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131 Cards in this Set

  • Front
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E = hv = hc/λ
E=photon's energy
h=Planck constant
v = frequency of radiation
λ= wavelength of radiation
c=velocity of propagation of light in vacuum (3x108 m/s)
spectrophotometry
E = ΔE*el + ΔE*v + ΔE*r
E= energy of absorbed photon
ΔEel/ΔEv/ΔEr = difference in electronic/vibrational/rotational energy levels
spectrophotometry
I*t = I*0 e^(-kd)
Lambert Law
I*t= intensity of transmitted beam
I*0 = intensity of incident beam
d = path length
k= λ-dependent absorption coefficient
spectrophotometry
T = I*t / I*0
T = transmittance
I*t= intensity of transmitted beam
I*0 = intensity of incident beam
spectrophotometry
A = - logT
A = absorbance
T = transmittance
spectrophotometry
A = ε*λ dc
Beer Law
A = absorbance
ε*λ = absorptivity
d = path length
c = concentration of absorbing species
spectrophotometry
T=10^(-ε*λ dc)
Beer-Lambert Law
T= transmittance
ε*λ = absorptivity
d = path length
c = concentration of absorbing species
spectrophotometry
Tan α = n
n= refractive index of reflecting surface
α = brewster angle (of incidence)
polarimetry
[α]*λ = φ / l c
φ = rotation angle
[α]*λ = specific rotation
l = path length
c = concentration
polarimetry
optical purity = [α]*mixture / [α]*pure component x 100%
[α]*mixture = specific rotation of a mixture
[α]*pure component = specific rotation of pure component
polarimetry
I= I*0 (cosα)^2
Malus's Law
I = intensity of transmitted beam
I*0 = incident beam (on polarizer)
α = angle b/n plane of polarization and transmission axis of polarizer
polarimetry
hv = E*K + E*B
hv = photon's energy
E*K = kinetic energy of ejected electron
E*B = binding energy of electron
attenuation of electro. radiation
hv = E*K + hv'
hv = photon's energy
E*K = kinetic energy of ejected electron
hv' = energy of scattered photon
attenuation of electro. radiation
hv = (E*K^+) + (m*op)c^2 + (E*K^-) + (m*oe)c^2
(E*K^+) = kinetic energy of positron
(m*op) = rest mass of positron
(E*K^-) = kinetic energy of electron
(m*oe) = rest mass of electron
c = speed of light in vacuum
attenuation of electro. radiation
I = I*0 e^(-μx)
Lambert Law
I = intensity of transmitted beam
I*0 = intensity of incident beam
μ = linear attenuation coefficient (1/m)
x = absorber thickness
attenuation of electro. radiation
μ*m = μ / d
μ*m = mass attenuation coefficient (m^2/kg)
μ = linear attenuation coefficient (1/m)
d= absorber density
attenuation of electro. radiation
I = I*0 e^(-μ*m dx)
Lambert Law
I = intensity of transmitted beam
I*0 = intensity of incident beam
μ*m = mass attenuation coefficient (m^2/kg)
d= absorber density
x = absorber thickness
attenuation of electro. radiation
I*0/2= I*0 e^(-μ HVL)
HVL = half value layer, absorber thickness that reduces I*0 to half
I*0 = intensity of incident beam
μ = linear attenuation coefficient (1/m)
attenuation of electro. radiation
HVL = ln2/μ
HVL = half value layer
μ = linear attenuation coefficient (1/m)
attenuation of electro. radiation
a = ΔN/Δt
a = counting rate
ΔN = # of pulses
Δt = unit time
attenuation of electro. radiation
a*x = a*0 e^(-μx)
Lambert Law
a*x = counting rate for absorber thickness x
a*0 = counting rate for no absorber
μ = linear attenuation coefficient (1/m)
x = absorber thickness
attenuation of electro. radiation
ln a*x = ln a*0 - μx
a*x = counting rate for absorber thickness x
a*0 = counting rate for no absorber
μ = linear attenuation coefficient (1/m)
x = absorber thickness
attenuation of electro. radiation
F = η S Δv/Δx
F = force needed to maintain a uniform motion of plate
η = viscosity
S = surface area of fluid layer
Δv = diff. in velocity
Δx = diff. in distance b/n 2 fluid layers
Δv/Δx = velocity gradient/rate of shear (1/s)
viscosity
τ = F / S
τ = shear stress
F = force needed to maintain a uniform motion of plate (constant Δv)
S = surface area of fluid layer
viscosity
τ = η Δv/Δx
τ = shear stress
η = viscosity
Δv = diff. in velocity
Δx = diff. in distance b/n 2 fluid layers
Δv/Δx = velocity gradient/rate of shear (1/s)
viscosity
η = F Δx / S Δv
F = force needed to maintain a uniform motion of plate
η = viscosity SI unit = Pa⋅s, kg/(m⋅s) or Poise
S = surface area of fluid layer
Δv = diff. in velocity
Δx = diff. in distance b/n 2 fluid layers
Δv/Δx = velocity gradient/rate of shear (1/s)
viscosity
F*S = 6 π r η v
Stokes Law
F*S = frictional (Stokes) force
r = radius of ball
η = viscosity
v = velocity of ball
viscosity
F*B + F*S = Q
F*B = buoyant force
F*S = Stokes force
Q = force of gravity
viscosity
4/3 π r^3 d*l g + 6π r η v = 4/3π r^3 dg
V=volume of ball (4/3π r^3), d=density of ball material
r= ball radius
g= acc. due to gravity
d*l=density of liquid
η = viscosity
v = velocity of ball
viscosity
η = (2r^2 g(d – d*l)) / (9v)
d=density of ball material
r= ball radius
g= acc. due to gravity
d*l=density of liquid
η = viscosity
v = velocity of ball
viscosity
η / η*0 = 1 +2.5 Φ
Einstein's formula
η / η*0 = relative viscosity
η = viscosity of solution of spherical molecules
η*0 = viscosity of pure solvent
Φ = volumic coefficient
viscosity of solutions
Φ = V*s / V*t
Φ = volumic coefficient
V*s = volume of particles of dissolved substance
V*t = total volume of solution
viscosity of solutions
V*s = n N*A v
V*s = volume of particles of dissolved substance
n = # of moles of substance
N*A = Avogadro's number (6.02x 10^23 1/mol)
v = volume of a single particle
viscosity of solutions
Φ = (c N*A v) / M
Φ = volumic coefficient
V*s = volume of particles of dissolved substance
n = # of moles of substance
N*A = Avogadro's number (6.02x 10^23 1/mol)
v = volume of a single particle
c = concentration of solution
M = molar mass
viscosity of solutions
η*s = (η / η*0 ) – 1
η*s = specific viscosity
η / η*0 = relative viscosity
viscosity of solutions
η*s = 2.5Φ
η*s = specific viscosity
Φ = volumic coefficient
viscosity of solutions
η*int = limc→0 (η*s / c)
η*int = intrinsic viscosity
η*s = specific viscosity
c = concentration of solution (tending to 0)
viscosity of solutions
η*int = 2.5 N*A v / M
η*int = intrinsic viscosity
N*A = Avogadro's number (6.02x 10^23 1/mol)
v = volume of a single particle
M = molar mass
viscosity of solutions
r = [(3M η*int ) / (10 π N*A)]1/3
r= radius of particle
η*int = intrinsic viscosity
N*A = Avogadro's number (6.02x 10^23 1/mol)
M = molar mass
viscosity of solutions
V = π R^4 t Δp / 8ηl
Hagen-Poiseuille Law
V = volume of fluid
η = viscosity
R = radius of tube
l = length of tube
Δp = pressure difference
t = time
viscosity of solutions
η / η*0 = td / t*0 d*0
η / η*0 = relative viscosity
d = density of solution
d*0 = density of water (reference solution)
t = time of flow of solution
t*0 = time of flow of water
viscosity of solutions
η = A e^(w*a/kT)
η = viscosity
w*a = energy of activation
k = Boltzmann constant
A = constant characteristic for a given fluid
T = absolute temperature
viscosity of solutions
j = Δm / Δt
j = flux j (kg/s)
Δm= amt. of substance which passes an imaginary surface
Δt = time
diffusion
Δm / Δt = –DS (Δc / Δx)
Fick’s first law of diffusion
Δm / Δt = flux j (kg/s)
Δc / Δx = concentration gradient
(kg/m^4)
D = diffusion coefficient (m^2/s)
S = surface area
diffusion
D = k T/ 6 π r η
Stokes-Einstein EQ
k – Boltzman’s constant
T – absolute temperature
r – molecular radius
η - viscosity of the medium
D = diffusion coefficient
diffusion
(Δx)^2 = 2Dt
Einstein-Smoluchowski EQ
Δx – avg displacement
t – time elapsed since molecule started diffusing
D – diffusion coefficient
diffusion
P = D / Δx
P = membrane permeability constant (m/s)
Δx – avg displacement
D – diffusion coefficient
diffusion
Δm/Δt = PS (c*b – c*a) = PSΔc
Δm/Δt = flux j
P = membrane permeability constant (m/s)
S = surface area
c*b - c*a = Δc = difference in concentration of 2 solutions
diffusion
C = 2Sa / VΔx
C= constant characterizing the measuring vessel
V – volume of solution
Δx – membrane thickness
Sa = active membrane area (the net area of all the membrane’s pores)
diffusion
c*a = ½ c*0 (1+e^(-CDt))
c*b = ½ c*0 (1–e^(-CDt))
c*a = c of more conc. solution
c*b = c of less conc. solution
diffusion
ln (c*0 / 2c*a – c*0) = CDt ln (c*0 / c*0 – 2c*b) = CDt
a = CD
c*0 = initial c of c*a
c*a = c of more conc. solution
c*b = c of less conc. solution
C = vessel constant
D = diffusion coefficient
t = time of diffusion
a = slope of line
diffusion
ΔV*e = ΔV*0 + RT lnc*i / zF
Nernst EQ
ΔV*e = electrode potential
R = universal gas constant (8.31 J/molK)
T = abs temp
z = ion valence
F = Faraday constant (9.65x104 C/mole)
c*i = conc. of metal ions in solution
ΔV*0 = standard electrode potential
EMF of concentration cell
ΔV*e = 0.250V + EMF
ΔV*e = electrode potential of electrode tested
EMF = electromotive force of cell formed by calomel and tested electrode
EMF of concentration cell
u = v / E
u = mobility
v = net ion transportation velocity of diffusing ions
E = intensity of electric field
EMF of concentration cell
ΔV*d = (u+ - u- / u+ + u-) (RT/zF) ln c*1/c*2
Henderson EQ
ΔV*d = diffusion potential
u+ = mobility of cations
u- = mobility of anions
R = universal gas constant (8.31 J/molK)
T = abs temp
z = ion valence
F = Faraday constant (9.65x104 C/mole)
c*1/c*2 = solutions of diff. concentrations
EMF of concentration cell
EMF = ΔV*e1 - ΔV*e2
EMF = EMF of concentration cell
ΔV*e1 = electrode potential of electrode immersed in sol of conc. c1
ΔV*e2 = electrode potential of electrode immersed in sol of conc. c2
EMF of concentration cell
EMF = (RT/zF) ln c*1/c*2
Nernst EQ for EMF of CC
EMF = EMF of concentration cell
R = universal gas constant (8.31 J/molK)
T = abs temp
z = ion valence
F = Faraday constant (9.65x104 C/mole)
c*1/c*2 = solutions of diff. concentrations
EMF of concentration cell
ΔV*d = EMF*t - EMF
ΔV*d = diffusion potential
EMF*t = EMF of cc w/ transference
EMF = EMF of cc w/out transference
EMF of concentration cell
P = Σp*i / V
P = polarization vector
pi = dipole moments
V = volume of polarized material
dispersion of e.r. of blood
P = q / S
P = polarization vector
q = charge
S = surface of material in electric field
dispersion of e.r. of blood
τ = 4π η r^3 / kT
τ = relaxation time
η = viscosity
r = molecular radius
k = Boltzmann constant
T = temperature
dispersion of e.r. of blood
K = R*(10^4) / R*(10^6)
K = polarization coefficient
R*(10^4) = resistance measured when f of flowing current is equal to 10^4 Hz
R*(10^6) = resistance measured when f of flowing current is equal to 10^6 Hz
dispersion of e.r. of blood
i = U/R
Ohm's Law
i = current (amperes)
U = electric potential difference (volts)
R = resistance (ohms)
hematocrit determination by maxwell method
R = ρ l /S
R = resistance (Ω)
ρ = electrical resistivity (Ωm)
l = length of conductor
S = cross sectional area of conductor
hematocrit determination by maxwell method
G = 1 / R
G = conductance (Siemens or 1/Ω)
R = resistance (Ω)
hematocrit determination by maxwell method
σ = 1/ρ
σ = electrical conductivity (S/m)
ρ = electrical resistivity (Ωm)
hematocrit determination by maxwell method
i = i*a + i*c = zenS(v*a +v*c)
i*c = cation current
i*a = anion current
z = ion valence
e = elementary charge
n = # of ions of each sign per unit volume
S = cross section area equal to electrode area
v*a/v*c = anion/cation transportation velocity
hematocrit determination by maxwell method
F*E = qE
F*E = electric force
q = ion charge
E = electric field
hematocrit determination by maxwell method
F*S = 6π r η v
Stokes Law
F*S = Stokes force
r = radius of molecule
η = viscosity
v = velocity of molecule
hematocrit determination by maxwell method
F*S = F*E
v = qE / 6π r η
F*E = electric force
q = ion charge
E = electric field
F*S = Stokes force
r = radius of molecule
η = viscosity
v = velocity of molecule
hematocrit determination by maxwell method
v = uE
v = transportation velocity
u = ion mobility
E = electric field
hematocrit determination by maxwell method
u*A = v*A / E
u*C = v*C / E
u*A = anion mobility
u*C = cation mobility
v*A = anion transportation velocity
v*C = cation transportation velocity
E = electric field
hematocrit determination by maxwell method
u = ze / 6 π r η
u = mobility
z = ion valence
e = elementary charge
ze = q = charge
r = radius of molecule
η = viscosity
hematocrit determination by maxwell method
σ = zen (u*A + u*c)
σ = electrical conductivity
z = ion valence
e = elementary charge
n = # of ions of each sign per unit volume
u*A = anion mobility
u*C = cation mobility
hematocrit determination by maxwell method
Z = (R^2 + (R*c)^2)^½
Z = impedance
R = resistance
R*c = capacitive reactance
hematocrit determination by maxwell method
R*c = 1/ωC
R*c = capacitive reactance
ω = angular frequency of current
C = capacitance
hematocrit determination by maxwell method
φ = V*e / V*t
φ = hematocrit
V*e = volume of erythrocytes
V*t = total volume of blood
hematocrit determination by maxwell method
φ = 2 (σ*p - σ) / (σ + 2 σ*p)
Maxwell's formula
φ = hematocrit
σ = conductivity of whole blood
σ*p = conductivity of plasma
hematocrit determination by maxwell method
σ = 1 / ρ = l / RS = C / R
σ = conductivity
ρ = resistivity
l = distance b/n electrodes
S = electrode surface area
C = l / S = measuring vessel constant
hematocrit determination by maxwell method
C = R σ*r
C = measuring vessel constant
R = resistance
σ*r = conductivity of reference solution
hematocrit determination by maxwell method
ΔV = (RT/zF) ln c*outside/c*inside
Nernst EQ
ΔV = electric potential difference
R = universal gas constant
z = ion valence
F = Faraday constant
T = absolute temperature
c = concentration of ions
action potential
ΔV = (RT/zF) ln (P*Na [Na]*out + P*K [K]*out + P*Cl [Cl]*in) / (P*Na [Na]*in + P*K [K]*in + P*Cl [Cl]*out )
Goldman EQ
ΔV = electric potential difference
R = universal gas constant
z = ion valence
F = Faraday constant
T = absolute temperature
P = membrane permeability for an ion
c = concentration of ions inside or outside
action potential
J = qt / S
J = stimulus strength
q = ion charge
S = membrane surface area
t = time
action potential
J = i / S
J = stimulus strength
i = ionic current
S = membrane surface area
action potential
log{Q} = 5.44 + 0.756 x log{m} ± 0.05
Kleiber EQ
Q = heat produced by individual in 24 hrs (BMR)
m = body mass
measurement of metabolic rate
Q = mC*s ΔT
Q = amt. of heat released by object
m = mass of object
C*s = specific heat
ΔT = diff. in temperature of water
measurement of metabolic rate
Q/t = V/t d C*s ΔT
Q/t = rate of heat loss (=MR)
V/t = rate of flow of water
d = density of water
C*s = specific heat
ΔT = diff. in temperature of water
measurement of metabolic rate
P= i^2 R
P = heater's power
i = intensity of current flowing in power compensation
R = resistance of heater
measurement of metabolic rate
Q*p =ΔH
Hess Law
Q*p = amt. of heat exchanged b/n a system in the environment (isobaric p = constant)
ΔH = change in enthalpy of the system
measurement of metabolic rate
Q*V = ΔU
Q*V = amt. of heat released in isovolumic rxn (v=constant)
ΔU = change in internal energy
measurement of metabolic rate
w = Q*C / V*(O2)
w = energy equivalent of oxygen
Q*C = amt. of heat released if unit volume of oxygen V*O2 is consumed
measurement of metabolic rate
RQ = V*(CO2) / V*(O2)
RQ = respiratory quotient
V*CO2 = volume of CO2 produced
V*O2 = volume of O2 consumed
measurement of metabolic rate
v = ΔV / t
v = rate of oxygen consumption
ΔV = volume of air consumed
t = time of experiment
measurement of metabolic rate
P= vw = (ΔV / t)(Q / V) = Q/t
P = power (MR) of animal
v = rate of oxygen consumption
ΔV = volume of air consumed
t = time of experiment
w = energy equivalent of oxygen
Q = amt. of heat released
V = volume of oxygen consumed
measurement of metabolic rate
F=kΔl
Hook's Law
F = force applied
k = spring constant
Δl = elongation
examinations of models of NSM
F=F*0 e^(-t/τ)
F = force decay
F*0 = initial applied force during stretching of model
τ = stress relaxation time, time req. for force F to reach 1/e of the initial value F*0
t = time
(Maxwell)
examinations of models of NSM
τ = η / E
τ = stress relaxation time
η = viscosity of dashpot
E = Young's modulus of spring
(Maxwell)
examinations of models of NSM
ln F = ln F*0 – t/τ
τ = 1/a
F = force decay
F*0 = initial applied force during stretching of model
τ = stress relaxation time, time req. for force F to reach 1/e of the initial value F*0
t = time
a = slope
(Maxwell)
examinations of models of NSM
Δl = v*c t
Δl = elongation
v*c = velocity of creep
t = time
(Maxwell)
examinations of models of NSM
Δl= Δl*max (1 – e^(-t/τ*r))
Δl = elongation
τ*r = retardation time
Δl*max = max elongation of model
t = time
(Kelvin-Voigt)
examinations of models of NSM
τ*r = η / E
τ*r = retardation time
η = viscosity of dashpot
E = Young's modulus of spring
(Kelvin-Voigt)
examinations of models of NSM
ln (1 - Δl/Δl*max) = - t/τ*r
τ*r = 1/a
τ*r = retardation time
Δl = elongation
Δl*max = max. elongation of model
t = time
a = slope
(Kelvin-Voigt)
examinations of models of NSM
D = 1/f
D = optical power (unit D = dioptre)
f = focal length
retinoscopy
D*s = D*1 + D*2 – dD*1D*2
D*s = optical power of optical system
D*1/D*2 = optical power of 2 lenses
d = distance b/n 2 lenses
retinoscopy
R=1/s*f
R = refractive error
s*f = distance of far point of accommodation
retinoscopy
R = D*cor.
R = refractive error
D*cor = optical power of corrective lens
retinoscopy
D*comp. = 1/l
D*comp. = optical power of compensative lens
l = distance b/n the patient's eye and examiner's eye
retinoscopy
D*cor. = D - D*comp.
D = optical power of lens that makes rapid filling of light in pupil
D*cor = optical power of corrective lens
D*comp. = optical power of compensative lens
retinoscopy
p*m = dcv*m
p*m = acoustic pressure amplitude (Pa)
d = density of medium
c = speed of wave propagating in medium
v*m = max speed of vibration of the medium molecules affected by acoustic wave
equal loudness curves
I = E/tS = P/S
I = sound intensity [I] = W/m2 (J/sm2)
E = energy carried by wave
S = surface area
t = time
P = E/t = wave power
equal loudness curves
I = (p*m)^2 / 2dc
I = sound intensity
p*m = acoustic pressure amplitude
d = density of medium
c – speed of wave propagating in medium
equal loudness curves
λ = c / f
λ = wavelength
f = frequency (Hz)
equal loudness curves
ΔI ∝ I
ΔI / I = constant
Weber-Fechner Law
ΔI = smallest noticeable difference in stimulus intensity
I = intensity of stimulus already acting
equal loudness curves
SIL = 10 log*10 I/I*0
SIL = sound intensity level (dB)
I = intensity of sound
I*0 = threshold of hearing 10^(-12) W/m2
equal loudness curves
SPL = 10 log*10 p/p*0
SPL = sound pressure level (dB)
p*0 = 20x10^(-6) Pa
equal loudness curves
P*a ∝ P*i ∝ U^2
P*a = power of acoustic wave emmitted by headphones
P*i = power of electric current supplying headphones
U = voltage supplied
equal loudness curves
L*p = 10 log P/P*0
L*p = 20 log U/U*0
L*p = electric power level (dB)
P = power
U*0 = reference voltage
equal loudness curves
RP = 1/ α*min
RP = resolving power
α*min = min. angular resolution
measurement of d of erythrocytes by microscope
α*min = 1.22λ / D
Rayleigh criterion
D = diameter of aperture (part of lens thru which light passes)
α*min = min angular resolution
λ = of light used for observation
measurement of d of erythrocytes by microscope
d = λ / 2n(sinu)
Rayleigh criterion for d
d = min. distance b/n 2 points of the object that can be separately detectable by the instrument
λ = of light used for observation
n = refractive index of medium separating the objective lens and the specimen
u = aperture angle
measurement of d of erythrocytes by microscope
A = n(sinu)
Abbe criterion
A = numerical aperture
n = refractive index of medium separating the objective lens and the specimen
u = aperture angle
measurement of d of erythrocytes by microscope
d = λ / 2A
λ = of light used for observation
A = numerical aperture
d = min. distance d b/n 2 points of the object that can be separately detectable by the instrument
measurement of d of erythrocytes by microscope
RP = 1/d = 2A/λ
RP = resolving power
d = min. distance d b/n 2 points of the object that can be separately detectable by the instrument
A = numerical aperture
λ = of light used for observation
measurement of d of erythrocytes by microscope
m = d*i / d*o
m = magnification
d*i - image height/distance
d*o = object height/distance
measurement of d of erythrocytes by microscope
m*t = m*o m*e
m*t = total magnification
m*o = magnification of objective
m*e = magnification of eyepiece
measurement of d of erythrocytes by microscope
m*o = d*i/d*o ≈ l/f*o
m*o = magnification of objective
d*i - image height/distance
d*o = object height/distance
l = distance b/n objective and eyepiece lenses
f*o = objective focal length
measurement of d of erythrocytes by microscope
m*e ≈ d*d/f*e
m*e = magnification of eyepiece
d*d = distance of distinct vision
f*e = eyepiece focal length
measurement of d of erythrocytes by microscope
m*t ≈ l d*d / f*o f*e
m*t = total magnification
l = distance b/n objective and eyepiece lenses
f*o = objective focal length
d*d = distance of distinct vision
f*e = eyepiece focal length
measurement of d of erythrocytes by microscope
s = N*1 k
s = distance b/n 2 pts on stage micrometer
N*1 = difference b/n 2 readings in units k
measurement of d of erythrocytes by microscope
s = N*2 b
s = distance b/n 2 pts on stage micrometer
N*2 = # of divisions of stage micrometer b/n the 2 pts
b = unit of stage micrometer
measurement of d of erythrocytes by microscope
k = N*2 b / N*1
N*2 = # of divisions of stage micrometer b/n the 2 pts
b = unit of stage micrometer
N*1 = difference b/n 2 readings in units k
measurements of d. of erythrocytes by microscope