Patch clamp

Patch clamp connects an electrode to a small area of cell membrane through a solution-filled patch pipette. A gigaohm seal around the rim makes tiny electric currents through ion channels distinguishable from seal leak current. The beautiful change of scale is from a population's average response to individual opening and closing events in single-channel recording.

Separate two questions. The configuration determines which cell membrane is accessible: an intact patch in cell-attached recording, an excised inside-out patch or outside-out patch, or intracellular access in whole-cell recording. The recording mode determines what is commanded and what is observed: voltage clamp commands an electric potential difference and measures electric current; current clamp commands electric current and measures membrane potential. Whole-cell recording supports both modes. A patch can contain several ion channels; a small recording area does not establish that only one is present.

The 1976 article Single-channel currents recorded from membrane of denervated frog muscle fibres describes an extracellular fire-polished pipette with a $3$–$5\mu \mathrm{m}$ opening and $2$–$5\mathrm{M\Omega }$ electrical resistance. It contained saline and a channel-activating compound. Two separate intracellular electrodes supplied local voltage clamp of the muscle fibre; the patch amplifier measured local electric current. Cooling to $6$–$8{}^{\circ }\mathrm{C}$ and hyperpolarization helped resolve elementary events. Figure 2 shows step-like pulses with a $200\mathrm{Hz}$ filter at $-120\mathrm{mV}$ and $8{}^{\circ }\mathrm{C}$. Discrete amplitudes and overlapping events supported individual ion channel openings rather than a smoothly varying population response. This was neither whole-cell recording through the patch pipette nor current clamp. The specialized conditions improved visibility but limit generalization to warmer preparations; filtering can conceal brief openings.^[ref]

For a new single-channel recording experiment, useful controls include a matched recording without the activating compound, controlled membrane potential, repeated seal tests, and an explicitly stated filter frequency response. These are proposed controls, not claims that every one was performed in that 1976 figure. Changing membrane potential tests the single-channel current-voltage relation; changing the recording filter tests whether a short pulse's apparent amplitude is an instrument artifact. A flat baseline establishes neither an absence of ion channels nor an absence of very brief events.

A patch pipette is the tapered glass, solution-filled probe used in patch clamp. Its electrode connects the solution to an amplifier, with another electrode referencing the bath. The open-tip electrical resistance differs from the much larger gigaohm seal electrical resistance. After break-in, a narrow or partly obstructed tip contributes to patch-clamp series resistance.

A gigaohm seal is the high electrical resistance contact between the glass rim and cell membrane, also called a gigaseal. It suppresses a bypass route around the membrane patch; it does not make the membrane patch itself impermeable. The 1981 methods used pulled, coated and heat-polished pipettes, a chlorided silver electrode and a pressure connection. Clean glass and suction supported tight seals; coating reduced pipette-to-bath capacitance and recording noise, rather than being required for sealing.^[ref]

Seal leak current bypasses the membrane patch through an imperfect seal. For an ideal ohmic seal to a zero-voltage bath, $I_{\mathrm{seal}}=V_p/R_{\mathrm{seal}}$, positive from pipette to bath. At $|V_p|=50\mathrm{mV}$ and $R_{\mathrm{seal}}=1\mathrm{G\Omega }$ its magnitude is $50\mathrm{pA}$, far larger than the synthetic $0.8\mathrm{pA}$ single-channel step. A stable baseline can be subtracted, but changing leakage can mimic a biological response. Intrinsic membrane leak through ion channels is distinct from this bypass: interpreting both as the same electrical conductance obscures whether the biological cell or the seal changed.

In cell-attached recording, the membrane under the patch pipette remains intact and the cytosol is retained. If bath voltage is zero, cell-interior voltage is $V_{\mathrm{cell}}$ and pipette voltage is $V_p$, the patch's inside-minus-outside membrane potential is $V_{\mathrm{cell}}-V_p$. Commanding $V_p$ alone does not determine that difference when $V_{\mathrm{cell}}$ is unknown or changing. This is especially relevant to single-channel current-voltage relations.

Single-channel recording resolves individual ion channel opening events as changes in electric current. The distinction is resolution, not an absolute rule about configuration: rare, sufficiently large events can also be resolved during whole-cell recording. Simultaneously open identical ion channels can give successive current levels; indistinguishable amplitudes alone do not prove a unique channel identity.

For an ideal open ion channel with constant electrical conductance $g$, membrane potential $V$ and reversal potential $E_{\mathrm{rev}}$, define outward electric current as positive:This is an Ohm's law model of the open state, not a universal channel law or a rule for opening probability. In the synthetic figure, $g=10\mathrm{pS}$ and $E_{\mathrm{rev}}=0\mathrm{mV}$. Because $1\mathrm{pS}\cdot 1\mathrm{mV}=10^{-3}\mathrm{pA}$, the open-state electric currents at $-80$ and $-40\mathrm{mV}$ are $-0.8$ and $-0.4\mathrm{pA}$. Zero electric current at the reversal potential does not imply a closed ion channel. Real ion channels can have nonlinear responses, so the straight line is an explicit idealization.

An inside-out patch is an excised membrane patch whose cytosol side faces the bath. Bath changes can therefore test effects on the intracellular face of an ion channel, with the extracellular face exposed to pipette solution.

An outside-out patch is an excised membrane patch whose extracellular side faces the bath. It can form on withdrawal after whole-cell recording, with the intracellular face exposed to pipette solution. The orientation determines which side a bath-applied substance reaches.

Whole-cell recording establishes intracellular electrical access by rupturing the membrane under a sealed patch pipette while retaining the gigaohm seal. Under adequate voltage clamp, the measured electric current combines contributions from accessible ion channels, membrane capacitance and seal leak current. Current clamp instead follows membrane potential while supplying a chosen electric current. Whole-cell recording is useful for linking a biological cell's total electrical response to its ion channels, but neither mode automatically controls distant dendrites or preserves the original cytosol.

In the 1981 methods demonstration, a bovine chromaffin biological cell was tested before and after patch rupture. Small voltage clamp steps produced a much larger capacitive transient after break-in. Integrating it gave $5\mathrm{pF}$ for a $13\mu \mathrm{m}$ cell; its decay indicated patch-clamp series resistance below $20\mathrm{M\Omega }$. Depolarizing commands then revealed ionic electric currents. Separate current clamp recordings showed spontaneous action potentials. The comparison established access to the cell interior, rather than a claim that every pipette command equals membrane potential. Slower transients sometimes indicated incomplete rupture, and these small-cell results do not establish spatial control of a branched neuron.^[ref]

Patch-clamp series resistance, also called patch-clamp access resistance, is the effective electrical resistance between the pipette's sensed voltage and the cell interior. It includes tip access and any remaining obstruction after break-in. For injected electric current $I$ into the biological cell, an ideal resistive access path givesThus $1\mathrm{nA}$ through $20\mathrm{M\Omega }$ produces a $20\mathrm{mV}$ difference: a substantial possible voltage clamp error. The electric current in this equation is the access-path current, excluding any bypass seal leak current. In current clamp, the same access drop contaminates the pipette voltage during injection. Bridge compensation subtracts an estimated $I{R}_s$; an estimate that changes during recording leaves an error.

An independent passive voltage clamp calculation makes both speed and error visible. Write $v=V-E_L$ and $v_p=V_p-E_L$, with fixed leak reversal potential $E_L$, constant membrane electrical resistance $R_m$ and membrane capacitance $C_m$. Assume an ideal command at the pipette node and omit seal leak current and pipette capacitance. Electric charge conservation givesFor a step $v_p=\Delta V$ from $v(0)=0$, the ordinary differential equation givesWith the figure's parameters and $\Delta V=10\mathrm{mV}$, the time constant is $0.909\mathrm{ms}$, the final membrane rise is $9.091\mathrm{mV}$, and access-path electric current falls from $500$ to $45.45\mathrm{pA}$. Only when $R_m\gg R_s$ does the time constant approach $R_s{C}_m$ and the final voltage approach the command. Actual voltage clamp also depends on amplifier feedback control and the space clamp problem.

Membrane capacitance is the capacitance associated with separated electric charge across cell membrane. A local ideal capacitor has charging electric current $I_C=C_{m}dV/dt$. If a known actual membrane voltage change is $\Delta V$, integrating the charging transient after subtracting sustained ionic and leak components gives $C_m=\Delta V^{-1}\int I_{C}dt$. Pipette capacitance, finite patch-clamp series resistance and imperfect transient subtraction can bias the estimate. A capacitive transient is not by itself an ion channel opening.

When a single ion species supplies the net charging of a cell membrane, its bulk concentration increment is $\Delta c=C_{m}A\Delta V/(zF\mathcal{V})$. Opposing ionic Electric currents can make gross entry exceed this minimum net electric charge budget. A large membrane potential change can coexist with approximate bulk electroneutrality.

The space clamp problem is the failure to maintain the commanded membrane potential throughout a spatially extended biological cell. A soma voltage clamp can coexist with substantial voltage changes in distant dendrites or an axon. Reducing patch-clamp series resistance improves access at the recording site, but does not eliminate electrical separation within the neuron.

Cytosol dialysis is exchange between the cytosol and pipette solution through the opening used in conventional whole-cell recording. Diffusion can change ion concentrations and dilute soluble regulators of ion channels. A diminishing response can therefore reflect the recording's alteration of the biological cell, rather than the experimental treatment.

A direct motivating example is the 1988 article Muscarinic activation of ionic currents measured by a new whole-cell recording method. In rat lacrimal gland biological cells, the acetylcholine response in conventional whole-cell recording lasted about five minutes. With a pore-forming substance in the patch pipette instead of open break-in, the response remained undiminished after one hour. The readout was activation of calcium-activated potassium and ${\mathrm{Cl}}^{-}$ ion electric currents; preserving the response supported a role for retained cytoplasmic components. The authors also tested the substance extracellularly and observed reversible increases in cation electrical conductance. This comparison motivates perforated patch recording, but does not show that every intracellular constituent or every ion channel response is preserved. ^[ref]

Practical controls are matched pipette and bath compositions, recording elapsed time after break-in, time-matched untreated preparations, and tracking both patch-clamp series resistance and baseline leakage. Comparing conventional whole-cell recording with perforated patch recording can separate loss of soluble components from an intended treatment effect, but only if electrical access is characterized in both. These are controls suggested by the mechanisms above, not a new set of measured results.

Perforated patch recording obtains intracellular electrical access through pores in the patch under the patch pipette, with less open exchange of large cytoplasmic components than conventional whole-cell recording. Pore selectivity matters: retaining some components does not guarantee unchanged ion concentrations. Monitor patch-clamp series resistance as access develops and distinguish a perforated patch from accidental full rupture.

Current clamp prescribes injected electric current while recording membrane potential. A constant command does not force membrane potential to remain constant: a neuron can produce action potentials or synaptic potentials while that command is unchanged. At zero commanded electric current, the amplifier still measures membrane potential; intrinsic ionic electric currents continue. The name concerns current supplied by the instrument, not the cancellation of all currents in the biological cell.

In whole-cell recording, the measured pipette voltage during a current pulse includes the patch-clamp series resistance drop. A modern authored methods article explicitly describes current-pulse protocols and this distortion.^[ref] Check the access contribution with small pulses and distinguish the immediate pipette-voltage jump from the slower membrane capacitance response. A zero-input interval measures a baseline, not proof that the instrument has no voltage offset. The passive example below explains these distinctions without asserting any new physiological measurements.

Model a spatially uniform cell membrane as a capacitor of membrane capacitance $C_m$ in parallel with membrane electrical resistance $R_m$ and a fixed leak reversal potential $E_L$. Exclude active ion channels, seal leak current and pipette capacitance. For electric current $I$ injected into the biological cell, electric charge conservation yieldsStarting at $V(0)=E_L$ and applying constant $I$ gives the ordinary differential equation solutionThe steady state rise is $I{R}_m$; the time constant is $R_m{C}_m$. With $I=50\mathrm{pA}$, $R_m=200\mathrm{M\Omega }$, $C_m=50\mathrm{pF}$ and $E_L=-70\mathrm{mV}$, the rise is $10\mathrm{mV}$ and ${\tau }_m=10\mathrm{ms}$. At one time constant the rise is $10(1-e^{-1})\mathrm{mV}\approx 6.321\mathrm{mV}$. The figure's uncompensated pipette voltage adds $I{R}_s=1\mathrm{mV}$ for $R_s=20\mathrm{M\Omega }$. The membrane voltage is continuous at step onset in this model, while the pipette voltage immediately acquires that access drop.

Checking the units is instructive: electrical resistance times capacitance has units $\Omega \mathrm{F}=\mathrm{s}$, and electric current times electrical resistance has units of voltage. Unlike the passive voltage clamp transient under patch-clamp series resistance, this ideal current clamp membrane time constant is set by $R_m{C}_m$, not $R_s{C}_m$. Strong current steps can recruit voltage-gated ion channels; the passive model then fails and cannot generate an action potential. Small pulses of both signs, stable access and repeated baseline measurements help test whether the passive approximation is appropriate.