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131 Cards in this Set
- Front
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- 3rd side (hint)
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
|
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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
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T = I*t / I*0
|
T = transmittance
I*t= intensity of transmitted beam I*0 = intensity of incident beam |
spectrophotometry
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A = - logT
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A = absorbance
T = transmittance |
spectrophotometry
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A = ε*λ dc
|
Beer Law
A = absorbance ε*λ = absorptivity d = path length c = concentration of absorbing species |
spectrophotometry
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T=10^(-ε*λ dc)
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Beer-Lambert Law
T= transmittance ε*λ = absorptivity d = path length c = concentration of absorbing species |
spectrophotometry
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Tan α = n
|
n= refractive index of reflecting surface
α = brewster angle (of incidence) |
polarimetry
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[α]*λ = φ / l c
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φ = rotation angle
[α]*λ = specific rotation l = path length c = concentration |
polarimetry
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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
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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
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hv = E*K + E*B
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hv = photon's energy
E*K = kinetic energy of ejected electron E*B = binding energy of electron |
attenuation of electro. radiation
|
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hv = E*K + hv'
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hv = photon's energy
E*K = kinetic energy of ejected electron hv' = energy of scattered photon |
attenuation of electro. radiation
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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)
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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
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μ*m = μ / d
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μ*m = mass attenuation coefficient (m^2/kg)
μ = linear attenuation coefficient (1/m) d= absorber density |
attenuation of electro. radiation
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I = I*0 e^(-μ*m dx)
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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
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I*0/2= I*0 e^(-μ HVL)
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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
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HVL = ln2/μ
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HVL = half value layer
μ = linear attenuation coefficient (1/m) |
attenuation of electro. radiation
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a = ΔN/Δt
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a = counting rate
ΔN = # of pulses Δt = unit time |
attenuation of electro. radiation
|
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a*x = a*0 e^(-μx)
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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
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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
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τ = F / S
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τ = shear stress
F = force needed to maintain a uniform motion of plate (constant Δv) S = surface area of fluid layer |
viscosity
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τ = η Δv/Δx
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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
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η = F Δx / S Δv
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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
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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
|
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F*B + F*S = Q
|
F*B = buoyant force
F*S = Stokes force Q = force of gravity |
viscosity
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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
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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
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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
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Φ = V*s / V*t
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Φ = volumic coefficient
V*s = volume of particles of dissolved substance V*t = total volume of solution |
viscosity of solutions
|
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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
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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
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η*s = (η / η*0 ) – 1
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η*s = specific viscosity
η / η*0 = relative viscosity |
viscosity of solutions
|
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η*s = 2.5Φ
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η*s = specific viscosity
Φ = volumic coefficient |
viscosity of solutions
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η*int = limc→0 (η*s / c)
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η*int = intrinsic viscosity
η*s = specific viscosity c = concentration of solution (tending to 0) |
viscosity of solutions
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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
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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
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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
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η / η*0 = td / t*0 d*0
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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
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η = A e^(w*a/kT)
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η = viscosity
w*a = energy of activation k = Boltzmann constant A = constant characteristic for a given fluid T = absolute temperature |
viscosity of solutions
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j = Δm / Δt
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j = flux j (kg/s)
Δm= amt. of substance which passes an imaginary surface Δt = time |
diffusion
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Δm / Δt = –DS (Δc / Δx)
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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
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|
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
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(Δx)^2 = 2Dt
|
Einstein-Smoluchowski EQ
Δx – avg displacement t – time elapsed since molecule started diffusing D – diffusion coefficient |
diffusion
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P = D / Δx
|
P = membrane permeability constant (m/s)
Δx – avg displacement D – diffusion coefficient |
diffusion
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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
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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
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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
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|
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
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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
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|
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
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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
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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
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P = q / S
|
P = polarization vector
q = charge S = surface of material in electric field |
dispersion of e.r. of blood
|
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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
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|
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
|
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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
|
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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
|
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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
|
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F*E = qE
|
F*E = electric force
q = ion charge E = electric field |
hematocrit determination by maxwell method
|
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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
|
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v = uE
|
v = transportation velocity
u = ion mobility E = electric field |
hematocrit determination by maxwell method
|
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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
|
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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
|
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Z = (R^2 + (R*c)^2)^½
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Z = impedance
R = resistance R*c = capacitive reactance |
hematocrit determination by maxwell method
|
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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
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|
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
|
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C = R σ*r
|
C = measuring vessel constant
R = resistance σ*r = conductivity of reference solution |
hematocrit determination by maxwell method
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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
|
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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
|
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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
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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
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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
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|
τ = η / E
|
τ = stress relaxation time
η = viscosity of dashpot E = Young's modulus of spring (Maxwell) |
examinations of models of NSM
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|
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
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|
Δl = v*c t
|
Δl = elongation
v*c = velocity of creep t = time (Maxwell) |
examinations of models of NSM
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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
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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
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|
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
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m*o = d*i/d*o ≈ l/f*o
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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
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m*e ≈ d*d/f*e
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m*e = magnification of eyepiece
d*d = distance of distinct vision f*e = eyepiece focal length |
measurement of d of erythrocytes by microscope
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m*t ≈ l d*d / f*o f*e
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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
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s = N*1 k
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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
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s = N*2 b
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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
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k = N*2 b / N*1
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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
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