In Vitro Radiation Detection
In many nuclear medicine procedures, such as the Schilling test, blood volume determinations, protein and fat absorption studies, ferrokinetics, and various radioimmunoassay, it is necessary to determine the amount of radioactivity in a given sample as compared with a standard. In some of these tests (e.g., Schilling test), a radioactive substance is administered to a patient; in others, such as various radioimmunoassay, no radioactive compound is given to the patient. In both cases, however, the choice of the radiation detector and the geometric setup for the measurement of a given radioactive sample are of great importance and are primarily dictated by the overall efficiency (sensitivity) of a particular setup. An increased overall efficiency in these studies allows one to reduce either the radiation dose to a patient or the count time for a given standard deviation error.
This chapter describes the various techniques used for the in vitro detection of the radioactivity of both βray and γray emitting radionuclides.
Overall Efficiency E
The overall efficiency E of a given device for the measurement of radioactivity depends on the geometric efficiency of the physical setup E_{g} and the intrinsic efficiency E_{i} of the detector. Thus, the overall efficiency can be expressed as
E = E_{g} × E_{i}
Intrinsic Efficiency. The intrinsic efficiency E_{i} (see Chapter 8) is defined as
It primarily depends on the linear attenuation coefficient µ (linear) of the material of which a detector is made and on the thickness of the detector.
In a scintillation counter, when one restricts oneself to the photo peak counts only, the resulting intrinsic efficiency is known as the photo peak efficiency.
Geometric Efficiency. Geometric efficiency E_{g} can be understood as follows. Let a small sample of radioactive compound be located at a distance from a detector with a crosssectional radius r as shown in Figure 9.1 (top). Because there is no preferred direction for the emission of radiation from a radionuclide, the radiations (α, β, or γ) from a radioactive sample will be emitted with equal probability in all directions. Therefore, of the total number of nuclear radiations emitted in all directions, only a fraction of these will be incident on the sensitive volume of the detector (Fig. 9.1, top). Geometric efficiency E_{g}, then, is defined as the ratio of the number of radiations incident on the detector from a radioactive sample
to the total number of radiations emitted by the sample, or
to the total number of radiations emitted by the sample, or
The geometric efficiency Eg, for the device shown in Figure 9.1 (top), depends on two factors: the distance x between the source and the detector, and the radius r of the crosssectional area of the detector. For distances that are sufficiently larger than the radius of the detector (i.e., x >> r), the geometric efficiency varies as 1/x^{2} and r^{2}, respectively, with the distance x and the radius r; that is, if one increases the distance between the sample and the detector twofold, the geometric efficiency is reduced fourfold (Fig. 9.1, center). If the radius of the detector is doubled, the geometric efficiency will be increased fourfold (Fig. 9.1, bottom).
When the sample is very close to the detector (i.e., x << r), the above relationship E_{g} ∝ (1/x^{2}) does not hold true. The exact relationship between E_{g} and the distance x, in this case, is of no practical concern to us here except to know that the maximum obtainable geometric efficiency is achieved when x = 0 (i.e., the source is directly against the face of the detector). In this case, E_{g} approaches 50%, because even in this situation, onehalf of the radiations are emitted away from the detector.
To increase E_{g} to more than 50%, one has to either use more than one detector or somehow surround the sample from all sides by the detector. The second approach is used in welltype NaI(Tl) scintillation detectors (well counters) and liquid scintillation detectors described later and is also used in dose calibrators as is described in Chapter 8.
WellType NaI(Tl) Scintillation Detectors (Well Counters)
In terms of its operation and associated electronics, the welltype NaI(Tl) scintillation detector (well counter) is exactly the same as the NaI(Tl) scintillation detector described in Chapter 8, except that in a well counter, a small cylindrical hole is constructed in the NaI(Tl) crystal to allow a radioactive sample to be positioned very close to the center of the crystal (Fig. 9.2). In this type of detector, only a small fraction (<5%) of the radiations emitted by the sample, escapes from the sensitive volume of the crystal. Thus, E_{g} approaches 95%. The intrinsic efficiency of an NaI(Tl) detector is dependent on the size of the crystal—the larger the crystal, the higher the intrinsic efficiency for a given energy γray. Well counters are commercially available in various sizes. The socalled standard well counter (1.75inch diameter, 2 inches in height with a hole 0.75 inches in diameter and 1.5 inches deep) enjoys the most popularity in nuclear medicine. For highenergy γrays (>500 keV), however, one achieves a far better count rate with a 3 × 3inch well counter
than with the standard model. Table 9.1 lists the intrinsic efficiencies of standard and 3 × 3inch well counters for various γray energies. It can be seen from columns 2 and 3 that at higher energies, one gains a factor of 1.5 in intrinsic efficiency by using a 3 × 3inch rather than a standard well counter. For many procedures, one is interested only in the photo peak counts (i.e., one rejects γray interactions via the Compton scattering). In this case, the advantage of a 3 × 3inch over a standard well counter for higher energy γrays becomes even greater (see columns 4 and 5 in Table 9.1).
than with the standard model. Table 9.1 lists the intrinsic efficiencies of standard and 3 × 3inch well counters for various γray energies. It can be seen from columns 2 and 3 that at higher energies, one gains a factor of 1.5 in intrinsic efficiency by using a 3 × 3inch rather than a standard well counter. For many procedures, one is interested only in the photo peak counts (i.e., one rejects γray interactions via the Compton scattering). In this case, the advantage of a 3 × 3inch over a standard well counter for higher energy γrays becomes even greater (see columns 4 and 5 in Table 9.1).
Table 9.1 Efficiency of a Well Counter  

