Introduction

Elements that emit radiation are known as radionuclides and have a number of applications in medicine. Radiopharmacy in hospital practice is concerned with the manufacture or preparation of radioactive medicines known as radiopharmaceuticals. These have two main applications in medicine:

In diagnostic imaging, gamma-emitting radionuclides are used, since their interaction with tissue is much less than that of particulate emitters and will cause significantly less damage to tissue. Radiopharmaceuticals are administered to the patient, usually by the intravenous (IV) route, and distribute into a particular organ. The radiation is then detected externally using a special scintillation detector known as a gamma-camera. These are used by nuclear medicine departments to image the distribution of the radiopharmaceutical within the patient’s body. Using the gamma-camera in conjunction with a computer system it is not only possible to produce static images of an organ, but also to examine how the radiopharmaceutical moves through an organ. These dynamic images describe how the organ is functioning. It is also possible to create images in three dimensions, a process known as single photon emission computerized tomography (SPECT) when used in combination with gamma-emitting radionuclides such as ^99mTc and positron emission tomography (PET) when used in combination with positron-emitting radionuclides such as ¹⁸F.

It is important to note that for the safe production of radiopharmaceuticals, the radiopharmacy must be designed to comply with, and procedures must follow, good manufacturing practice and good radiation protection practice. Radiopharmacists working in this field are part of a multidisciplinary team which includes physicians, physicists, radiochemists and technicians from the field of pharmacy as well as nuclear medicine. As part of this team, they not only ensure that the radiopharmaceuticals will give high-quality clinical information, but also that they are safe for both patient and user alike.

Radionuclides used in nuclear medicine

Beta-emitters

Beta-decay occurs in two ways, one that involves the emission of a negatively charged beta⁻-particle, or electron, and the other that involves the emission of a positively charged beta⁺-particle, or positron.

Beta⁻-emitters

Radionuclides which decay by beta⁻-decay tend to have nuclei that are neutron rich. They attempt to reach a more stable state by the transformation of a neutron into a proton with the emission of a beta⁻-particle. (e.g. ³²P: ³²₁₅P → ³²₁₆S + beta⁻). Despite beta⁻-particles having a range in air of up to several meters, their range in tissues is only a few millimetres. Because of this and their highly ionizing nature, beta⁻-emitters tend to be used in therapeutic radiopharmaceuticals (Table 42.1).

Table 42.1 Examples of radionuclides used in nuclear medicine

The principle of therapeutic treatment with radionuclides is to target the radionuclide to a specific tissue within the body in an attempt to selectively damage or destroy that tissue. Ideally therapeutic beta⁻-emitting radionuclides should have energies of 0.5–1.5 MeV and a half-life of several days to provide a prolonged radiobiological effect.

The most widely used example of this is ¹³¹I-sodium iodide which is used in the treatment of hyperactive thyroid disease and in certain thyroid tumours. Here the physiological property of thyroid tissue is exploited to target the radionuclide to the site of action. Since thyroid tissue avidly takes up iodine in the normal synthesis of the hormone levothyroxine, radioactive iodine is also taken up and held in the thyroid tissue. Hence the radiation damage is targeted to the thyroid tissue specifically and the normal excretion of any excess iodine results in no significant damage to other organs and tissues.

Beta⁺-emitters

Radionuclides that emit positrons are becoming more widely used in nuclear medicine. In this transformation, a proton-rich nuclide attempts to achieve stability by converting a proton to a neutron with the emission of a positron (e.g. ¹¹C: ¹¹₆C → ¹¹₅S + beta⁺ + gamma). The positron is very short-lived, since it interacts with an electron resulting in an annihilation reaction and the conversion of both particles into electromagnetic (EM) radiation. This EM radiation is in the form of two gamma-rays, each having energy of 0.511 MeV, which are emitted at an angle of 180° to each other.

When used in conjunction with a specialized gamma-camera with detectors placed 180° apart, it is possible to create images in all three dimensions with the position of the radiopharmaceutical being very precisely known. This type of imaging technique is known as positron emission tomography (PET). There are a number of positron emitting radionuclides which are becoming important tools in diagnostic imaging. Currently ¹⁸F labelled glucose, known as ¹⁸F-fluoro deoxy-glucose (¹⁸F-FDG), is the most commonly used PET radiopharmaceutical in hospital practice and as a result the production processes for it will be described in simplified form and used as an example. However, it should be noted there are four main positron emitters used to prepare radiopharmaceuticals (see Table 42.1). PET imaging with ¹⁸F-FDG, in combination with X-ray computerized tomography (CT) is rapidly becoming an important imaging technique in the diagnosis of cancer.

In the manufacture of ¹⁸F-FDG there are two main processes required. First there is the production of the radionuclide itself, which is produced in a cyclotron facility. This is followed by the radio-synthesis of the ¹⁸F-FDG, which is carried out in an automated apparatus, known as a synthesis module. The resulting solution of ¹⁸F-FDG has then to be sterilized and may have to be sub-dispensed in some way so as to provide the injection in a ready to administer form. Since the ¹⁸F-FDG has been synthesized, it will require analysis and other quality control checks prior to administration to the patient.

Radionuclide production

A cyclotron is a device used to produce radionuclides. It accelerates atomic or subatomic particles in a circular orbit, increasing the energy of the particles until a high-energy beam of particles is created. Once the particles have reached their maximum energy they are extracted using high voltage and allowed to bombard target materials. The composition of the target material and the nuclear reactions that take place determine the radionuclides that are produced.

For ¹⁸F production, the most common nuclear reaction used is the ¹⁸O (p,n) ¹⁸F reaction where protons are produced from hydrogen gas and are accelerated until, at a required energy, a ‘beam’ of the protons are allowed to bombard a target of ¹⁸O-enriched water (H₂¹⁸O). ¹⁸O is a naturally occurring isotope of oxygen, but much less abundant than the normal ¹⁶O. By forcing a proton into the ¹⁸O nucleus the now unstable nucleus ejects a neutron and the result is the production of ¹⁸F – a positron-emitting radionuclide.

Radio-synthesis

2-[¹⁸F] fluoro-2-deoxy-D glucose (¹⁸F-FDG) may be prepared by various chemical pathways, but whatever radio-synthetic route is used it must be rapid to minimize the radiation risk and be of high yield. An automated apparatus, the synthesis module, is used to synthesize the ¹⁸F-FDG to assure production efficiency and keep radiation exposure to a minimum. There are now commercially available synthesis modules such as the TRACERlabFx Synthesizer^® as shown in Figure 42.1, which are supplied with good manufacturing practice (GMP) standard raw materials and reagents for use in the module. Using this equipment, the following synthetic pathway is performed:

1. The ¹⁸F-fluoride is adsorbed by an anion-exchange resin.

2. The retained ¹⁸F-fluoride is eluted using an aqueous potassium carbonate solution.

3. A phase transfer catalyst (Kriptofix 222) dissolved in acetonitrile is then added, to bind the potassium ion and to enhance the nucleophilic reactivity of the ¹⁸F-fluoride.

4. After evaporation of the solvents, the ¹⁸F-fluoride is allowed to react with the reagent mannose triflate at elevated temperature (1,3,4,6-O-Acetyl-2-O-trifluoromethanesulfonyl-beta-D-mannopyranose). The structure of mannose triflate is similar to that of glucose with a leaving group (triflate) and four acetyl protecting groups to ensure the mannose ring undergoes nucleophilic substitution at the second carbon atom.

5. Hydrolysis under acidic or alkaline conditions also at elevated temperature yields 2-[¹⁸F] fluoro-2-deoxy-D glucose (¹⁸F-FDG).

Fig. 42.1 Synthesis module for ¹⁸F-FDG production (TRACERlabFx Synthesizer^®. (Courtesy of GE Healthcare plc.) Module located in lead-shielded (5.5 cm) specialized fume cupboard known as ‘hot cell’.

Isomeric transition

Some radionuclides exist for measurable periods in excited, or isomeric, states prior to reaching ground state. This form of decay involves the emission of a gamma-ray and is known as isomeric transition. When radionuclides exist in this transitional state, they are known as metastable, which is denoted by the letter ‘m’ and written thus: ^99mTc.

A simplified decay scheme for ^99mTc-technetium is shown in Figure 42.2 where ^99mTc’s parent radionuclide, molybdenum (⁹⁹Mo), decays by beta⁻– emission to the ground state ⁹⁹Tc either directly or indirectly. The indirect route, which is the most common, involves the isomer ^99mTc, which in turn decays from its metastable state to ⁹⁹Tc by isomeric transition.

Fig. 42.2 Diagrammatic representation of ⁹⁹Mo decay.

Radionuclides which decay by this process are used in diagnostic imaging since they emit gamma-rays (see Table 42.1). It should be noted that ^99mTc is the most widely used radionuclide in hospital radiopharmacy today, making up the radionuclide component of around 90% of the radiopharmaceuticals produced. For these reasons the production processes for ^99mTc-radiopharmaceuticals will be especially emphasized.

Principles of ^99mTc-radiopharmaceutical production

The physical and chemical properties of ^99mTc make it nearly ideal for imaging purposes as outlined below:

Table 42.2 Examples of ^99mTc-radiopharmaceuticals

The production of ^99mTc – the molybdenum/technetium generator

Radionuclides with long half-lives (e.g. ¹³¹I, T_1/2 = 8 days) can be easily transported from production site to the user hospital. With shorter half-life radionuclides, e.g. ^99mTc, this supply system would be extremely difficult. As a result, a device known as the radionuclide generator is used to provide ^99mTc to the hospital site.

Radionuclide generators work on the principle that they contain a relatively long-lived ‘parent’ radionuclide that decays to produce a ‘daughter’ radionuclide. The chemical nature of parent and daughter are different, allowing separation of the daughter from the parent.

The molybdenum/technetium generator consists of ⁹⁹Mo (long-lived ‘parent’) absorbed onto an alumina-filled column, the ⁹⁹Mo being present in the form of molybdate (⁹⁹MoO₄²⁻). ⁹⁹Mo decays to its ‘daughter’ radionuclide ^99mTc, as pertechnetate, ^99mTcO₄⁻ (see Fig. 42.2). The amount of ^99mTcO₄⁻ grows as a result of the decay of ⁹⁹Mo, until a transient equilibrium is reached. At this point the amount of ^99mTc in the column appears to decay with the half-life of ⁹⁹Mo (Fig. 42.3).

Fig. 42.3 Radioactivity changes with time in a molybdenum/technetium generator column.

By drawing a solution of sodium chloride 0.9% weight in volume (w/v) through the column, ^99mTc is removed from the column in the form of sodium pertechnetate, Na^99mTcO₄. This process is known as eluting the generator and the resulting solution as the eluate. This process results in the production of a sterile solution of sodium pertechnetate that may now be used to make ^99mTc -radiopharmaceuticals.

⁹⁹Mo remains on the column where it decays to produce further ^99mTc, the equilibrium being re-established about 23 hours after elution. Elution of the generator is repeated daily to provide the radiopharmacy with a supply of ^99mTc for 7–14 days, beyond which the yield of ^99mTc becomes too small to be useful. Hospital radiopharmacies tend to buy generators on a weekly basis to provide a continuous supply of ^99mTc.

Design of a ^99mTc-generator

The design of a typical generator will be described by reference to the GE Healthcare generator, Drytec (Fig. 42.4). The main components of this generator are:

• A needle connected to the top end of the alumina column by tubing (it is this needle upon which a vial of IV Sodium Chloride Intravenous Infusion BP 0.9% w/v will be placed)

• A sterile alumina column to which is bound ⁹⁹Mo

• An elution needle which is connected to the bottom end of the alumina column

• Two 0.22 μm filters.

These components are housed within a compact plastic casing. The alumina column is encased in lead to give protection from the radiation.

Fig. 42.4 The Drytec^{® 99m}Tc-generator. (Courtesy of GE Healthcare plc.)

Operating the generator is fairly straightforward. A vial of Sodium Chloride Intravenous Infusion BP 0.9% w/v, supplied with the generator, is first placed on the left hand needle (see Fig. 42.4). A sterile evacuated vial, also supplied with the generator, is placed in a lead pot designed for the elution process. Then, by placing this on the elution needle, the vacuum draws sterile Sodium Chloride Intravenous Infusion BP 0.9% w/v from the vial through the column and into the evacuated vial. When eluate has been collected, air enters the elution vial after first passing through the column. This dries the column as well as removing excess vacuum in the elution vial. The elution process is now complete and the vial may be removed from the generator.

The sterility of the eluates is maintained throughout the useful life of the generator by the following means:

• The eluting solution is terminally sterilized Sodium Chloride Intravenous Infusion BP 0.9% w/v

• Air entering the system passes through a 0.22 μm filter

• A terminal eluate 0.22 μm filter is placed between the column and the elution needle

• Between elutions, the needle is protected by a single-use, disposable, sterile needle guard.

The elution of the generator should be carried out in a Grade A environment (see Ch. 29).

Preparation of ^99mTc-radiopharmaceuticals

The daily supply of ^99mTc is provided by the elution of the generator, resulting in a sterile solution of sodium pertechnetate that is subdivided to provide the radioactive component of the radiopharmaceutical. Some nuclear medicine investigations use sodium pertechnetate alone as the radiopharmaceutical (see Table 42.2). In this case, preparation of sodium pertechnetate injection requires only the subdivision from the generator eluate with perhaps some further dilution with Sodium Chloride Intravenous Infusion BP 0.9% w/v.

Other investigations, and these are in the majority, use radiopharmaceuticals that involve the chemical transformation of the sodium pertechnetate into another radiochemical form.

In order to make the preparation of ^99mTc-radiopharmaceuticals as simple as possible, commercially available ‘kits’ are used to manufacture these radiopharmaceuticals. These kits allow the radiopharmacist, in the hospital environment, to transform the pertechnetate, via complex chemical reactions performed within the vial, into the desired radiopharmaceutical. This is achieved by the simple addition of pertechnetate into the vial followed by shaking to dissolve the contents.

A kit consists of a prepacked set of sterile ingredients designed for the preparation of a specific radiopharmaceutical. Most commonly the ingredients are freeze dried, enclosed within a rubber-capped nitrogen-filled vial. Normally the kit contains sufficient materials to prepare a number of patient doses. In a typical formulation, the following may be found:

Given below is an example of how ^99mTc-radiopharmaceutical production may be performed. The compounding procedures must be carried out within the facilities described in Chapter 29 using aseptic technique and carried out as ‘closed’ procedures (GMP).

The production method (Fig. 42.5) involves two simple steps:

Fig. 42.5 Schematic representation of the preparation of patient doses of radiopharmaceuticals.

Step 1. The freeze-dried kit is reconstituted by aseptically transferring the necessary activity of sodium pertechnetate using a sterile syringe and needle. This step may also include a further dilution of the eluate with a suitable diluent. The amount of activity withdrawn for the reconstitution of the kit vial depends on two factors:

Manufacturers normally specify a maximum activity that may be added to the vial.

Step 2. The reconstituted kit is aseptically subdivided to provide each patient dose with sufficient activity to allow proper imaging after administration. As in Step 1, a diluent may be added to the final dose to give the desired radioactive concentration.

^99mTc-radiopharmaceuticals must be administered on the day of production, for the following reasons:

Radiation protection in the radiopharmacy

There are three basic principles to radiation protection:

In working practice all three of these principles may be used in isolation or together to reduce the radiation dose to the operator. For example, in the dispensing operation outlined in Figure 42.5, all vials containing radioactive material would be contained in a 3 mm lead pot. This will attenuate ^99mTc’s gamma-rays by a factor of approximately 1000. The syringes used to carry out the transfers would be only half full (i.e. 1 mL of radioactive solution would be transferred with a 2 mL syringe) in order to maximize the distance between the operator’s fingers and the source, without compromising the accuracy of the dispensing operation.

The syringes, during the operation, should also be contained within a syringe shield. These are made of materials such as lead, tungsten, lead glass or lead acrylic, the latter two being transparent. Lead and tungsten syringe shields have lead glass/acrylic windows incorporated to allow the operator to see the graduations on the syringe. Alternatively the whole syringe shield may be made of lead glass/acrylic which would have the advantage of giving greater visibility.

Handling the vials outside their lead pots should be carried out using long forceps and not with the fingers. The dispensing process should be carried out over a ‘drip tray’ that allows easy containment of any accidental spillage. It also should be carried out within a laminar flow safety cabinet or negative pressure isolator that provides operator protection as well as product protection (see Ch. 29).

The staff working in the radiopharmacy will be constantly monitored to assess their radiation exposure and to ensure compliance with safety legislation. Whole-body dose may be monitored with film badges and the radiation dose to the finger pulp with thermo luminescent dosimeters.