Physics Flashcards
osmolarity vs osmolality
Osmolarity = number of osmotically active particles in 1 litre of solution
Osmolality = number of osmotically active particles in 1 kg solvent
Osmolality used as temperature alters volume not mass
tonicity is the osmotic properties of a fluid in relation to a membrane
Measuring osmolarity and osmolality
Osmolarity is calculated (difficult to measure)
glucose + urea + 2 x Na
Osmolality is measured by osmometer - depression of freezing point of water (higher osmolality, lower freezing point)
Osmolar gap = difference between two i.e. unmeasured osmoles (methanol, ethanol, ethylene glycol)
Osmole
unit of measurement describing number of moles of a compound that contribute to osmotic pressure and that would depress freezing point by 1.86 K
Colligative properties
properties of a solution which are affected by osmolarity
- depression of freezing point (1.86K per osmole)
- reduction of vapour pressure (less space for solvent on surface)
- increase boiling point
- increase osmotic pressure
Clinical applications of osmolality
- SIADH - reduced osmolality
- DI - increased osmolality
- TURP syndrome - reduced osmolality
- Hyperosmolar states e.g. HSS
Transducer
Converts one form of energy into another form
Active - generate electric current directly in response to stimulation e.g. piezoelectric
Passive - external power source - change in resistance etc converted to equivalent electric current
Ultrasound
Sound waves at frequency above human hearing > 20KHz
Medical USS 2.5 - 15 MHz
Principles
- Array of piezoelectric crystals
- USS waves generated by piezoelectric effect - electric voltage across piezoelectric crystal makes it vibrate
- Frequency of vibration corresponds to frequency of current
- USS travels through tissue and reflected at tissue interfaces - when there is a change in density e.g. boundaries between tissues
- reflection transduced into display
- strong reflections from solid structures are white
- weaker reflections grey
- absence of reflections e.g. blood black
velocity of sound waves in tissue is 1540m/s
Ultrasound modes
A-mode - transducer scans a line through the body, echoes plotted on screen as function of depth
B- mode - brightness - linear array of transducers produces beam of USS in a plane, reflections viewed as two dimensional image
M-mode - motion - rapid sequence of B mode follow each other in sequence - examination of moving structure
Doppler mode - Doppler effect - increase in frequency of signal when the source of signal is approaching the observer and decrease in frequencyy as sound source moves away.
change in frequency i.e. increase in frequency of RBC moving towards and decrease in frequency of RBC moving away = doppler shift, can be used to calculate velocity
v = Fd x 1540 / 2 x emitted frequency x angle
USS image quality
Not all of the USS beam is reflected
- absorption - tissue absorbs acoustic energy
- reflection - only some of acoustic energy is reflected directly back to the probe
- refraction - deflected acoustic energy at difference angle
- divergence - spread out of energy
Improved by
- amplitude - increasing strength of the use wave increases reflected acoustic energy
- frequency - higher frequency better resolution but worse penetration (linear = 10MHz, curvilinear = 5MHz)
- Gain - screen brightness
How is blood pressure measured
Non-invasively
- Mercury sphigmanometer
- Oscillometery
Invasively
- Arterial line
Non-invasive non automated BP measurement
Sphygmomanometer
- Centre of cuff over brachial artery
- Width 20% greater than diameter of arm
- Aneroid gauge or column of mercury
- Cuff inflated above systolic, released 2-3mmhg/sec
- Auscultation over brachial artery for Korotkoff sounds
1 = blood flow in artery first appears
2 = muffling
3 = rising in volume
4 = fall
5 = absence
Oscillometric
- cuff / aneroid gauge
- cuff deflated below systolic, needle on aneroid gauge oscillates
- pressure at onset of oscillation = systolic
- max oscillations = mean
- decreasing oscillation = diastolic
Von-Recklinghausen oscillotonometer
- two overlapping cuffs on upper arm
- proximal = sphygmomanometer
- distal = measure oscillation
Non-invasive automated BP measurement
DINAMAP - device for indirect non-invasive automated MAP
- similar to von-recklingausen
- single cuff, pressure transducer, microprocessor, display
- pressure transducers measured pressure and oscillations
- onset of oscillations = systolic, max = MAP, diastolic derived
- reliable but need 2 min intervals, arrhythmias unreliable, fail to record if < 50
Penaz
- LED through small finger cuff
- light detected other side
- amount of light absorbed by tissues proportional to volume and therefore BP
Invasive arterial blood pressure measurement
gold standard, beat to beat
intra-arterial cannula - short, stiff
column of fluid pressurised to 300mmHg with 4ml.hr flush
transducer - mechanical energy (movement of diaphragm) to electric
electric signal amplified and processed
- saline column in contact with diaphragm and 4 strain gauges
- tension of strain gauges alter as diaphragm moves
- change in tension changes electrical resistance, measured by wheatsonte bridge
Complications of arterial cannulation
Early
- haematoma
ischaema (vasospasm)
Late
- ischaemia (thrombosis
- infection
Any time
- exsanguiantion
- intra-arterial injection
Damping and resonance
resonance - every system has resonant frequency - system will ossilate if left alone. if frequency coincides with frequency of arterial waveform - increased amplitude and distortion
Damping - inherent tendency of system to resist oscillations
- optimal 0.67
- critical 1.0
- over damped - waveform stops quickly due to compliant tubing, air bubble > 1
- underdamped - resonance causes the trace to oscillate and overshoot
Information from arterial waveform
- slope of upstroke - myocardial contractility
- downslope - SVR. steep downstroke with low dicrotic notch indicates low SVR. high dicrotic notch implies high SVR
- respiratory swing in IPPV - hypovolaemia
Pulse contour analysis
SV proportional to AUC systolic portion of curve
CO = SV x HR
SVV - min SV divided by max. > 15% suggests fluid responsive
Cardiac output measurement
Clinical
Non-invasive - TT electrical impendence
Minimally invasive - ODM PICCO
Invasive - PAC
PAFC
Fick principle - uptake of substance by organ is equal to amount entering and leaving
PAC indirectly measures CO by thermodilution
- cold saline 10ml proximal lumen
- change in temperature measured by thermistor in tip
- rate of change in temperature reflective of CO and calculated by Stewart-hamilton equation (AUC log change in temp over time)
Pulse contour analysis
Arterial pressure waveform morphology
- slope up - contractility
- AUC up to dicrotic notch - SV
- downstroke / position dicrotic notch - SVR
Computer algorithms to calculate CO
- SVV - change in CO over respiratory cycle
- calibrated - PICCO - CVC / specialised art line measure transpulmonary thermodilution. LIDCO uses lithium. Stewart-Hamilton eq
Uncalibrated use height weight nomograms e.g. lid rapid
Oesophageal doppler
USS probe at 45 degrees to aorta
USS beam reflected at different frequency when red blood cells are in motion
- measure blood velocity multiplied by CSA aorta
- velocity plotted against time
waveform
- contractility - peak velocity
- preload- flow time
- SV - stroke distance area under the velocity / time curve
Thoracic electrical bioimpedence
Resistance to alternating current flowing through the body
electrodes neck / chest. resistance to current flowing from outer to inner electrodes measured.
Bioimpedence is related to water content of the thorax
nomograms to estimate volume of electrically participating tissue
impedance changes throughout the cardiac cycle as the volume of blood in the thorax changes - microprocessor analyses and estimates SV
Sensitive to movement, diathermy, arrhythmias
Electrical current
Rate of flow of electrons past a point in a conductor
Measured in Amperes (SI unit)
- 1 coulomb of charge passing a point in one second.