Cerebral blood flow sensitivity to CO2 measured with steady-state and Read's rebreathing methods
Introduction
Read, 1967, Read and Leigh, 1967 described a rebreathing technique to measure the central chemoreceptor ventilatory response to CO2. Their method is still used widely in basic science and clinical research (Saito et al., 1995). Read (1967) used a small bag (about 6 L) filled with a gas mixture of about 6–7% CO2 in O2. Under these conditions, rebreathing was initiated at a CO2 tension close to that of mixed venous blood (PvCO2) and the subsequent increases in end-tidal PCO2 (PetCO2) and ventilation (e) were linear in time. It is generally thought that initiating rebreathing close to PvCO2 leads to a rapid equalisation of PetCO2, arterial PCO2 (PaCO2), PvCO2, and presumably also brain tissue (extracellular) PCO2 (PtCO2), and that all these variables increase at the same rate (Rebuck and Slutsky, 1981).
Read's method differs from the alternative, steady-state method in which inspired PCO2 is manipulated to increase PetCO2 in a step to a new level, and then held constant at this new, higher level until the ventilatory response reaches a steady-state. With this method (and in contrast with rebreathing) there is always a gradient between PetCO2 and PtCO2.
Some studies have found good agreement between Read's method and the steady-state method for the central chemoreflex ventilatory CO2-sensitivity (Read, 1967, Clark, 1968), but most investigators have concluded that the ventilatory CO2-sensitivity measured by Read's method was greater than that measured by the steady-state method (Tenney et al., 1963, Honda and Miyumara, 1972, Linton et al., 1973, Jacobi et al., 1989, Berkenbosch et al., 1989, Bourke and Warley, 1989, Lumb and Nunn, 1991, Mohan et al., 1999). Berkenbosch et al. (1989) have argued that this more usual result was predictable from first principles: since PetCO2 and PtCO2 are always equal during rebreathing, the corresponding rise in PtCO2 must be the same as a unit rise in PetCO2. However, since a gradient always exists between PetCO2 and PtCO2 in the steady-state, a unit rise in PetCO2 will yield a smaller corresponding rise in PtCO2 (and as the CO2 perturbation increases in the steady-state, the difference between PetCO2 and PtCO2 will decrease). Poulin and Robbins (1998) have estimated that a step increase in PaCO2 of 7.5 mmHg results in a corresponding rise in PtCO2 of only 5.5 mmHg in the steady-state. Because PtCO2 in the region of the central chemoreceptor ultimately determines the ventilatory response to CO2, the slope of the e–PetCO2 relationship will, therefore, be greater with rebreathing than with the steady-state method. Additionally (because of the gradient between PetCO2 and PtCO2 in the steady-state), it is expected that the x-axis intercept of the e versus PetCO2 plot will be shifted to the left as compared with the rebreathing plot. These predictions have been confirmed experimentally (Berkenbosch et al., 1986, Berkenbosch et al., 1989, Dahan et al., 1990).
Read's method would seem to provide a relatively simple means of effecting a predictable change in CO2 tensions, whilst at the same time allowing continuous estimation of the cerebral blood flow (CBF). However, to our knowledge, Read's method and the steady-state methods have not previously been directly compared with regard to CBF sensitivities to CO2.
We made two assumptions. First, we assumed that brain extracellular PtCO2 is the prime determinant of the CBF response to CO2. This view is widely-held (at cellular level, PtCO2 might exert its effect through changes in local pH), and PtCO2 is thought to be one of the main mediators of the increase in blood flow in response to increased local metabolic brain activity (Busija and Heistad, 1984, Brian, 1998). Second, we assumed that if this is the case, the same argument employed by Berkenbosch and colleagues regarding the reasons for the rebreathing ventilatory CO2 sensitivity being higher than steady-state sensitivity, would also apply to the CBF response to CO2. We consequently predicted that (a) the CBF sensitivity to CO2 would be higher when measured by Read's technique as compared with the steady-state method; (b) the x-axis intercept of the plot of CBF versus PetCO2 will be shifted to the left for the steady-state as compared with rebreathing. The purpose of this study was to test these predictions and compare CBF sensitivities to CO2 measured by rebreathing and steady-state methods.
Section snippets
Subjects
This study had the approval of the Central Oxford Research Ethics Committee, and written informed consent was obtained from all participants. Six healthy non-smoking subjects (five males, one female) were studied, aged 21–35 years, weight 65–85 kg, height 167–180 cm. Subjects were seated in a chair, an ECG monitored the heart rate, and a finger pulse oximeter was used to measure oxygen saturation.
Apparatus for steady-state method
Subjects wore a noseclip and breathed through a mouthpiece. A dynamic end-tidal forcing system was
Ventilatory responses to carbon dioxide
Fig. 1 shows the ventilatory responses in the two protocols for one example subject. In the steady-state protocol, ventilation increased in a step-manner as each of the three hypercapnic stimuli was applied, and was reasonably constant during periods of eucapnia (Fig. 1, top panel). The rise in e with time (and so also with PetCO2) during rebreathing was linear (Fig. 1, middle panel). The steady-state protocol yielded four data points for e versus PetCO2, and these are plotted in Fig. 1
Discussion
Based on the assumption that brain extracellular PtCO2 is the main determinant of the CBF sensitivity to CO2 we predicted that as with the ventilatory response, the CBF–CO2 sensitivity measured by the rebreathing method should be greater than that measured by the steady-state method. The striking result of this study is that this is not the case: steady-state CBF sensitivity significantly exceeds rebreathing CBF sensitivity.
Acknowledgements
This study was approved by the Central Oxford Research Ethics Committee and was supported by the Wellcome Trust. M.J. Poulin and N.D. Paterson were supported by the Heart and Stroke Foundation of Ontario (Canada), (postdoctoral research fellowship Grant F3555). We wish to acknowledge the volunteers for their participation in the study.
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