiography (TOF, PC, 3D CE) in vivo spectroscopy

56 molecular basis of MRI tissue contrast 1. water content Relaxation rate is directly proportional to water content 2. restricted water movement Originates from the interaction of water and macromolecules. This phenomenon is common in pathologic tissues. 3. macromolecular motion It also influences water motion. Other parameters might also be important, like ph, ion concentration, polimerisation of macromolecules, etc. 4. lipid content Hidrophobic lipids membranes 5. paramagnetic ions Primarily paramagnetic iron; contrast agents..

57 T1 weighted

58 T2 weighted

59 FLAIR & T2 weighted

60 Myelinisation T1 weighted

61 T2 weighted submilimeter slice thickness

62 Pre- and postcontrast T1 weighted Note the metallic artifact in the mouth!

63 T2 weighted and DWI

64 Inversion Recovery TR = 2000 ms TI (ms)

65 1.5T vs. 3T

66

67 fat suppression

68 Late enhancement method myocardial infarction

69 MR-guided neurosurgery

70 Fetal imaging

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